US20050169969A1 - Controlled delivery of therapeutic agents by insertable medical devices - Google Patents

Controlled delivery of therapeutic agents by insertable medical devices Download PDF

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US20050169969A1
US20050169969A1 US11/060,383 US6038305A US2005169969A1 US 20050169969 A1 US20050169969 A1 US 20050169969A1 US 6038305 A US6038305 A US 6038305A US 2005169969 A1 US2005169969 A1 US 2005169969A1
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therapeutic agent
protein
negatively charged
medical device
dna
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Weiping Li
Hai-quan Mao
Kam Leong
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Boston Scientific Scimed Inc
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    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61LMETHODS 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
    • A61L31/00Materials 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
    • A61L31/14Materials characterised by their function or physical properties, e.g. injectable or lubricating compositions, shape-memory materials, surface modified materials
    • A61L31/16Biologically active materials, e.g. therapeutic substances
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61LMETHODS 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
    • A61L29/00Materials for catheters, medical tubing, cannulae, or endoscopes or for coating catheters
    • A61L29/14Materials characterised by their function or physical properties, e.g. lubricating compositions
    • A61L29/16Biologically active materials, e.g. therapeutic substances
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61LMETHODS 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
    • A61L2300/00Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices
    • A61L2300/20Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices containing or releasing organic materials
    • A61L2300/258Genetic materials, DNA, RNA, genes, vectors, e.g. plasmids
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61LMETHODS 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
    • A61L2300/00Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices
    • A61L2300/40Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices characterised by a specific therapeutic activity or mode of action
    • A61L2300/416Anti-neoplastic or anti-proliferative or anti-restenosis or anti-angiogenic agents, e.g. paclitaxel, sirolimus
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61LMETHODS 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
    • A61L2300/00Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices
    • A61L2300/60Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices characterised by a special physical form
    • A61L2300/602Type of release, e.g. controlled, sustained, slow
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61LMETHODS 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
    • A61L2300/00Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices
    • A61L2300/60Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices characterised by a special physical form
    • A61L2300/606Coatings
    • A61L2300/608Coatings having two or more layers
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61LMETHODS 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
    • A61L2300/00Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices
    • A61L2300/80Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices characterised by a special chemical form
    • A61L2300/802Additives, excipients, e.g. cyclodextrins, fatty acids, surfactants

Definitions

  • the present invention relates to the localized delivery of negatively charged therapeutic agents, and more particularly to the localized and controlled delivery of DNA absorbed to the surface of insertable medical devices, in particular, balloon catheters or stents.
  • U.S. Pat. No. 5,304,121 which is incorporated herein by reference, discloses a method of delivering water-soluble drugs to tissue at desired locations of a body lumen wall. The method generally includes the steps of impregnating a hydrogel polymer on a balloon catheter with an aqueous drug solution, inserting the catheter into a blood vessel to a desired location, and expanding the catheter balloon against the surrounding tissue to allow the release of the drug.
  • One potential drawback to conventional localized drug administration is the uncontrolled manner at which the drug or drug solution is released from the delivery device. It is often desired, if not necessary, to control and/or lengthen the time period over which the drug is released. For example, it might be advantageous to lengthen the release time from seconds to minutes, or from minutes to hours, days, or even weeks. Exceptionally long release times as long as several months are often desired, for example, where the drug is released from an implanted device such as a stent. Moreover, it is often desired to control the release rate of the drug over prolonged periods of time.
  • Gene therapy provides an alternative approach to combating many intractable cardiovascular diseases.
  • a site-specific delivery of the genetic vectors to minimize systemic complications is crucial for the therapeutic potential of this approach to be realized.
  • Advances in interventional radiology and innovative designs in balloon angioplasty and stents have raised that possibility.
  • the invention disclosed herein solves the potential drawbacks to the drug delivery methods and instruments of the prior art by providing novel apparatus and methods for the transfer of therapeutic agents, such as therapeutic genes, to internal body sites.
  • the apparatus of the invention may be guided to diseased or deficient organs, or other lesions, and deliver the therapeutic agent in a targeted and controlled manner.
  • the present invention provides a method of delivering a negatively charged therapeutic agent to a target location within a mammalian body.
  • the method comprises the steps of applying a multiplicity of alternating layers of at least one cationic polyelectrolyte carrier and a multiplicity of layers of a negatively charged therapeutic agent to at least one surface of an insertable medical device.
  • a washing step is employed between application of the cationic polyelectrolyte and the negatively charged therapeutic agent.
  • the medical device is delivered to a target site within the body, and upon reaching the target site the negatively charged therapeutic agent is released into the target site.
  • the negatively charged therapeutic agent remains qualitatively and quantitatively intact during the stages of coating, washing, delivery and release.
  • the at least one cationic polyelectrolyte carrier is human serum albumin, gelatin, chitosan or a combination thereof.
  • the outer coating layer of the cationic polyelectrolyte carrier is chitosan, gelatin or both, which cationic polyelectrolyte carriers affect the time of release of the negatively charged therapeutic agent from the insertable medical device upon delivery.
  • the length of the time lag could be controlled by the type and amount of the cationic polyelectrolyte carrier used.
  • the device of this invention may compose a negatively charged, neutral, or positively charged structure such as polystyrene, polyethylene film, or glass.
  • a balloon catheter having a balloon in a diameter of about 0.4 cm, and a length of about 1.5, is used.
  • the negatively charged therapeutic agent is a polynucleotide and in a more preferred embodiment of this invention, the polynucleotide is a naked DNA, DNA inserted into a viral or non-viral vectors.
  • Another preferred embodiment of this invention provides an insertable medical device for insertion into a mammalian body, wherein the insertable medical device has a multiplicity of alternating layers of at least one cationic polyelectrolyte and a biologically effective amount of a negatively charged therapeutic agent, which are adsorbed on to a surface of the insertable medical device.
  • the amount of adsorbed negatively charged therapeutic agent increases linearly with the number of the layers of same applied and entrapped onto the surface of the medical device.
  • the insertable medical device is, for example, a stent or a balloon catheter.
  • an outer coating of the insertable medical device is employed to delay the release of the negatively charged therapeutic agent.
  • the outer coating is preferably gelatin, and more preferably chitosan.
  • a method for delivering a therapeutic agent that prevents or treats angiogenesis, restenosis, cardiomyopathy, cystic fibrosis, or malignant cell proliferation.
  • FIG. 1 is a histogram showing the effect of pH on the amount of DNA released from the surface of an insertable device. The amount of released DNA from 10 layers of coating was measured at pH 3 and 4.
  • FIG. 2 is a graph showing the relationship between the number of DNA layers and the amount of DNA adsorbed on the surface of a medical device. Released DNA was measured against the number of layers of DNA coatings on the surface of the medical device.
  • FIG. 3 is a photographic image of a DNA coated balloon catheter (ethydium bromide stained) before and after the DNA release.
  • 1 DNA coated balloon catheter (stained with ethydium bromide);
  • 2 DNA coated balloon catheter after in vitro release stained with ethydium 20 bromide;
  • 3 control uncoated balloon catheter.
  • FIG. 4 is a graph showing release kinetics studies using gelatin or chitosan coatings
  • FIG. 5 is a histogram showing transfection rate of HEK 293 cells with DNA released from a balloon medical device. Columns 1-6 each represents the following:
  • 3 pRE-Luc
  • 4 DNA+Chitosan coated surface
  • 5 DNA+gelatin coated surface
  • 6 DNA coated surface.
  • “Therapeutic agent” as used herein includes any compounds or compositions that induce a biological/medical reaction in vitro, in situ, or in vivo settings.
  • “Negatively charged therapeutic agent” as used herein, encompasses therapeutic agents that are negatively charged, either naturally or synthetically.
  • a negative charge may be added by any known chemical means or biological means (i.e., addition or deletion of functionalities, substitutions, or mutations).
  • “Therapeutic polynucleotide” as used herein includes nucleic acids with and without carrier vectors, compacting agents, virus, polymers, proteins, or targeting sequences.
  • Stepsis refers to a stricture of any bodily canal.
  • “Stent” refers to any tubular structure used to maintain or support a bodily orifice or cavity.
  • Balloon catheter refers to a tubular instrument with a balloon or multiple balloons that can be inflated or deflated without removal after insertion into the body.
  • Washing solution is water, any suitable buffers or detergents, solvents or a combination thereof.
  • “Surface” means any portions of any parts of an insertable medical device, or a combination of different portions of different surfaces, of an insertable medical device.
  • Effective expression-inducing amount means amount of a polynucleotide that effectuates expression of a polypeptide encoded by a gene contained in such polynucleotide.
  • “Qualitatively and quantitatively intact”, as described herein, means substantially the same biological activity and substantially the same amount. Substantially means at least about 90%.
  • This invention describes a medical device and a method to deliver a negatively charged therapeutic agent within the vasculature of a patient.
  • the negatively charged therapeutic agent is adsorbed onto one or more sites or surfaces of a medical device, thereby forming a coated surface, by a controlled adsorption technique.
  • the negatively charged therapeutic agent is released with a short controlled lag time of about 1 to several minutes (for example, 1, 5 or 10 minutes) to allow the medical device to reach the target site.
  • the method and medical device of this invention maximize the amount of a negative therapeutic agent that can be adsorbed to the medical device and control the release of the negatively charged therapeutic agent, with only minimal perturbation, at the target site.
  • the method and medical device use clinically acceptable polyelectrolytes biopolymers such as human serum albumin (HSA) to build the negatively charged therapeutic agent onto the surface of medical device.
  • HSA human serum albumin
  • Washing is employed between application of each alternate layers of one or more polyelectrolytes and the negatively charged therapeutic agent. Washing ensures that the negatively charged therapeutic agent is stably entrapped and not just precipitated on the surface of the device. This method of coating the medical device provides a more reproducible and controllable adsorption and release kinetics of a negatively charged therapeutic agent adsorption and release.
  • the medical device used in this invention is any insertable medical device, including, for example, stents, catheters, or balloon catheters.
  • a preferred medical device for use with the present invention is a balloon catheter.
  • the medical device of this invention can be used, for example, in any application for treating, preventing, or otherwise affecting the course of a disease or tissue or organ dysfunction.
  • the medical instrument of the invention can be used to induce or inhibit angiogenesis, or to prevent or treat restenosis, cardiomyopathy, or other dysfunction of the heart, and is particularly applicable to angioplasty treatment.
  • the method and medical device described herein can be used, for example, in treating cystic fibrosis or other dysfunction of the lung, for treating or inhibiting malignant cell proliferation, for treating any malignancy, and for inducing nerve, blood vessel or tissue regeneration in a particular tissue or organ.
  • the negatively charged therapeutic agent used in conjunction with the present invention includes, for example, any negatively charged compounds or compositions that are negatively charged, either naturally or synthetically by means of known chemical methods.
  • therapeutic agents and “drugs” are used interchangeably herein and include pharmaceutically active compounds and compositions, polynucleotides with and without carrier vectors such as lipids, compacting agents (such as histones), virus, polymers, proteins, and the like, with or without targeting sequences.
  • polynucleotide used in conjunction with the present invention include, for example, oligonucleotides, ribozymes, anti-sense oligonucleotides, DNA compacting agents, gene/vector systems (i.e., any vehicle that allows for the uptake and expression of nucleic acids), nucleic acids (including, for example, recombinant nucleic acids; naked DNA, cDNA, RNA; genomic DNA, cDNA or RNA in a non-infectious vector or in a viral vector and which further may have attached peptide targeting sequences; antisense nucleic acid (RNA or DNA); and DNA chimeras which include gene sequences and encoding for ferry proteins such as membrane trans locating sequences (“MTS”) and herpes simplex virus-I (“VP22”), and constitutive housekeeping genes which are theoretically expressed in all cell types.
  • gene/vector systems i.e., any vehicle that allows for the uptake and expression of nucleic acids
  • nucleic acids including,
  • virus vectors or vectors derived from viral sources include adenoviral vectors, herpes simplex vectors, papilloma vectors, adeno-associated vectors, retroviral vectors, and the like.
  • adenovirus is particularly preferred.
  • the therapeutic agent include any of the following compounds and compositions, provided that they are made to be negatively charged, using any known chemical and/or biological method. Any of these modifications is routinely made by one skilled in the art.
  • These compounds include anti-thrombogenic agents such as heparin, heparin derivatives, urokinase, and PPACK (dextrophenylalanine proline arginine chloromethylketone); antioxidants such as probucol and retinoic acid; angiogenic and anti-angiogenic agents and factors; agents blocking smooth muscle cell proliferation such as rapamycin, angiopeptin, and monoclonal antibodies capable of blocking smooth muscle cell proliferation; anti-inflammatory agents such as dexamethasone, prednisolone, corticosterone, budesonide, estrogen, sulfasalazine, acetyl salicylic acid, and mesalamine; calcium entry blockers such as verapamil, diltiazem and nifedipine
  • anti-coagulants such as D-Phe-Pro-Arg chloromethyl ketone, an RGD peptide-containing compound, heparin, antithrombin compounds, platelet receptor antagonists, anti-thrombin antibodies, anti-platelet receptor antibodies, enoxaparin, hirudin, Warafin sodium, Dicumarol, aspirin, prostaglandin inhibitors, platelet inhibitors and tick antiplatelet factors
  • vascular cell growth promotors such as growth factors, growth factor receptor antagonists, transcriptional activators, and translational promotors
  • vascular cell growth inhibitors such as growth factor inhibitors, growth factor receptor antagonists, transcriptional repressors, translational repressors, replication inhibitors, inhibitory antibodies, antibodies directed against growth factors, bifunctional molecules consisting of a growth factor and a
  • Polynucleotide sequences useful in practice of the invention include DNA or RNA sequences having a therapeutic effect after being taken up by a cell.
  • therapeutic polynucleotides include anti-sense DNA and RNA; DNA coding for an anti-sense RNA; or DNA coding for tRNA or rRNA to replace defective or deficient endogenous molecules.
  • the polynucleotides of the invention can also code for therapeutic proteins or polypeptides.
  • a polypeptide is understood to be any translation product of a polynucleotide regardless of size, and whether glycosylated or not.
  • Therapeutic proteins and polypeptides include as a primary example, those proteins or polypeptides that can compensate for defective or deficient species in an animal, or those that act through toxic effects to limit or remove harmful cells from the body.
  • polypeptides or proteins, DNA of which can be incorporated include without limitation, angiogenic factors and other molecules competent to induce angiogenesis, including acidic and basic fibroblast growth factors, vascular endothelial growth factor, hif-1, epidermal growth factor, transforming growth factor ⁇ and ⁇ , platelet-derived endothelial growth factor, platelet-derived growth factor, tumor necrosis factor ⁇ , hepatocyte growth factor and insulin-like growth factor; growth factors; cell cycle inhibitors including CDK inhibitors; anti-restenosis agents, including p15, p16, p18, p19, p21, p27, p53, p57, Rb, nFkB and E2F decoys, thymidine kinase (“TK”) and combinations thereof and other agents useful for interfering with cell proliferation, including agents for treating malignancies; and combinations thereof.
  • angiogenic factors and other molecules competent to induce angiogenesis including acidic and basic fibroblast growth factors,
  • MCP-I monocyte chemoattractant protein
  • BMP's the family of bone morphogenic proteins
  • the known proteins include BMP-2, BMP-3, BMP-4, BMP-5, BMP-6 (Vgr-1), BMP-7 (OP-1), BMP-8, BMP-9, BMP-10, BMP-11, BMP-12, BMP-13, BMP-14, BMP-15, and BMP-16.
  • BMP's are any of BMP-2, BMP-3, BMP-4, BMP-5, BMP-6 and BMP-7.
  • dimeric proteins can be provided as homodimers, heterodimers, or combinations thereof, alone or together with other molecules.
  • molecules capable of inducing an upstream or downstream effect of a BMP can be provided.
  • Such molecules include any of the “hedgehog” proteins, or the DNA's encoding them.
  • the amount of polynucleotide adsorbed is an effective expression-inducing amount.
  • the term “effective expression-inducing amount” means that amount of the polynucleotide that effectuates expression of a gene product encoded by such polynucleotide. Means for determining an effective expression-inducing amount of a polynucleotide are well known in the art.
  • an effective expression-inducing amount of the polypeptide of this invention is from about 0.3 to about 10 ⁇ g/cm 2 /layer, preferably from about 0.5 to about 0.9 ⁇ g/cm 2 /layer.
  • the amount of polynucleotide adsorbed onto the surface of the medical device is linearly proportional to the number of layers applied thereto. At least up to 40 layers of a therapeutic agent could be applied without affecting the properties of the medical device. Preferably from about 4 to about 60 layers, more preferably from about 10 to about 50 layers and most preferably from about 20 about 40 layers of a therapeutic agent are applied.
  • Polynucleotides for example, naked DNA, DNA plus vector or DNA delivery complex is captured on the surface of the medical device by a cationic polyelectrolyte carrier.
  • Viral or non-viral vectors could be used to potentiate the transfection efficiency of the released DNA.
  • a virus culture such as adenovirus could be layered on the surface of the insertable medical device. The concentration of the virus solution significantly affects the amount of the viral particles, which is incorporated into the layers on the surface of the insertable medical device. The release kinetics are reproducible and controlled. The released DNA is bioactive with little decrease of potency.
  • Biological activity of the DNA released from the medical device was studied by transfection of HEK 293 cells in vitro. The results indicated that the biological activity of the released DNA was the same as the control. Similar controlled-adsorption techniques were used to adsorb adenoviruses on to the balloon surface.
  • any suitable surface of the medical instrument may be coated.
  • the surfaces to be coated may comprise any medically acceptable material, such as, for example, carboxylated and aminated polystyrene, and silanized glass.
  • any medically acceptable polymers or copolymers, or natural polymers such as human serum albumin, gelatin, chitosan and the like may be used.
  • the natural polymers are adsorbed onto a desired surface of the medical device for coating. It is not necessary that an entire surface is coated, rather, merely a portion of a surface may be coated.
  • the coated medical device is inserted into the patient and directed to the target site.
  • the coated surface comes into contact with blood, the charge interaction of the cationic polymer and the negatively charged therapeutic agent is disrupted due to a charge screening effect and because the charge density of the polymer is greatly decreased at physiological pH.
  • proteolytic degradation of the gelatin or HAS may also contribute to the dissociation of the polymer-drug complex.
  • a more cationic and more hydrophobic polymer layer can be applied at the outer coating.
  • the quantity and quality of the biopolymer, particularly, the outer biopolymer is directly proportional to the duration of lag time achieved before the release occurred.
  • Chitosan a natural polysaccharide derived from crab shells, was used and shown to serve this purpose.
  • Other polymers can also be used to fine-tune the release kinetics of the therapeutic agent from the coated surface. For example, with a thin coating of condensed gelatin or chitosan, a short lag time of about 1-2 minutes is achieved before release occurs . Without the use of gelatin or chitosan, 100% of the DNA is released at physiological pH within minutes.
  • Organs and tissues that are treated by the methods of the present invention include any mammalian tissue or organ, whether injected in vivo or ex vivo.
  • Non-limiting examples include
  • the negatively charged therapeutic agents can be used, for example, in any application for treating, preventing, or otherwise affecting the course of a disease or tissue or organ dysfunction.
  • the methods of the invention can be used to induce or inhibit angiogenesis, as desired, to prevent or treat restenosis, to treat a cardiomyopathy or other dysfunction of the heart, for treating cystic fibrosis or other dysfunction of the lung, for treating or inhibiting malignant cell proliferation, for treating any malignancy, and for inducing nerve, blood vessel or tissue regeneration in a particular tissue or organ.
  • the negatively charged therapeutic agents of this invention are used preferably in angioplasty.
  • Multilayered films of DNA were built up on various negatively charged, neutral, and positively charged surfaces, by spraying or dipping.
  • the DNA adsorbed by HSA or gelatin was released quickly whereas, due to the hydrophobicity of chitosan at neutral pH, the DNA adsorbed by chitosan was released very slowly.
  • Table 1 shows natural polymers, as polyelectrolytes, are coated onto several surfaces, which surfaces were modified by different substrates. When different surfaces were dipped into a slightly acidic solution containing a polynucleotide, the positively charged coated surface induced adsorption of the polynucleotide (i.e., adsorption was driven by the charged interaction).
  • Successive layering of the surface with polyelectrolyte and DNA can be repeated as many times as needed to maximize the amount of DNA adsorbed to the surface.
  • the alternate layers of polyelectrolyte and polynucleotide are stable in a solution that is slightly acidic and of low ionic strength.
  • the effect of pH on the amount of DNA adsorbed was investigated by alternating adsorption of DNA and HSA at different pHs.
  • the results, as shown in FIG. 1 indicated that HSA adsorption is optimal at pH 4.0; no DNA could be adsorbed at pH 5.0 or higher.
  • the relationship between the number of DNA layers and adsorbed amount of DNA was investigated by alternating adsorption of DNA and HSA at pH4.0.
  • the results, as demonstrated in FIG. 2 showed that the amount of DNA absorbed increased linearly with the number of DNA layers on the surface of the medical device.
  • Carboxylated polystyrene (PS) wells were treated with 360 ⁇ l (per well) of 0.1% human serum albumin (HSA) in 25 mM HAc-NaAc/25 mM Na 2 SO 4 buffer (pH 4.0) at room temperature (RT) overnight.
  • HSA human serum albumin
  • the wells were washed thoroughly with water and then treated with 360 ⁇ L (per well) of DNA (247 ⁇ g/ml) in 25 mM HAc-NaAc/25 mM Na 2 SO 4 buffer (pH 4.0) at RT for 0.5 hr.
  • the wells were washed once with 360 ⁇ l (per well) of 25 mM HAc-NaAc/25 mM Na 2 SO 4 buffer (pH 4.0) and then treated again with 360 ⁇ l of 0.1% HSA in 25 mM HAc-NaAc/25 mM Na 2 SO 4 buffer (pH 4.0) at RT for 0.5 hr.
  • the wells were washed once with 360 ⁇ l (per well) of 25 mM HAc-NaAc/25 mM Na 2 SO 4 buffer (pH 4.0) and then treated again with 360 ⁇ l (per well) of DNA (247 ug/ml) in 25 mM HAc-NaAc/25 mM Na 2 SO 4 buffer (pH 4.0) at RT for 0.5 hr. The preceding washing steps were repeated until multilayer of DNA layers were adsorbed.
  • Two balloons (each having the diameter of 0.4 cm, length of 1.5 cm, and a surface area of ca. 1.88 cm 2 ) were treated with 5 ml of 0.1% HSA in 25 mM HAc-NaAc/25 mM Na 2 SO 4 buffer (pH 4.0) at RT for 2 hours.
  • the balloons were washed thoroughly with water and then treated with 5 ml of DNA (141 ⁇ g/ml, p 43 hGFP) in 25 mM HAc-NaAc/25 mM Na 2 SO 4 buffer (pH 4.0) at RT for 0.5 hr.
  • the balloons were washed once with 5 ml of 25 mM HAc-NaAc/25 mM Na 2 SO 4 buffer (pH 4.0) and then treated again with 5 ml of 0.1% HSA in 25 mM HAc-NaAc/25 mM Na 2 SO 4 buffer (pH 4.0) at RT for 0.5 hr.
  • Balloons were washed once with 5 ml of 25 mM HAc-NaAc/25 mM Na 2 SO 4 buffer (pH 4.0) and then treated again with 5 ml of DNA (141 ⁇ g/ml) in 25 mM HAc-NaAc/25 mM Na 2 SO 4 buffer (pH 4.0) at RT for 0.5 hr. The preceding washing steps were repeated until 4 DNA layers were adsorbed. Results are tabulated in Table 5 below. TABLE 5 DNA delivery on two balloons.
  • HEK 293 cells were seeded in 1 ml of the appropriate complete growth medium (10% serum) and incubated at 37° C. in a CO 2 incubator for 1 day. The culture medium was then removed and the transfection medium was added to the cells. The cells were then divided into 6 different groups:
  • Group 1 2 ⁇ g of DNA (Luci) and 2 ⁇ l of lipofectamine in 1 ml of serum-free medium;
  • Group 2 Released DNA (Luci, 20 layers) and 2 ⁇ l of lipofectamine in 1 ml of serum-free medium.
  • Group 3 2 ⁇ g of DNA (Luci) in I ml of serum-free medium.
  • Group 4 Released DNA (Luci, 20 layers) with an outermost chitosan coating.
  • Group 5 Released DNA (Luci, 20 layers) with an outermost gelatin coating.
  • Group 6 Released DNA (Luci, 20 layers). The cells were incubated at 37° C. in a CO 2 incubator for three days. The media was removed from the cells and the cells were rinsed once with 1 ⁇ PBS.
  • Cell Culture Lysis 200 ⁇ l was added at the concentration of 1 ⁇ Reagent per well to cover the cells. The cells were incubated at room temperature for 10-15 minutes. The cell extract (about 20 ⁇ l) was added to a luminometer cuvette at room temperature, followed by 100 ⁇ l of Luciferase Assay Reagent, again at room temperature. The cuvette was placed in the luminometer. Light emission was measured for ten seconds. Protein concentration was determined using the Bio-Rad protein assay kit. The results, as shown in FIG. 5 , were expressed as relative light units/min mg protein.
  • Two balloons [1.5 cm (L) ⁇ 0.3 cm (D), 1.41 cm 2 ] were treated with 1 ml of 0.1% gelatin (A, 300) in 25 mM HAc-NaAc/25 mM Na 2 SO 4 buffer (pH 5.0) at RT for 2 hours.
  • the balloons were washed three times with 25 mM HAc-NaAc/25 mM Na 2 SO 4 buffer (pH 5.0) and then treated with 1 ml of adenovirus (1.6 ⁇ 10 9 pfu/ml or 4 ⁇ 10 vp/ml containing a small amount of 125 I -labeled adenovirus) in 25 mM HAc-NaAc/25 mM Na 2 SO 4 buffer (pH 5.0) at RT for 2 minutes.
  • adenovirus 1.6 ⁇ 10 9 pfu/ml or 4 ⁇ 10 vp/ml containing a small amount of 125 I -labeled adenovirus
  • the balloons were washed once with 1 ml of 25 mM HAc-NaAc/25 mM Na 2 SO 4 buffer (pH 5.0) and then treated with 1 ml of 0.1% gelatin (A, 300) in 25 mM HAc-NaAc/25 mM Na 2 SO 4 buffer (pH 5.0) at RT for 2 minutes.
  • the balloons were washed once with 1 ml of 25 mM HAc-NaAc/25 mM Na 2 SO 4 buffer (pH 5.0) and then treated again with 1 ml of adenovirus (1.6 ⁇ 10 9 pfu/ml or 4 ⁇ 10 10 vp/ml) containing a small amount of 125 I-labeled adenovirus in 25 mM HAc-NaAc/25 mM Na 2 SO 4 buffer (pH 5.0) at RT for 2 minutes. The preceding two steps were repeated until ten adenovirus layers were adsorbed.
  • the balloons were washed once with 1 ml of 25 mM HAc-NaAc/25 mM Na 2 SO 4 buffer (pH 5.0) and dipped in 1 ml of 10% serum culture medium for 60 min.
  • the amount of adenovirus was determined by comparing the amount of radioactivity of 125 I (10 ml of counting medium was used for each sample, Count 1 minute). The result of this experiment is shown in Table 5, above.
  • a balloon catheter To stimulate angiogenesis or collateral blood flow in the adult rat heart, a balloon catheter, is coated with 40 layers of a DNA encoding human fibroblast growth factor-5 (hFGF-5) and is inserted into a blood vessel that perfuses the heart. Rats have been sacrificed at 3 weeks following injection and capillary density was measured by computerized light microscopy. The results have shown that a direct injection of a fibroblast growth factor -5 expression vector stimulates collateral vessel formation in areas of injected myocardium.
  • hFGF-5 human fibroblast growth factor-5

Abstract

A medical device and method for transportation and release of a therapeutic agent into a mammalian body are disclosed. The medical device is coated with alternating layers of a negatively charged therapeutic agent and a cationic polyelectrolyte, following a controlled adsorption technique. The method is simple, with minimal perturbation to the therapeutic agent and uses clinically acceptable biopolymers such as human serum albumin. The amount of the therapeutic agent that can be delivered by this technique is optimized by the number of the layers of the therapeutic agent adsorbed on the surface of medical device. There is a washing step between alternate layers of the therapeutic agent and cationic polyelectrolyte carrier, so that the amount of the therapeutic agent on the insertable medical device represents the portion that is stably entrapped and adsorbed on to the medical device. The insertable medical device and method according to this invention are capable of reproducibly delivering therapeutic agent to a site in a mammalian body, and allow for a highly reproducible and controllable release kinetics of the therapeutic agent.

Description

    BACKGROUND
  • 1. Field of the Invention
  • The present invention relates to the localized delivery of negatively charged therapeutic agents, and more particularly to the localized and controlled delivery of DNA absorbed to the surface of insertable medical devices, in particular, balloon catheters or stents.
  • 2. Background of the Invention
  • It is often desirable to administer drug agents at localized sites within the body because the systemic administration of drug agents treats the body as a whole even though the disease to be treated may be localized. Various methods have been proposed for such localized drug administration. For example, U.S. Pat. No. 5,304,121, which is incorporated herein by reference, discloses a method of delivering water-soluble drugs to tissue at desired locations of a body lumen wall. The method generally includes the steps of impregnating a hydrogel polymer on a balloon catheter with an aqueous drug solution, inserting the catheter into a blood vessel to a desired location, and expanding the catheter balloon against the surrounding tissue to allow the release of the drug.
  • One potential drawback to conventional localized drug administration is the uncontrolled manner at which the drug or drug solution is released from the delivery device. It is often desired, if not necessary, to control and/or lengthen the time period over which the drug is released. For example, it might be advantageous to lengthen the release time from seconds to minutes, or from minutes to hours, days, or even weeks. Exceptionally long release times as long as several months are often desired, for example, where the drug is released from an implanted device such as a stent. Moreover, it is often desired to control the release rate of the drug over prolonged periods of time.
  • Gene therapy provides an alternative approach to combating many intractable cardiovascular diseases. A site-specific delivery of the genetic vectors to minimize systemic complications is crucial for the therapeutic potential of this approach to be realized. Advances in interventional radiology and innovative designs in balloon angioplasty and stents have raised that possibility.
  • The invention disclosed herein solves the potential drawbacks to the drug delivery methods and instruments of the prior art by providing novel apparatus and methods for the transfer of therapeutic agents, such as therapeutic genes, to internal body sites. The apparatus of the invention may be guided to diseased or deficient organs, or other lesions, and deliver the therapeutic agent in a targeted and controlled manner.
  • SUMMARY OF THE INVENTION
  • In one aspect, the present invention provides a method of delivering a negatively charged therapeutic agent to a target location within a mammalian body. The method comprises the steps of applying a multiplicity of alternating layers of at least one cationic polyelectrolyte carrier and a multiplicity of layers of a negatively charged therapeutic agent to at least one surface of an insertable medical device. A washing step is employed between application of the cationic polyelectrolyte and the negatively charged therapeutic agent. The medical device is delivered to a target site within the body, and upon reaching the target site the negatively charged therapeutic agent is released into the target site. The negatively charged therapeutic agent remains qualitatively and quantitatively intact during the stages of coating, washing, delivery and release.
  • In a preferred embodiment of this invention, the at least one cationic polyelectrolyte carrier is human serum albumin, gelatin, chitosan or a combination thereof.
  • In a more preferred embodiment of this invention, the outer coating layer of the cationic polyelectrolyte carrier is chitosan, gelatin or both, which cationic polyelectrolyte carriers affect the time of release of the negatively charged therapeutic agent from the insertable medical device upon delivery. The length of the time lag could be controlled by the type and amount of the cationic polyelectrolyte carrier used.
  • The device of this invention may compose a negatively charged, neutral, or positively charged structure such as polystyrene, polyethylene film, or glass. In a preferred embodiment of this invention, a balloon catheter, having a balloon in a diameter of about 0.4 cm, and a length of about 1.5, is used.
  • In yet another preferred embodiment of this invention, the negatively charged therapeutic agent is a polynucleotide and in a more preferred embodiment of this invention, the polynucleotide is a naked DNA, DNA inserted into a viral or non-viral vectors.
  • Another preferred embodiment of this invention provides an insertable medical device for insertion into a mammalian body, wherein the insertable medical device has a multiplicity of alternating layers of at least one cationic polyelectrolyte and a biologically effective amount of a negatively charged therapeutic agent, which are adsorbed on to a surface of the insertable medical device. The amount of adsorbed negatively charged therapeutic agent increases linearly with the number of the layers of same applied and entrapped onto the surface of the medical device.
  • In a preferred embodiment of this invention, the insertable medical device is, for example, a stent or a balloon catheter. In a more preferred embodiment of this invention an outer coating of the insertable medical device is employed to delay the release of the negatively charged therapeutic agent. The outer coating is preferably gelatin, and more preferably chitosan.
  • In another aspect of this invention, there is provided a method for delivering a therapeutic agent that prevents or treats angiogenesis, restenosis, cardiomyopathy, cystic fibrosis, or malignant cell proliferation.
  • BRIEF DESCRIPTION OF THE DRAWINGS
  • FIG. 1 is a histogram showing the effect of pH on the amount of DNA released from the surface of an insertable device. The amount of released DNA from 10 layers of coating was measured at pH 3 and 4.
  • FIG. 2 is a graph showing the relationship between the number of DNA layers and the amount of DNA adsorbed on the surface of a medical device. Released DNA was measured against the number of layers of DNA coatings on the surface of the medical device.
  • FIG. 3 is a photographic image of a DNA coated balloon catheter (ethydium bromide stained) before and after the DNA release. 1: DNA coated balloon catheter (stained with ethydium bromide); 2: DNA coated balloon catheter after in vitro release stained with ethydium 20 bromide; and 3: control uncoated balloon catheter.
  • FIG. 4 is a graph showing release kinetics studies using gelatin or chitosan coatings
      • ▪ without outer coating
      • ⋄ with gelatin coating (2%)
      • □ with chitosan coating (10 ppm)
      • ⋄ with chitosan coating (20 ppm)
      • Figure US20050169969A1-20050804-P00001
        with chitosan coating (40 ppm)
  • FIG. 5 is a histogram showing transfection rate of HEK 293 cells with DNA released from a balloon medical device. Columns 1-6 each represents the following:
  • 1: pRE-Luc+Lipofectamine; 2: pRE-Luc released from the balloon+Lipofectamine;
  • 3: pRE-Luc; 4: DNA+Chitosan coated surface; 5: DNA+gelatin coated surface; 6: DNA coated surface.
  • DETAILED DESCRIPTION OF THE INVENTION
  • Definitions
  • As used herein, the following terms are defined as follows:
  • “Therapeutic agent” as used herein includes any compounds or compositions that induce a biological/medical reaction in vitro, in situ, or in vivo settings.
  • “Negatively charged therapeutic agent” as used herein, encompasses therapeutic agents that are negatively charged, either naturally or synthetically. A negative charge may be added by any known chemical means or biological means (i.e., addition or deletion of functionalities, substitutions, or mutations).
  • “Therapeutic polynucleotide” as used herein includes nucleic acids with and without carrier vectors, compacting agents, virus, polymers, proteins, or targeting sequences.
  • “Stenosis” refers to a stricture of any bodily canal.
  • “Stent” refers to any tubular structure used to maintain or support a bodily orifice or cavity.
  • “Balloon catheter” refers to a tubular instrument with a balloon or multiple balloons that can be inflated or deflated without removal after insertion into the body.
  • “Washing solution” according to this invention is water, any suitable buffers or detergents, solvents or a combination thereof.
  • “Surface” according to this invention means any portions of any parts of an insertable medical device, or a combination of different portions of different surfaces, of an insertable medical device.
  • “Effective expression-inducing amount”, as described herein, means amount of a polynucleotide that effectuates expression of a polypeptide encoded by a gene contained in such polynucleotide.
  • “Qualitatively and quantitatively intact”, as described herein, means substantially the same biological activity and substantially the same amount. Substantially means at least about 90%.
  • DETAILED DESCRIPTION OF THE INVENTION
  • This invention describes a medical device and a method to deliver a negatively charged therapeutic agent within the vasculature of a patient. The negatively charged therapeutic agent is adsorbed onto one or more sites or surfaces of a medical device, thereby forming a coated surface, by a controlled adsorption technique. When the coated surface(s) comes into contact with the patient's blood, the negatively charged therapeutic agent is released with a short controlled lag time of about 1 to several minutes (for example, 1, 5 or 10 minutes) to allow the medical device to reach the target site.
  • The method and medical device of this invention, as described herein, maximize the amount of a negative therapeutic agent that can be adsorbed to the medical device and control the release of the negatively charged therapeutic agent, with only minimal perturbation, at the target site. The method and medical device, as described herein, use clinically acceptable polyelectrolytes biopolymers such as human serum albumin (HSA) to build the negatively charged therapeutic agent onto the surface of medical device.
  • Washing is employed between application of each alternate layers of one or more polyelectrolytes and the negatively charged therapeutic agent. Washing ensures that the negatively charged therapeutic agent is stably entrapped and not just precipitated on the surface of the device. This method of coating the medical device provides a more reproducible and controllable adsorption and release kinetics of a negatively charged therapeutic agent adsorption and release.
  • The medical device used in this invention is any insertable medical device, including, for example, stents, catheters, or balloon catheters. A preferred medical device for use with the present invention is a balloon catheter. The medical device of this invention can be used, for example, in any application for treating, preventing, or otherwise affecting the course of a disease or tissue or organ dysfunction. For example, the medical instrument of the invention can be used to induce or inhibit angiogenesis, or to prevent or treat restenosis, cardiomyopathy, or other dysfunction of the heart, and is particularly applicable to angioplasty treatment.
  • Additionally, the method and medical device described herein can be used, for example, in treating cystic fibrosis or other dysfunction of the lung, for treating or inhibiting malignant cell proliferation, for treating any malignancy, and for inducing nerve, blood vessel or tissue regeneration in a particular tissue or organ.
  • Specific examples of the negatively charged therapeutic agent used in conjunction with the present invention includes, for example, any negatively charged compounds or compositions that are negatively charged, either naturally or synthetically by means of known chemical methods. In particular, the terms “therapeutic agents” and “drugs” are used interchangeably herein and include pharmaceutically active compounds and compositions, polynucleotides with and without carrier vectors such as lipids, compacting agents (such as histones), virus, polymers, proteins, and the like, with or without targeting sequences.
  • Specific examples of the polynucleotide used in conjunction with the present invention include, for example, oligonucleotides, ribozymes, anti-sense oligonucleotides, DNA compacting agents, gene/vector systems (i.e., any vehicle that allows for the uptake and expression of nucleic acids), nucleic acids (including, for example, recombinant nucleic acids; naked DNA, cDNA, RNA; genomic DNA, cDNA or RNA in a non-infectious vector or in a viral vector and which further may have attached peptide targeting sequences; antisense nucleic acid (RNA or DNA); and DNA chimeras which include gene sequences and encoding for ferry proteins such as membrane trans locating sequences (“MTS”) and herpes simplex virus-I (“VP22”), and constitutive housekeeping genes which are theoretically expressed in all cell types.
  • Non-limiting examples of virus vectors or vectors derived from viral sources include adenoviral vectors, herpes simplex vectors, papilloma vectors, adeno-associated vectors, retroviral vectors, and the like. The use of adenovirus is particularly preferred.
  • Other examples of the therapeutic agent include any of the following compounds and compositions, provided that they are made to be negatively charged, using any known chemical and/or biological method. Any of these modifications is routinely made by one skilled in the art. These compounds include anti-thrombogenic agents such as heparin, heparin derivatives, urokinase, and PPACK (dextrophenylalanine proline arginine chloromethylketone); antioxidants such as probucol and retinoic acid; angiogenic and anti-angiogenic agents and factors; agents blocking smooth muscle cell proliferation such as rapamycin, angiopeptin, and monoclonal antibodies capable of blocking smooth muscle cell proliferation; anti-inflammatory agents such as dexamethasone, prednisolone, corticosterone, budesonide, estrogen, sulfasalazine, acetyl salicylic acid, and mesalamine; calcium entry blockers such as verapamil, diltiazem and nifedipine; antineoplastic/antiproliferative/anti-mitotic agents such as paclitaxel, 5-fluorouracil, methotrexate, doxorubicin, daunorubicin, cyclosporine, cisplatin, vinblastine, vincristine, epothilones, endostatin, angiostatin and thymidine kinase inhibitors; antimicrobials such as triclosan, cephalosporins, aminoglycosides, andnitorfurantoin; anesthetic agents such as lidocaine, bupivacaine, and ropivacaine; nitric oxide (NO) donors. such as lisidomine, molsidomine, L-arginine, NO-protein adducts, NO-carbohydrate adducts, polymeric or oligomeric NO adducts; anti-coagulants such as D-Phe-Pro-Arg chloromethyl ketone, an RGD peptide-containing compound, heparin, antithrombin compounds, platelet receptor antagonists, anti-thrombin antibodies, anti-platelet receptor antibodies, enoxaparin, hirudin, Warafin sodium, Dicumarol, aspirin, prostaglandin inhibitors, platelet inhibitors and tick antiplatelet factors; vascular cell growth promotors such as growth factors, growth factor receptor antagonists, transcriptional activators, and translational promotors; vascular cell growth inhibitors such as growth factor inhibitors, growth factor receptor antagonists, transcriptional repressors, translational repressors, replication inhibitors, inhibitory antibodies, antibodies directed against growth factors, bifunctional molecules consisting of a growth factor and a cytotoxin, bifunctional molecules consisting of an antibody and a cytotoxin; cholesterol-lowering agents; vasodilating-agents; agents which interfere with endogeneus vascoactive mechanisms; survival genes which protect against cell death, such as anti-apoptotic Bcl-2 family factors and Akt kinase; and combinations thereof.
  • Polynucleotide sequences useful in practice of the invention include DNA or RNA sequences having a therapeutic effect after being taken up by a cell. Examples of therapeutic polynucleotides include anti-sense DNA and RNA; DNA coding for an anti-sense RNA; or DNA coding for tRNA or rRNA to replace defective or deficient endogenous molecules. The polynucleotides of the invention can also code for therapeutic proteins or polypeptides. A polypeptide is understood to be any translation product of a polynucleotide regardless of size, and whether glycosylated or not. Therapeutic proteins and polypeptides include as a primary example, those proteins or polypeptides that can compensate for defective or deficient species in an animal, or those that act through toxic effects to limit or remove harmful cells from the body.
  • In addition, the polypeptides or proteins, DNA of which can be incorporated, include without limitation, angiogenic factors and other molecules competent to induce angiogenesis, including acidic and basic fibroblast growth factors, vascular endothelial growth factor, hif-1, epidermal growth factor, transforming growth factor α and β, platelet-derived endothelial growth factor, platelet-derived growth factor, tumor necrosis factor α, hepatocyte growth factor and insulin-like growth factor; growth factors; cell cycle inhibitors including CDK inhibitors; anti-restenosis agents, including p15, p16, p18, p19, p21, p27, p53, p57, Rb, nFkB and E2F decoys, thymidine kinase (“TK”) and combinations thereof and other agents useful for interfering with cell proliferation, including agents for treating malignancies; and combinations thereof. Still other useful factors, which can be provided as polypeptides or as DNA encoding these polypeptides, include monocyte chemoattractant protein (“MCP-I”), and the family of bone morphogenic proteins (“BMP's”). The known proteins include BMP-2, BMP-3, BMP-4, BMP-5, BMP-6 (Vgr-1), BMP-7 (OP-1), BMP-8, BMP-9, BMP-10, BMP-11, BMP-12, BMP-13, BMP-14, BMP-15, and BMP-16. Currently preferred BMP's are any of BMP-2, BMP-3, BMP-4, BMP-5, BMP-6 and BMP-7. These dimeric proteins can be provided as homodimers, heterodimers, or combinations thereof, alone or together with other molecules. Alternatively or, in addition, molecules capable of inducing an upstream or downstream effect of a BMP can be provided. Such molecules include any of the “hedgehog” proteins, or the DNA's encoding them.
  • The amount of polynucleotide adsorbed is an effective expression-inducing amount. As used herein, the term “effective expression-inducing amount” means that amount of the polynucleotide that effectuates expression of a gene product encoded by such polynucleotide. Means for determining an effective expression-inducing amount of a polynucleotide are well known in the art. For example, an effective expression-inducing amount of the polypeptide of this invention is from about 0.3 to about 10 μg/cm2/layer, preferably from about 0.5 to about 0.9 μg/cm2/layer. The amount of polynucleotide adsorbed onto the surface of the medical device is linearly proportional to the number of layers applied thereto. At least up to 40 layers of a therapeutic agent could be applied without affecting the properties of the medical device. Preferably from about 4 to about 60 layers, more preferably from about 10 to about 50 layers and most preferably from about 20 about 40 layers of a therapeutic agent are applied.
  • Polynucleotides, for example, naked DNA, DNA plus vector or DNA delivery complex is captured on the surface of the medical device by a cationic polyelectrolyte carrier. Viral or non-viral vectors could be used to potentiate the transfection efficiency of the released DNA. For example, a virus culture, such as adenovirus could be layered on the surface of the insertable medical device. The concentration of the virus solution significantly affects the amount of the viral particles, which is incorporated into the layers on the surface of the insertable medical device. The release kinetics are reproducible and controlled. The released DNA is bioactive with little decrease of potency.
  • Biological activity of the DNA released from the medical device was studied by transfection of HEK 293 cells in vitro. The results indicated that the biological activity of the released DNA was the same as the control. Similar controlled-adsorption techniques were used to adsorb adenoviruses on to the balloon surface.
  • Any suitable surface of the medical instrument may be coated. The surfaces to be coated may comprise any medically acceptable material, such as, for example, carboxylated and aminated polystyrene, and silanized glass.
  • As cationic polyelectrolyte carriers, any medically acceptable polymers or copolymers, or natural polymers such as human serum albumin, gelatin, chitosan and the like may be used. The natural polymers are adsorbed onto a desired surface of the medical device for coating. It is not necessary that an entire surface is coated, rather, merely a portion of a surface may be coated.
  • The coated medical device is inserted into the patient and directed to the target site. When the coated surface comes into contact with blood, the charge interaction of the cationic polymer and the negatively charged therapeutic agent is disrupted due to a charge screening effect and because the charge density of the polymer is greatly decreased at physiological pH. In addition, proteolytic degradation of the gelatin or HAS may also contribute to the dissociation of the polymer-drug complex.
  • To delay dissociation of the adsorbed therapeutic agent when a medical device coating with same is inserted into the blood stream, a more cationic and more hydrophobic polymer layer can be applied at the outer coating. The quantity and quality of the biopolymer, particularly, the outer biopolymer, is directly proportional to the duration of lag time achieved before the release occurred. Chitosan, a natural polysaccharide derived from crab shells, was used and shown to serve this purpose. Other polymers can also be used to fine-tune the release kinetics of the therapeutic agent from the coated surface. For example, with a thin coating of condensed gelatin or chitosan, a short lag time of about 1-2 minutes is achieved before release occurs . Without the use of gelatin or chitosan, 100% of the DNA is released at physiological pH within minutes.
  • Organs and tissues that are treated by the methods of the present invention include any mammalian tissue or organ, whether injected in vivo or ex vivo. Non-limiting examples include
  • the heart, lung, brain, liver, skeletal muscle, smooth muscle, kidney, bladder, intestines, stomach, pancreas, ovary, prostate, cartilage and bone.
  • The negatively charged therapeutic agents, according to the invention, can be used, for example, in any application for treating, preventing, or otherwise affecting the course of a disease or tissue or organ dysfunction. For example, the methods of the invention can be used to induce or inhibit angiogenesis, as desired, to prevent or treat restenosis, to treat a cardiomyopathy or other dysfunction of the heart, for treating cystic fibrosis or other dysfunction of the lung, for treating or inhibiting malignant cell proliferation, for treating any malignancy, and for inducing nerve, blood vessel or tissue regeneration in a particular tissue or organ. Particularly, the negatively charged therapeutic agents of this invention are used preferably in angioplasty. Having now fully described the invention, the same would be more readily understood by reference to specific examples which are provided by way of illustration, and not intended to be limiting of the invention, unless herein specified.
  • EXAMPLE 1 Effect of Surfaces and Polyelectrolytes on the DNA Release
  • Multilayered films of DNA were built up on various negatively charged, neutral, and positively charged surfaces, by spraying or dipping. The DNA adsorbed by HSA or gelatin was released quickly whereas, due to the hydrophobicity of chitosan at neutral pH, the DNA adsorbed by chitosan was released very slowly. The result of this experiment is tabulated in Table 1 below. Table 1 shows natural polymers, as polyelectrolytes, are coated onto several surfaces, which surfaces were modified by different substrates. When different surfaces were dipped into a slightly acidic solution containing a polynucleotide, the positively charged coated surface induced adsorption of the polynucleotide (i.e., adsorption was driven by the charged interaction). Successive layering of the surface with polyelectrolyte and DNA can be repeated as many times as needed to maximize the amount of DNA adsorbed to the surface. The alternate layers of polyelectrolyte and polynucleotide are stable in a solution that is slightly acidic and of low ionic strength.
    TABLE 1
    The amount of DNA release with different polyelectrolyte
    combinations and substrates
    Number Amount of DNA released
    Substrate Formulation of layers (μg/cm2)
    PEG/gelatin- Gelatin/DNA 4 1.23 (overnight)
    modified Glass
    Carboxylated PS HSA/DNA 4 1.24 (0.5 hr)
    Polyethylene film HSA/DNA 4 1.14 (0.5 hr)
    PET balloon HSA/DNA 4 1.29 (0.5 hr)
    PET balloon HSA/DNA 10 3.28 (overnight)
    PET balloon Gelatin/DNA 10 2.62/5.13 (0.5 hr/4 d)
    PET balloon Chitosan/DNA 20 0/0.86 (1 hr/17 hrs)
  • EXAMPLE 2 Effects of pH on the Amount of DNA Released
  • The effect of pH on the amount of DNA adsorbed was investigated by alternating adsorption of DNA and HSA at different pHs. The results, as shown in FIG. 1, indicated that HSA adsorption is optimal at pH 4.0; no DNA could be adsorbed at pH 5.0 or higher. The relationship between the number of DNA layers and adsorbed amount of DNA was investigated by alternating adsorption of DNA and HSA at pH4.0. The results, as demonstrated in FIG. 2, showed that the amount of DNA absorbed increased linearly with the number of DNA layers on the surface of the medical device.
  • EXAMPLE 3 The Release Kinetics of the Adsorbed DNA from the Surface of the Medical Device
  • Release kinetics studies indicated that the adsorbed polynucleotide could be released completely within 5 minutes. (See FIG. 3 which shows that the adsorbed DNA was released almost completely from the surface of a coated balloon catheter.) When the medical device is coated with a condensed gelatin coating, the release rate of the adsorbed DNA was reduced slightly, whereas when the device was coated with a thin layer of chitosan, the release rate of the adsorbed DNA was decreased remarkably. The release kinetics of the adsorbed DNA, as shown in FIG. 4, was also shown to be dependant on the thickness of chitosan coating (i.e., the concentration of chitosan solution when the dipping time was fixed).
  • EXAMPLE 4 Biological Activity of the Released DNA
  • The biological activity of DNA, released from the surface of a coated medical device, was investigated by transfecting HEK 293 cells in vitro. The result of this study, as shown in FIG. 5, indicates that the released DNA was still biologically active. A comparison between columns 1 and 2 of FIG. 5 shows that the DNA released from the medical device coated with gelatin or chitosan, similar to the naked DNA, had a high transfection efficiency. Occasionally, cationic gelatin complexes with DNA in the soluble form and transfects cells in culture better than naked DNA.
  • EXAMPLE 5 Feasibility of Delivering Adenovirus
  • Using similar adsorption technique with gelatin as the polycation, 125I labeled recombinant adenovirus, encoding the Lac Z gene, was adsorbed onto a balloon surface. The result of this experiment is shown in Table 2 below. Table 2 indicates that the amount of plaque forming units and virus particles of adenovirus, released or remained on the balloon after release delivery, constitutes a major portion of the total amount of virus found on the surface of the balloon.
    TABLE 2
    Feasibility of delivering adenovirus
    Total amount of virus Amount of adenovirus
    Readings (pfu) (particles) (pfu/cm2) (vp/cm2)
    Calibration Standard 538.5 ± 52 6.4 ± 0.6 × 107 1.6 ± 0.2 × 109
    Released adenovirus   47 ± 9.5 5.6 ± 1.1 × 106 1.4 ± 0.3 × 108 4.0 ± 0.8 × 106 1.0 ± 0.2 × 108
    Virus remained 168.5 ± 58 2.0 ± 0.7 × 107 5.0 ± 1.7 × 108 1.4 ± 0.5 × 107 3.5 ± 1.2 × 108
    balloon after release

    Table 2 shows the amount of adenovirus released in 60 minutes in 10% serum culture media from a 10-layered balloon.
  • EXAMPLE 6 DNA Delivery via Negatively Charged Polystyrene (PS) Surface
  • Carboxylated polystyrene (PS) wells were treated with 360 μl (per well) of 0.1% human serum albumin (HSA) in 25 mM HAc-NaAc/25 mM Na2SO4 buffer (pH 4.0) at room temperature (RT) overnight. The wells were washed thoroughly with water and then treated with 360 μL (per well) of DNA (247 μg/ml) in 25 mM HAc-NaAc/25 mM Na2SO4 buffer (pH 4.0) at RT for 0.5 hr. The wells were washed once with 360 μl (per well) of 25 mM HAc-NaAc/25 mM Na2SO4 buffer (pH 4.0) and then treated again with 360 μl of 0.1% HSA in 25 mM HAc-NaAc/25 mM Na2SO4 buffer (pH 4.0) at RT for 0.5 hr. The wells were washed once with 360 μl (per well) of 25 mM HAc-NaAc/25 mM Na2SO4 buffer (pH 4.0) and then treated again with 360 μl (per well) of DNA (247 ug/ml) in 25 mM HAc-NaAc/25 mM Na2SO4 buffer (pH 4.0) at RT for 0.5 hr. The preceding washing steps were repeated until multilayer of DNA layers were adsorbed. The wells were washed once with 360 μl (per well) of 25 mM HAc-NaAc/25 mM Na2SO4 buffer (pH 4.0) and then treated with 360 μl of 1× phosphate buffered saline (PBS) at RT for 0.5 hr .The amount of DNA released in PBS was determined, and shown in Table 3 below.
    TABLE 3
    Relationship between the number of DNA layers and the amount of
    DNA Released
    A B C D
    Number of DNA layers 1 2 3 4
    Released DNA (μg/cm2) 0.105 0.493 0.806 1.240
  • EXAMPLE 7 DNA Delivery via Positively Charged Glass Surface
  • Two pieces of polyethylene glycol (PEG)/gelatin-modified glass plates were treated with 2 ml of DNA (140 μg/ml) in 25 mM HAc-NaAc/25 mM Na2SO4 buffer (pH 5.5) at 37° C. for 1 hr. The plates were washed once with 3 ml of 25 mM HAc-NaAc/25 mM Na2SO4 buffer (pH 4.0) and then treated with 2 ml of 0.05% gelatin (A, 175) in 25 mM HAc-NaAc/25 mM Na2SO4 buffer (pH 4.8) at 37° C. for 1 hr. The plates were washed once with 3 ml of 25 mM HAc-NaAc/25 mM Na2SO4 buffer (pH 4.0) and then treated again with 2 ml of DNA (88 μg/ml) in 25 mM HAc-NaAc/25 mM Na2SO4 buffer (pH 5.5) at 37° C. for 1 hr. The preceding washing steps were repeated until several layers of DNA layers were adsorbed. The plates were washed once with 3 ml of 25 mM HAc-NaAc/25 mM Na2SO4 buffer (pH 4.0) and then dipped in 2 ml of 1×PBS at RT for 1 hr. The amount of DNA released in PBS is shown in Table 4 below.
    TABLE 4
    DNA release from glass surface.
    A B
    Number of DNA layers 4 9
    Released DNA (μg/cm2) 1.231 3.923
  • EXAMPLE 8 cDNA Delivery via Neutral PET Balloon Surface
  • Two balloons (each having the diameter of 0.4 cm, length of 1.5 cm, and a surface area of ca. 1.88 cm2) were treated with 5 ml of 0.1% HSA in 25 mM HAc-NaAc/25 mM Na2SO4 buffer (pH 4.0) at RT for 2 hours. The balloons were washed thoroughly with water and then treated with 5 ml of DNA (141 μg/ml, p 43 hGFP) in 25 mM HAc-NaAc/25 mM Na2SO4 buffer (pH 4.0) at RT for 0.5 hr. The balloons were washed once with 5 ml of 25 mM HAc-NaAc/25 mM Na2SO4 buffer (pH 4.0) and then treated again with 5 ml of 0.1% HSA in 25 mM HAc-NaAc/25 mM Na2SO4 buffer (pH 4.0) at RT for 0.5 hr. Balloons were washed once with 5 ml of 25 mM HAc-NaAc/25 mM Na2SO4 buffer (pH 4.0) and then treated again with 5 ml of DNA (141 μg/ml) in 25 mM HAc-NaAc/25 mM Na2SO4 buffer (pH 4.0) at RT for 0.5 hr. The preceding washing steps were repeated until 4 DNA layers were adsorbed. Results are tabulated in Table 5 below.
    TABLE 5
    DNA delivery on two balloons.
    A B
    Readings (ng/ml) 55 54
    Released DNA (μg) 2.42 2.376
    Released DNA (μg/cm2) 1.287 1.264

    A: Balloon was washed once with 5 ml of 25 mM HAc-NaAc/25 mM Na2SO4 buffer (pH 4.0) and then dipped in 4 ml of I × PBS at RT for 0.5 hr.

    B: Balloon was not washed and directly dipped in 4 ml of 1 × PBS at RT for 0.5 hr. The amount of DNA released in PBS was determined (200 μl was taken into 2 ml of test solution).
  • EXAMPLE 9 Transfection of HEK 293 Cells in Vitro
  • In a twelve-well tissue culture plate, 8×104 HEK 293 cells per well were seeded in 1 ml of the appropriate complete growth medium (10% serum) and incubated at 37° C. in a CO2 incubator for 1 day. The culture medium was then removed and the transfection medium was added to the cells. The cells were then divided into 6 different groups:
  • Group 1: 2 μg of DNA (Luci) and 2 μl of lipofectamine in 1 ml of serum-free medium; Group 2: Released DNA (Luci, 20 layers) and 2 μl of lipofectamine in 1 ml of serum-free medium. Group 3: 2 μg of DNA (Luci) in I ml of serum-free medium. Group 4: Released DNA (Luci, 20 layers) with an outermost chitosan coating. Group 5: Released DNA (Luci, 20 layers) with an outermost gelatin coating. Group 6: Released DNA (Luci, 20 layers). The cells were incubated at 37° C. in a CO2 incubator for three days. The media was removed from the cells and the cells were rinsed once with 1×PBS. Cell Culture Lysis (200 μl) was added at the concentration of 1× Reagent per well to cover the cells. The cells were incubated at room temperature for 10-15 minutes. The cell extract (about 20 μl) was added to a luminometer cuvette at room temperature, followed by 100 μl of Luciferase Assay Reagent, again at room temperature. The cuvette was placed in the luminometer. Light emission was measured for ten seconds. Protein concentration was determined using the Bio-Rad protein assay kit. The results, as shown in FIG. 5, were expressed as relative light units/min mg protein.
  • EXAMPLE 10 Adenovirus Adsorption
  • Two balloons [1.5 cm (L)×0.3 cm (D), 1.41 cm2] were treated with 1 ml of 0.1% gelatin (A, 300) in 25 mM HAc-NaAc/25 mM Na2SO4 buffer (pH 5.0) at RT for 2 hours. The balloons were washed three times with 25 mM HAc-NaAc/25 mM Na2SO4 buffer (pH 5.0) and then treated with 1 ml of adenovirus (1.6×109 pfu/ml or 4×10 vp/ml containing a small amount of 125I -labeled adenovirus) in 25 mM HAc-NaAc/25 mM Na2SO4 buffer (pH 5.0) at RT for 2 minutes. The balloons were washed once with 1 ml of 25 mM HAc-NaAc/25 mM Na2SO4 buffer (pH 5.0) and then treated with 1 ml of 0.1% gelatin (A, 300) in 25 mM HAc-NaAc/25 mM Na2SO4 buffer (pH 5.0) at RT for 2 minutes. The balloons were washed once with 1 ml of 25 mM HAc-NaAc/25 mM Na2SO4 buffer (pH 5.0) and then treated again with 1 ml of adenovirus (1.6×109 pfu/ml or 4×1010 vp/ml) containing a small amount of 125I-labeled adenovirus in 25 mM HAc-NaAc/25 mM Na2SO4 buffer (pH 5.0) at RT for 2 minutes. The preceding two steps were repeated until ten adenovirus layers were adsorbed. The balloons were washed once with 1 ml of 25 mM HAc-NaAc/25 mM Na2SO4 buffer (pH 5.0) and dipped in 1 ml of 10% serum culture medium for 60 min. The amount of adenovirus was determined by comparing the amount of radioactivity of 125I (10 ml of counting medium was used for each sample, Count 1 minute). The result of this experiment is shown in Table 5, above.
  • EXAMPLE 11 In Vivo Delivery of DNA to Heart
  • To stimulate angiogenesis or collateral blood flow in the adult rat heart, a balloon catheter, is coated with 40 layers of a DNA encoding human fibroblast growth factor-5 (hFGF-5) and is inserted into a blood vessel that perfuses the heart. Rats have been sacrificed at 3 weeks following injection and capillary density was measured by computerized light microscopy. The results have shown that a direct injection of a fibroblast growth factor -5 expression vector stimulates collateral vessel formation in areas of injected myocardium.

Claims (18)

1-46. (canceled)
47. A method of treating or preventing the course of a disease or tissue dysfunction comprising:
providing a medical device comprising:
an inner layer of a cationic polyelectrolyte carrier;
a layer of a negatively charged therapeutic agent adsorbed onto said inner layer of a cationic polyelectrolyte carrier; and
an additional layer of a cationic polyelectrolyte carrier and an additional layer of a negatively charged therapeutic agent adsorbed onto said additional layer of said cationic polyelectrolyte carrier, wherein said additional layer of a cationic polyelectrolyte carrier and said additional layer of a negatively charged therapeutic agent alternate;
implanting the medical device into a target location from which the negatively charged therapeutic agent can treat or prevent the course of the disease or tissue dysfunction.
48. The method of claim 47, wherein treating or preventing tissue dysfunction comprises inhibiting angiogenesis.
49. The method of claim 48, wherein treating or preventing tissue dysfunction comprises inducing angiogenesis.
50. The method of claim 49, wherein treating or preventing the course of a disease or tissue dysfunction comprises treating or preventing restenosis; cardiomyopathy or other dysfunction of the heart; or cystic fibrosis or other dysfunction of the lung.
51. The method of claim 47, wherein treating or preventing the course of a disease or tissue dysfunction comprises treating or inhibiting malignant cell proliferation.
52. The method of claim 47, wherein treating or preventing the course of a disease or tissue dysfunction comprises inducing nerve, blood vessel, or tissue regeneration in a tissue.
53. The method of claim 47, wherein the medical device is used in angioplasty.
54. The method of claim 47, wherein the medical device further comprises an outermost layer of a cationic polyelectrolyte carrier which is the same or different from the inner or the additional layer of a cationic polyelectrolyte carrier.
55. The method of claim 47, wherein the inner or the additional layer of a cationic polyelectrolyte carrier comprises human serum albumin, gelatin, chitosan, or a combination thereof.
56. The method of claim 47, wherein the medical device is a stent or a catheter.
57. The method of claim 56, wherein the catheter is a balloon catheter.
58. The method of claim 47, wherein the negatively charged therapeutic agent is rapamycin or paclitaxel.
59. The method of claim 47, wherein the negatively charged therapeutic agent comprises more than one negatively charged therapeutic agent.
60. The method of claim 47, wherein the negatively charged therapeutic agent is selected from the group consisting of a: anti-thrombogenic protein, antioxidant compound, angiogenic protein, agent which blocks smooth muscle cell proliferation, anti-inflammatory agent, calcium entry blocker, antineoplastic/antiproliferative/anti-mitotic compound, anti-microbial compound, anesthetic agent, nitric oxide donor, anti-coagulant, vascular cell growth promoting protein, vascular cell growth protein inhibitor, vascular cell growth antibody inhibitor, cholesterol lowering drug, vasodilating drug, protein that protects against cell death, cell cycle CDK protein inhibitor, anti-restenosis protein, agent for treating malignancies, bone morphogenic protein, a polynucleotide encoding any of the above named proteins or protein inhibitors, and a vector comprising a polynucleotide encoding any of the above named proteins or protein inhibitors.
61. A method of delivering a therapeutic agent to a target location comprising
providing a medical device comprising:
an inner layer of a cationic polyelectrolyte carrier;
a layer of a negatively charged therapeutic agent adsorbed onto said inner layer of a cationic polyelectrolyte carrier; and
an additional layer of a cationic polyelectrolyte carrier and an additional layer of a negatively charged therapeutic agent adsorbed onto said additional layer of said cationic polyelectrolyte carrier, wherein said additional layer of a cationic polyelectrolyte carrier and said additional layer of a negatively charged therapeutic agent alternate;
implanting the medical device into a target location to deliver the negatively charged therapeutic agent to the target location.
62. The method of claim 61, wherein the target location is a brain, heart, liver, skeletal muscle, smooth muscle, kidney, bladder, intestine, stomach, pancreas, ovary, prostate, cartilage, bone, lung, blood vessel, ureter, urethra, or testes.
63. The method of claim 61, wherein the at least one negatively charged therapeutic agent is selected from the group consisting of a: anti-thrombogenic protein, antioxidant compound, angiogenic protein, agent which blocks smooth muscle cell proliferation, anti-inflammatory agent, calcium entry blocker, antineoplastic/antiproliferative/anti-mitotic compound, anti-microbial compound, anesthetic agent, nitric oxide donor, anti-coagulant, vascular cell growth promoting protein, vascular cell growth protein inhibitor, vascular cell growth antibody inhibitor, cholesterol lowering drug, vasodilating drug, protein that protects against cell death, cell cycle CDK protein inhibitor, anti-restenosis protein, agent for treating malignancies, bone morphogenic protein, a polynucleotide encoding any of the above named proteins or protein inhibitors, and a vector comprising a polynucleotide encoding any of the above named proteins or protein inhibitors.
US11/060,383 1999-12-30 2005-02-17 Controlled delivery of therapeutic agents by insertable medical devices Abandoned US20050169969A1 (en)

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Cited By (36)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20080195079A1 (en) * 2007-02-07 2008-08-14 Cook Incorporated Medical device coatings for releasing a therapeutic agent at multiple rates
US20080208315A1 (en) * 2007-02-27 2008-08-28 National Taiwan University Of Science & Technology Coronary stent having a surface of multi-layer immobilized structures
US20100087783A1 (en) * 2008-10-07 2010-04-08 Boston Scientific Scimed, Inc. Medical devices for delivery of therapeutic agents to body lumens
US7955382B2 (en) 2006-09-15 2011-06-07 Boston Scientific Scimed, Inc. Endoprosthesis with adjustable surface features
US7985252B2 (en) 2008-07-30 2011-07-26 Boston Scientific Scimed, Inc. Bioerodible endoprosthesis
US7998192B2 (en) 2008-05-09 2011-08-16 Boston Scientific Scimed, Inc. Endoprostheses
US8002821B2 (en) 2006-09-18 2011-08-23 Boston Scientific Scimed, Inc. Bioerodible metallic ENDOPROSTHESES
US8048150B2 (en) 2006-04-12 2011-11-01 Boston Scientific Scimed, Inc. Endoprosthesis having a fiber meshwork disposed thereon
US8052744B2 (en) 2006-09-15 2011-11-08 Boston Scientific Scimed, Inc. Medical devices and methods of making the same
US8052745B2 (en) 2007-09-13 2011-11-08 Boston Scientific Scimed, Inc. Endoprosthesis
US8052743B2 (en) 2006-08-02 2011-11-08 Boston Scientific Scimed, Inc. Endoprosthesis with three-dimensional disintegration control
US8057534B2 (en) 2006-09-15 2011-11-15 Boston Scientific Scimed, Inc. Bioerodible endoprostheses and methods of making the same
US8080055B2 (en) 2006-12-28 2011-12-20 Boston Scientific Scimed, Inc. Bioerodible endoprostheses and methods of making the same
US8089029B2 (en) 2006-02-01 2012-01-03 Boston Scientific Scimed, Inc. Bioabsorbable metal medical device and method of manufacture
US8128689B2 (en) 2006-09-15 2012-03-06 Boston Scientific Scimed, Inc. Bioerodible endoprosthesis with biostable inorganic layers
US8133553B2 (en) 2007-06-18 2012-03-13 Zimmer, Inc. Process for forming a ceramic layer
US8236046B2 (en) 2008-06-10 2012-08-07 Boston Scientific Scimed, Inc. Bioerodible endoprosthesis
US8267992B2 (en) 2009-03-02 2012-09-18 Boston Scientific Scimed, Inc. Self-buffering medical implants
US8303643B2 (en) 2001-06-27 2012-11-06 Remon Medical Technologies Ltd. Method and device for electrochemical formation of therapeutic species in vivo
US8309521B2 (en) 2007-06-19 2012-11-13 Zimmer, Inc. Spacer with a coating thereon for use with an implant device
US8382824B2 (en) 2008-10-03 2013-02-26 Boston Scientific Scimed, Inc. Medical implant having NANO-crystal grains with barrier layers of metal nitrides or fluorides
US8449901B2 (en) 2003-03-28 2013-05-28 Innovational Holdings, Llc Implantable medical device with beneficial agent concentration gradient
US8597720B2 (en) 2007-01-21 2013-12-03 Hemoteq Ag Medical product for treating stenosis of body passages and for preventing threatening restenosis
US8602290B2 (en) 2007-10-10 2013-12-10 Zimmer, Inc. Method for bonding a tantalum structure to a cobalt-alloy substrate
US8668732B2 (en) 2010-03-23 2014-03-11 Boston Scientific Scimed, Inc. Surface treated bioerodible metal endoprostheses
US8669360B2 (en) 2011-08-05 2014-03-11 Boston Scientific Scimed, Inc. Methods of converting amorphous drug substance into crystalline form
US8808726B2 (en) 2006-09-15 2014-08-19 Boston Scientific Scimed. Inc. Bioerodible endoprostheses and methods of making the same
US8840660B2 (en) 2006-01-05 2014-09-23 Boston Scientific Scimed, Inc. Bioerodible endoprostheses and methods of making the same
US8889211B2 (en) 2010-09-02 2014-11-18 Boston Scientific Scimed, Inc. Coating process for drug delivery balloons using heat-induced rewrap memory
US9056152B2 (en) 2011-08-25 2015-06-16 Boston Scientific Scimed, Inc. Medical device with crystalline drug coating
US9192697B2 (en) 2007-07-03 2015-11-24 Hemoteq Ag Balloon catheter for treating stenosis of body passages and for preventing threatening restenosis
WO2016154050A1 (en) * 2015-03-20 2016-09-29 The Trustees Of Dartmouth College System and methods for enhancing uptake of therapeutic agent from bloodstream into disease site
US10010400B2 (en) 2015-03-30 2018-07-03 Taris Biomedical Llc Devices and methods for local delivery of drug to upper urinary tract
US10080821B2 (en) 2009-07-17 2018-09-25 Boston Scientific Scimed, Inc. Nucleation of drug delivery balloons to provide improved crystal size and density
US10094836B2 (en) 2007-01-08 2018-10-09 The United States Of America, As Represented By The Secretary, Department Of Health & Human Services SLCO1B3 genotype
US10369256B2 (en) 2009-07-10 2019-08-06 Boston Scientific Scimed, Inc. Use of nanocrystals for drug delivery from a balloon

Families Citing this family (172)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20030153985A1 (en) * 1997-04-26 2003-08-14 Lee Yong Chan Medical implant
US6890546B2 (en) 1998-09-24 2005-05-10 Abbott Laboratories Medical devices containing rapamycin analogs
US20030129215A1 (en) * 1998-09-24 2003-07-10 T-Ram, Inc. Medical devices containing rapamycin analogs
US7637948B2 (en) 1997-10-10 2009-12-29 Senorx, Inc. Tissue marking implant
US8668737B2 (en) 1997-10-10 2014-03-11 Senorx, Inc. Tissue marking implant
US7208010B2 (en) 2000-10-16 2007-04-24 Conor Medsystems, Inc. Expandable medical device for delivery of beneficial agent
US20040254635A1 (en) 1998-03-30 2004-12-16 Shanley John F. Expandable medical device for delivery of beneficial agent
US6241762B1 (en) 1998-03-30 2001-06-05 Conor Medsystems, Inc. Expandable medical device with ductile hinges
US8029561B1 (en) * 2000-05-12 2011-10-04 Cordis Corporation Drug combination useful for prevention of restenosis
US9820824B2 (en) 1999-02-02 2017-11-21 Senorx, Inc. Deployment of polysaccharide markers for treating a site within a patent
US7983734B2 (en) 2003-05-23 2011-07-19 Senorx, Inc. Fibrous marker and intracorporeal delivery thereof
US7651505B2 (en) 2002-06-17 2010-01-26 Senorx, Inc. Plugged tip delivery for marker placement
US6725083B1 (en) 1999-02-02 2004-04-20 Senorx, Inc. Tissue site markers for in VIVO imaging
US20090030309A1 (en) 2007-07-26 2009-01-29 Senorx, Inc. Deployment of polysaccharide markers
US8361082B2 (en) 1999-02-02 2013-01-29 Senorx, Inc. Marker delivery device with releasable plug
US6862470B2 (en) 1999-02-02 2005-03-01 Senorx, Inc. Cavity-filling biopsy site markers
US8498693B2 (en) 1999-02-02 2013-07-30 Senorx, Inc. Intracorporeal marker and marker delivery device
US6575991B1 (en) 1999-06-17 2003-06-10 Inrad, Inc. Apparatus for the percutaneous marking of a lesion
US20030070676A1 (en) * 1999-08-05 2003-04-17 Cooper Joel D. Conduits having distal cage structure for maintaining collateral channels in tissue and related methods
US20070032853A1 (en) 2002-03-27 2007-02-08 Hossainy Syed F 40-O-(2-hydroxy)ethyl-rapamycin coated stent
US7807211B2 (en) 1999-09-03 2010-10-05 Advanced Cardiovascular Systems, Inc. Thermal treatment of an implantable medical device
US7419678B2 (en) * 2000-05-12 2008-09-02 Cordis Corporation Coated medical devices for the prevention and treatment of vascular disease
US8236048B2 (en) 2000-05-12 2012-08-07 Cordis Corporation Drug/drug delivery systems for the prevention and treatment of vascular disease
US6776796B2 (en) 2000-05-12 2004-08-17 Cordis Corportation Antiinflammatory drug and delivery device
US20050002986A1 (en) * 2000-05-12 2005-01-06 Robert Falotico Drug/drug delivery systems for the prevention and treatment of vascular disease
US6953560B1 (en) 2000-09-28 2005-10-11 Advanced Cardiovascular Systems, Inc. Barriers for polymer-coated implantable medical devices and methods for making the same
US8303609B2 (en) 2000-09-29 2012-11-06 Cordis Corporation Coated medical devices
DK1328213T3 (en) 2000-10-16 2005-11-28 Conor Medsystems Inc Expandable medical device for delivery of a useful agent
WO2002041786A2 (en) 2000-11-20 2002-05-30 Senorx, Inc. Tissue site markers for in vivo imaging
US6812217B2 (en) * 2000-12-04 2004-11-02 Medtronic, Inc. Medical device and methods of use
US20040073294A1 (en) 2002-09-20 2004-04-15 Conor Medsystems, Inc. Method and apparatus for loading a beneficial agent into an expandable medical device
AU2016206379B2 (en) * 2001-02-19 2017-09-14 Novartis Ag Cancer Treatment
EP2269604B1 (en) 2001-02-19 2016-07-27 Novartis AG Treatment of solid kidney tumours with a rapamycin derivative
AU2011226833B9 (en) * 2001-02-19 2014-07-03 Novartis Ag Cancer treatment
DE10115740A1 (en) * 2001-03-26 2002-10-02 Ulrich Speck Preparation for restenosis prophylaxis
US7862495B2 (en) * 2001-05-31 2011-01-04 Advanced Cardiovascular Systems, Inc. Radiation or drug delivery source with activity gradient to minimize edge effects
US8741378B1 (en) 2001-06-27 2014-06-03 Advanced Cardiovascular Systems, Inc. Methods of coating an implantable device
US6656216B1 (en) * 2001-06-29 2003-12-02 Advanced Cardiovascular Systems, Inc. Composite stent with regioselective material
US7682669B1 (en) 2001-07-30 2010-03-23 Advanced Cardiovascular Systems, Inc. Methods for covalently immobilizing anti-thrombogenic material into a coating on a medical device
US7708712B2 (en) 2001-09-04 2010-05-04 Broncus Technologies, Inc. Methods and devices for maintaining patency of surgically created channels in a body organ
US20030093147A1 (en) * 2001-11-13 2003-05-15 Ogle Matthew F. Medical devices that stimulate growth factor production
CA2467239A1 (en) * 2001-11-14 2003-05-22 Alza Corporation Catheter injectable depot compositions and uses thereof
US20070196415A1 (en) * 2002-11-14 2007-08-23 Guohua Chen Depot compositions with multiple drug release rate controls and uses thereof
EA011488B1 (en) 2002-02-01 2009-04-28 Ариад Джин Терапьютикс, Инк. Phosphorus-containing compounds & uses thereof
AR038926A1 (en) 2002-03-13 2005-02-02 Novartis Ag MATERIALS WITH MULTIPLE VESICLE LAYER CONTENT
US8506617B1 (en) 2002-06-21 2013-08-13 Advanced Cardiovascular Systems, Inc. Micronized peptide coated stent
US20040001889A1 (en) 2002-06-25 2004-01-01 Guohua Chen Short duration depot formulations
CA2494342A1 (en) * 2002-07-31 2004-02-12 Alza Corporation Injectable depot compositions and uses thereof
CN101057824A (en) * 2002-07-31 2007-10-24 阿尔萨公司 Injectable multimodal polymer depot compositions and uses thereof
DE10244847A1 (en) 2002-09-20 2004-04-01 Ulrich Prof. Dr. Speck Medical device for drug delivery
US20060036158A1 (en) 2003-11-17 2006-02-16 Inrad, Inc. Self-contained, self-piercing, side-expelling marking apparatus
US7776926B1 (en) 2002-12-11 2010-08-17 Advanced Cardiovascular Systems, Inc. Biocompatible coating for implantable medical devices
US7758880B2 (en) 2002-12-11 2010-07-20 Advanced Cardiovascular Systems, Inc. Biocompatible polyacrylate compositions for medical applications
US20060002968A1 (en) 2004-06-30 2006-01-05 Gordon Stewart Anti-proliferative and anti-inflammatory agent combination for treatment of vascular disorders
US7758881B2 (en) 2004-06-30 2010-07-20 Advanced Cardiovascular Systems, Inc. Anti-proliferative and anti-inflammatory agent combination for treatment of vascular disorders with an implantable medical device
US8435550B2 (en) 2002-12-16 2013-05-07 Abbot Cardiovascular Systems Inc. Anti-proliferative and anti-inflammatory agent combination for treatment of vascular disorders with an implantable medical device
KR20050119665A (en) * 2003-03-28 2005-12-21 코산 바이오사이언시즈, 인코포레이티드 Devices, methods, and compositions to prevent restenosis
US20080215137A1 (en) * 2003-04-30 2008-09-04 Boston Scientific Scimed, Inc. Therapeutic driving layer for a medical device
US7279174B2 (en) 2003-05-08 2007-10-09 Advanced Cardiovascular Systems, Inc. Stent coatings comprising hydrophilic additives
US7877133B2 (en) 2003-05-23 2011-01-25 Senorx, Inc. Marker or filler forming fluid
US20050118344A1 (en) 2003-12-01 2005-06-02 Pacetti Stephen D. Temperature controlled crimping
US8308682B2 (en) 2003-07-18 2012-11-13 Broncus Medical Inc. Devices for maintaining patency of surgically created channels in tissue
US20050037048A1 (en) * 2003-08-11 2005-02-17 Young-Ho Song Medical devices containing antioxidant and therapeutic agent
US7785653B2 (en) 2003-09-22 2010-08-31 Innovational Holdings Llc Method and apparatus for loading a beneficial agent into an expandable medical device
US7198675B2 (en) 2003-09-30 2007-04-03 Advanced Cardiovascular Systems Stent mandrel fixture and method for selectively coating surfaces of a stent
WO2005039664A2 (en) * 2003-10-14 2005-05-06 Cube Medical A/S Medical device with electrospun nanofibers
US9278015B2 (en) * 2003-10-16 2016-03-08 Minvasys Catheter system for stenting and drug treatment of bifurcated vessels
US20050273002A1 (en) 2004-06-04 2005-12-08 Goosen Ryan L Multi-mode imaging marker
US9114198B2 (en) 2003-11-19 2015-08-25 Advanced Cardiovascular Systems, Inc. Biologically beneficial coatings for implantable devices containing fluorinated polymers and methods for fabricating the same
DE10355511A1 (en) * 2003-11-24 2005-06-09 Biotronik Gmbh & Co. Kg Endovascular implant with an active coating
US7744644B2 (en) * 2004-03-19 2010-06-29 Boston Scientific Scimed, Inc. Medical articles having regions with polyelectrolyte multilayer coatings for regulating drug release
JP2007534389A (en) * 2004-04-29 2007-11-29 キューブ・メディカル・アクティーゼルスカブ Balloon used for angiogenesis
US8293890B2 (en) 2004-04-30 2012-10-23 Advanced Cardiovascular Systems, Inc. Hyaluronic acid based copolymers
US7758892B1 (en) * 2004-05-20 2010-07-20 Boston Scientific Scimed, Inc. Medical devices having multiple layers
JP5026970B2 (en) * 2004-05-20 2012-09-19 ボストン サイエンティフィック リミテッド Medical device and method of making the same
US9561309B2 (en) 2004-05-27 2017-02-07 Advanced Cardiovascular Systems, Inc. Antifouling heparin coatings
US7563780B1 (en) 2004-06-18 2009-07-21 Advanced Cardiovascular Systems, Inc. Heparin prodrugs and drug delivery stents formed therefrom
US8709469B2 (en) 2004-06-30 2014-04-29 Abbott Cardiovascular Systems Inc. Anti-proliferative and anti-inflammatory agent combination for treatment of vascular disorders with an implantable medical device
US8409167B2 (en) 2004-07-19 2013-04-02 Broncus Medical Inc Devices for delivering substances through an extra-anatomic opening created in an airway
US7494665B1 (en) 2004-07-30 2009-02-24 Advanced Cardiovascular Systems, Inc. Polymers containing siloxane monomers
US7648727B2 (en) 2004-08-26 2010-01-19 Advanced Cardiovascular Systems, Inc. Methods for manufacturing a coated stent-balloon assembly
US8603634B2 (en) 2004-10-27 2013-12-10 Abbott Cardiovascular Systems Inc. End-capped poly(ester amide) copolymers
US8419656B2 (en) 2004-11-22 2013-04-16 Bard Peripheral Vascular, Inc. Post decompression marker introducer system
US7604818B2 (en) 2004-12-22 2009-10-20 Advanced Cardiovascular Systems, Inc. Polymers of fluorinated monomers and hydrocarbon monomers
US20060142234A1 (en) * 2004-12-23 2006-06-29 Guohua Chen Injectable non-aqueous suspension
US20060212106A1 (en) * 2005-03-21 2006-09-21 Jan Weber Coatings for use on medical devices
US10357328B2 (en) 2005-04-20 2019-07-23 Bard Peripheral Vascular, Inc. and Bard Shannon Limited Marking device with retractable cannula
US7795467B1 (en) 2005-04-26 2010-09-14 Advanced Cardiovascular Systems, Inc. Bioabsorbable, biobeneficial polyurethanes for use in medical devices
US8778375B2 (en) 2005-04-29 2014-07-15 Advanced Cardiovascular Systems, Inc. Amorphous poly(D,L-lactide) coating
US8021676B2 (en) 2005-07-08 2011-09-20 Advanced Cardiovascular Systems, Inc. Functionalized chemically inert polymers for coatings
US7785647B2 (en) 2005-07-25 2010-08-31 Advanced Cardiovascular Systems, Inc. Methods of providing antioxidants to a drug containing product
US20070067882A1 (en) * 2005-09-21 2007-03-22 Liliana Atanasoska Internal medical devices having polyelectrolyte-containing extruded regions
CA2562580C (en) 2005-10-07 2014-04-29 Inrad, Inc. Drug-eluting tissue marker
US20070110786A1 (en) * 2005-11-15 2007-05-17 Boston Scientific Scimed, Inc. Medical articles having enhanced therapeutic agent binding
US7976891B1 (en) 2005-12-16 2011-07-12 Advanced Cardiovascular Systems, Inc. Abluminal stent coating apparatus and method of using focused acoustic energy
US7867547B2 (en) 2005-12-19 2011-01-11 Advanced Cardiovascular Systems, Inc. Selectively coating luminal surfaces of stents
US20070154466A1 (en) * 2005-12-30 2007-07-05 Jan Weber Internal medical devices containing peroxide-converting catalysts
US8834912B2 (en) * 2005-12-30 2014-09-16 Boston Scientific Scimed, Inc. Medical devices having multiple charged layers
US20070196428A1 (en) 2006-02-17 2007-08-23 Thierry Glauser Nitric oxide generating medical devices
US7713637B2 (en) 2006-03-03 2010-05-11 Advanced Cardiovascular Systems, Inc. Coating containing PEGylated hyaluronic acid and a PEGylated non-hyaluronic acid polymer
EP1832289A3 (en) * 2006-03-08 2007-12-12 Sahajanand Medical Technologies PVT. ltd Compositions and coatings for implantable medical devices
DE102006016598A1 (en) * 2006-04-06 2007-11-15 Heraeus Kulzer Gmbh Coated vascular implants
US20070254003A1 (en) * 2006-05-01 2007-11-01 Pu Zhou Non-sticky coatings with therapeutic agents for medical devices
US20070259116A1 (en) * 2006-05-02 2007-11-08 Boston Scientific Scimed, Inc. Partially coated workpiece and method of making same
US8003156B2 (en) 2006-05-04 2011-08-23 Advanced Cardiovascular Systems, Inc. Rotatable support elements for stents
US7985441B1 (en) 2006-05-04 2011-07-26 Yiwen Tang Purification of polymers for coating applications
US8304012B2 (en) 2006-05-04 2012-11-06 Advanced Cardiovascular Systems, Inc. Method for drying a stent
US7775178B2 (en) 2006-05-26 2010-08-17 Advanced Cardiovascular Systems, Inc. Stent coating apparatus and method
US8568764B2 (en) 2006-05-31 2013-10-29 Advanced Cardiovascular Systems, Inc. Methods of forming coating layers for medical devices utilizing flash vaporization
US9561351B2 (en) 2006-05-31 2017-02-07 Advanced Cardiovascular Systems, Inc. Drug delivery spiral coil construct
US8703167B2 (en) 2006-06-05 2014-04-22 Advanced Cardiovascular Systems, Inc. Coatings for implantable medical devices for controlled release of a hydrophilic drug and a hydrophobic drug
US8778376B2 (en) 2006-06-09 2014-07-15 Advanced Cardiovascular Systems, Inc. Copolymer comprising elastin pentapeptide block and hydrophilic block, and medical device and method of treating
US8603530B2 (en) 2006-06-14 2013-12-10 Abbott Cardiovascular Systems Inc. Nanoshell therapy
US8114150B2 (en) 2006-06-14 2012-02-14 Advanced Cardiovascular Systems, Inc. RGD peptide attached to bioabsorbable stents
US8048448B2 (en) 2006-06-15 2011-11-01 Abbott Cardiovascular Systems Inc. Nanoshells for drug delivery
US8017237B2 (en) 2006-06-23 2011-09-13 Abbott Cardiovascular Systems, Inc. Nanoshells on polymers
US9028859B2 (en) 2006-07-07 2015-05-12 Advanced Cardiovascular Systems, Inc. Phase-separated block copolymer coatings for implantable medical devices
US8703169B1 (en) 2006-08-15 2014-04-22 Abbott Cardiovascular Systems Inc. Implantable device having a coating comprising carrageenan and a biostable polymer
US20080213334A1 (en) * 2006-09-29 2008-09-04 Lockwood Nathan A Polyelectrolyte media for bioactive agent delivery
ES2443526T3 (en) 2006-10-23 2014-02-19 C.R. Bard, Inc. Breast marker
US20080276935A1 (en) 2006-11-20 2008-11-13 Lixiao Wang Treatment of asthma and chronic obstructive pulmonary disease with anti-proliferate and anti-inflammatory drugs
US8998846B2 (en) 2006-11-20 2015-04-07 Lutonix, Inc. Drug releasing coatings for balloon catheters
US8414525B2 (en) 2006-11-20 2013-04-09 Lutonix, Inc. Drug releasing coatings for medical devices
US9737640B2 (en) 2006-11-20 2017-08-22 Lutonix, Inc. Drug releasing coatings for medical devices
US20080175887A1 (en) 2006-11-20 2008-07-24 Lixiao Wang Treatment of Asthma and Chronic Obstructive Pulmonary Disease With Anti-proliferate and Anti-inflammatory Drugs
US8425459B2 (en) 2006-11-20 2013-04-23 Lutonix, Inc. Medical device rapid drug releasing coatings comprising a therapeutic agent and a contrast agent
US8430055B2 (en) 2008-08-29 2013-04-30 Lutonix, Inc. Methods and apparatuses for coating balloon catheters
US8414910B2 (en) 2006-11-20 2013-04-09 Lutonix, Inc. Drug releasing coatings for medical devices
US8414526B2 (en) 2006-11-20 2013-04-09 Lutonix, Inc. Medical device rapid drug releasing coatings comprising oils, fatty acids, and/or lipids
US9700704B2 (en) 2006-11-20 2017-07-11 Lutonix, Inc. Drug releasing coatings for balloon catheters
WO2008073965A2 (en) 2006-12-12 2008-06-19 C.R. Bard Inc. Multiple imaging mode tissue marker
US8597673B2 (en) 2006-12-13 2013-12-03 Advanced Cardiovascular Systems, Inc. Coating of fast absorption or dissolution
WO2008076973A2 (en) 2006-12-18 2008-06-26 C.R.Bard Inc. Biopsy marker with in situ-generated imaging properties
JP2010512947A (en) * 2006-12-20 2010-04-30 ボストン サイエンティフィック リミテッド Stent with coating for delivering therapeutic agent
US8728170B1 (en) 2006-12-28 2014-05-20 Boston Scientific Scimed, Inc. Bioerodible nano-fibrous and nano-porous conductive composites
US8114466B2 (en) * 2007-01-03 2012-02-14 Boston Scientific Scimed, Inc. Methods of applying coating to the inside surface of a stent
US8147769B1 (en) 2007-05-16 2012-04-03 Abbott Cardiovascular Systems Inc. Stent and delivery system with reduced chemical degradation
US9056155B1 (en) 2007-05-29 2015-06-16 Abbott Cardiovascular Systems Inc. Coatings having an elastic primer layer
US8048441B2 (en) 2007-06-25 2011-11-01 Abbott Cardiovascular Systems, Inc. Nanobead releasing medical devices
US8109904B1 (en) 2007-06-25 2012-02-07 Abbott Cardiovascular Systems Inc. Drug delivery medical devices
US9216101B2 (en) * 2007-07-10 2015-12-22 Boston Scientific Scime, Inc. Dual taper stent protector
US20090018635A1 (en) * 2007-07-10 2009-01-15 Boston Scientific Scimed, Inc. Stent protector
US20090018633A1 (en) * 2007-07-10 2009-01-15 Boston Scientific Scimed, Inc. Protector for an insertable or implantable medical device
US8613721B2 (en) * 2007-11-14 2013-12-24 Medrad, Inc. Delivery and administration of compositions using interventional catheters
US8551072B2 (en) * 2007-12-12 2013-10-08 Boston Scientific Scimed, Inc. Methods, devices and compositions for controlled drug delivery to injured myocardium
WO2009099767A2 (en) 2008-01-31 2009-08-13 C.R. Bard, Inc. Biopsy tissue marker
US8252048B2 (en) * 2008-03-19 2012-08-28 Boston Scientific Scimed, Inc. Drug eluting stent and method of making the same
US8771332B2 (en) * 2008-05-29 2014-07-08 Boston Scientific Scimed, Inc. Multi-layer balloon design for use in combination with catheter assemblies, and methods of making the same
US9327061B2 (en) 2008-09-23 2016-05-03 Senorx, Inc. Porous bioabsorbable implant
US8049061B2 (en) 2008-09-25 2011-11-01 Abbott Cardiovascular Systems, Inc. Expandable member formed of a fibrous matrix having hydrogel polymer for intraluminal drug delivery
US8226603B2 (en) 2008-09-25 2012-07-24 Abbott Cardiovascular Systems Inc. Expandable member having a covering formed of a fibrous matrix for intraluminal drug delivery
US8076529B2 (en) 2008-09-26 2011-12-13 Abbott Cardiovascular Systems, Inc. Expandable member formed of a fibrous matrix for intraluminal drug delivery
US9149376B2 (en) 2008-10-06 2015-10-06 Cordis Corporation Reconstrainable stent delivery system
JP5453453B2 (en) 2008-12-30 2014-03-26 シー・アール・バード・インコーポレーテッド Marker transmission device for placement of tissue markers
US8591494B2 (en) * 2009-06-10 2013-11-26 Boston Scientific Scimed, Inc. Electrochemical therapeutic agent delivery device
WO2011022623A2 (en) * 2009-08-21 2011-02-24 Boston Scientific Scimed, Inc. Medical devices containing therapeutic agents
EP2528537A4 (en) * 2010-01-27 2016-09-07 Vascular Therapies Inc Device and method for preventing stenosis at an anastomosis site
WO2011119536A1 (en) 2010-03-22 2011-09-29 Abbott Cardiovascular Systems Inc. Stent delivery system having a fibrous matrix covering with improved stent retention
US8685433B2 (en) 2010-03-31 2014-04-01 Abbott Cardiovascular Systems Inc. Absorbable coating for implantable device
US8709034B2 (en) 2011-05-13 2014-04-29 Broncus Medical Inc. Methods and devices for diagnosing, monitoring, or treating medical conditions through an opening through an airway wall
US9345532B2 (en) 2011-05-13 2016-05-24 Broncus Medical Inc. Methods and devices for ablation of tissue
WO2013078235A1 (en) 2011-11-23 2013-05-30 Broncus Medical Inc Methods and devices for diagnosing, monitoring, or treating medical conditions through an opening through an airway wall
US20140308236A1 (en) * 2013-01-08 2014-10-16 Technion Research And Development Foundation Ltd. Antimicrobial composition and uses thereof
US20140272232A1 (en) * 2013-03-15 2014-09-18 Bard Access Systems, Inc. Antithrombic coatings and uses thereof
USD716450S1 (en) 2013-09-24 2014-10-28 C. R. Bard, Inc. Tissue marker for intracorporeal site identification
USD715442S1 (en) 2013-09-24 2014-10-14 C. R. Bard, Inc. Tissue marker for intracorporeal site identification
USD716451S1 (en) 2013-09-24 2014-10-28 C. R. Bard, Inc. Tissue marker for intracorporeal site identification
USD715942S1 (en) 2013-09-24 2014-10-21 C. R. Bard, Inc. Tissue marker for intracorporeal site identification
US20160303242A1 (en) 2013-12-09 2016-10-20 Durect Corporation Pharmaceutically Active Agent Complexes, Polymer Complexes, and Compositions and Methods Involving the Same
WO2015100238A1 (en) * 2013-12-27 2015-07-02 Neograft Technologies, Inc. Artificial graft devices and related systems and methods
KR20220140711A (en) 2020-01-13 2022-10-18 듀렉트 코퍼레이션 Reduced Impurity Sustained Release Drug Delivery Systems and Related Methods
CN114159556B (en) * 2021-12-14 2023-06-16 中国人民解放军军事科学院军事医学研究院 Protein nano delivery carrier for enhancing immunity of adenovirus carrier vaccine

Citations (15)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3127448A (en) * 1960-09-21 1964-03-31 Metal Hydrides Inc Method for preparing tertiary amine boranes
US5075112A (en) * 1990-02-12 1991-12-24 Cartilage Technologies Inc. Method of and dosage unit for inhibiting angiogenesis or vascularization in an animal using shark cartilage
US5516781A (en) * 1992-01-09 1996-05-14 American Home Products Corporation Method of treating restenosis with rapamycin
US5578073A (en) * 1994-09-16 1996-11-26 Ramot Of Tel Aviv University Thromboresistant surface treatment for biomaterials
US5634895A (en) * 1994-06-23 1997-06-03 Cormedics Corp. Apparatus and method for transpericardial delivery of fluid
US5652225A (en) * 1994-10-04 1997-07-29 St. Elizabeth's Medical Center Of Boston, Inc. Methods and products for nucleic acid delivery
US5854205A (en) * 1995-10-23 1998-12-29 The Children's Medical Center Corporation Therapeutic antiangiogenic compositions and methods
US6004943A (en) * 1995-11-27 1999-12-21 Inst. Of Biomedical Engineering, Chinese Acdmy Of Med. Science Protein-coated medical substrates for local delivery of genes and method of forming coatings on the substrates
US6013780A (en) * 1996-09-06 2000-01-11 Technion Research & Development Co. Ltd. VEGF145 expression vectors
US6099562A (en) * 1996-06-13 2000-08-08 Schneider (Usa) Inc. Drug coating with topcoat
US6299604B1 (en) * 1998-08-20 2001-10-09 Cook Incorporated Coated implantable medical device
US20020028243A1 (en) * 1998-09-25 2002-03-07 Masters David B. Protein matrix materials, devices and methods of making and using thereof
US6468304B1 (en) * 1997-07-16 2002-10-22 Centre National De La Recherche Scientifique Implantable device covered with polymer capable of releasing biologically active substances
US6589546B2 (en) * 1998-08-28 2003-07-08 Scimed Life Systems, Inc. Polymeric coatings for controlled delivery of active agents
US6740736B2 (en) * 1998-09-24 2004-05-25 Ppl Therapeutics (Scotland) Limited Purification of fibrinogen from milk by use of cation exchange chromatography

Family Cites Families (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
AU8782098A (en) 1997-08-13 1999-03-08 Boston Scientific Limited Loading and release of water-insoluble drugs
IL122153A (en) * 1997-11-10 2005-03-20 Alomone Labs Ltd Biocompatible polymeric coating material
DE19806989A1 (en) 1998-02-19 1999-08-26 Roche Diagnostics Gmbh Generation of spatially sharply defined solid phases for binding assays
US6280411B1 (en) 1998-05-18 2001-08-28 Scimed Life Systems, Inc. Localized delivery of drug agents
US6368658B1 (en) 1999-04-19 2002-04-09 Scimed Life Systems, Inc. Coating medical devices using air suspension

Patent Citations (15)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3127448A (en) * 1960-09-21 1964-03-31 Metal Hydrides Inc Method for preparing tertiary amine boranes
US5075112A (en) * 1990-02-12 1991-12-24 Cartilage Technologies Inc. Method of and dosage unit for inhibiting angiogenesis or vascularization in an animal using shark cartilage
US5516781A (en) * 1992-01-09 1996-05-14 American Home Products Corporation Method of treating restenosis with rapamycin
US5634895A (en) * 1994-06-23 1997-06-03 Cormedics Corp. Apparatus and method for transpericardial delivery of fluid
US5578073A (en) * 1994-09-16 1996-11-26 Ramot Of Tel Aviv University Thromboresistant surface treatment for biomaterials
US5652225A (en) * 1994-10-04 1997-07-29 St. Elizabeth's Medical Center Of Boston, Inc. Methods and products for nucleic acid delivery
US5854205A (en) * 1995-10-23 1998-12-29 The Children's Medical Center Corporation Therapeutic antiangiogenic compositions and methods
US6004943A (en) * 1995-11-27 1999-12-21 Inst. Of Biomedical Engineering, Chinese Acdmy Of Med. Science Protein-coated medical substrates for local delivery of genes and method of forming coatings on the substrates
US6099562A (en) * 1996-06-13 2000-08-08 Schneider (Usa) Inc. Drug coating with topcoat
US6013780A (en) * 1996-09-06 2000-01-11 Technion Research & Development Co. Ltd. VEGF145 expression vectors
US6468304B1 (en) * 1997-07-16 2002-10-22 Centre National De La Recherche Scientifique Implantable device covered with polymer capable of releasing biologically active substances
US6299604B1 (en) * 1998-08-20 2001-10-09 Cook Incorporated Coated implantable medical device
US6589546B2 (en) * 1998-08-28 2003-07-08 Scimed Life Systems, Inc. Polymeric coatings for controlled delivery of active agents
US6740736B2 (en) * 1998-09-24 2004-05-25 Ppl Therapeutics (Scotland) Limited Purification of fibrinogen from milk by use of cation exchange chromatography
US20020028243A1 (en) * 1998-09-25 2002-03-07 Masters David B. Protein matrix materials, devices and methods of making and using thereof

Cited By (43)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US8303643B2 (en) 2001-06-27 2012-11-06 Remon Medical Technologies Ltd. Method and device for electrochemical formation of therapeutic species in vivo
US8449901B2 (en) 2003-03-28 2013-05-28 Innovational Holdings, Llc Implantable medical device with beneficial agent concentration gradient
US8840660B2 (en) 2006-01-05 2014-09-23 Boston Scientific Scimed, Inc. Bioerodible endoprostheses and methods of making the same
US8089029B2 (en) 2006-02-01 2012-01-03 Boston Scientific Scimed, Inc. Bioabsorbable metal medical device and method of manufacture
US8048150B2 (en) 2006-04-12 2011-11-01 Boston Scientific Scimed, Inc. Endoprosthesis having a fiber meshwork disposed thereon
US8052743B2 (en) 2006-08-02 2011-11-08 Boston Scientific Scimed, Inc. Endoprosthesis with three-dimensional disintegration control
US7955382B2 (en) 2006-09-15 2011-06-07 Boston Scientific Scimed, Inc. Endoprosthesis with adjustable surface features
US8057534B2 (en) 2006-09-15 2011-11-15 Boston Scientific Scimed, Inc. Bioerodible endoprostheses and methods of making the same
US8128689B2 (en) 2006-09-15 2012-03-06 Boston Scientific Scimed, Inc. Bioerodible endoprosthesis with biostable inorganic layers
US8808726B2 (en) 2006-09-15 2014-08-19 Boston Scientific Scimed. Inc. Bioerodible endoprostheses and methods of making the same
US8052744B2 (en) 2006-09-15 2011-11-08 Boston Scientific Scimed, Inc. Medical devices and methods of making the same
US8002821B2 (en) 2006-09-18 2011-08-23 Boston Scientific Scimed, Inc. Bioerodible metallic ENDOPROSTHESES
US8715339B2 (en) 2006-12-28 2014-05-06 Boston Scientific Scimed, Inc. Bioerodible endoprostheses and methods of making the same
US8080055B2 (en) 2006-12-28 2011-12-20 Boston Scientific Scimed, Inc. Bioerodible endoprostheses and methods of making the same
US10094836B2 (en) 2007-01-08 2018-10-09 The United States Of America, As Represented By The Secretary, Department Of Health & Human Services SLCO1B3 genotype
US8597720B2 (en) 2007-01-21 2013-12-03 Hemoteq Ag Medical product for treating stenosis of body passages and for preventing threatening restenosis
US9656003B2 (en) 2007-02-07 2017-05-23 Cook Medical Technologies Llc Medical device coatings for releasing a therapeutic agent at multiple rates
US20080195079A1 (en) * 2007-02-07 2008-08-14 Cook Incorporated Medical device coatings for releasing a therapeutic agent at multiple rates
US8932345B2 (en) 2007-02-07 2015-01-13 Cook Medical Technologies Llc Medical device coatings for releasing a therapeutic agent at multiple rates
US20080208315A1 (en) * 2007-02-27 2008-08-28 National Taiwan University Of Science & Technology Coronary stent having a surface of multi-layer immobilized structures
US8663337B2 (en) 2007-06-18 2014-03-04 Zimmer, Inc. Process for forming a ceramic layer
US8133553B2 (en) 2007-06-18 2012-03-13 Zimmer, Inc. Process for forming a ceramic layer
US8309521B2 (en) 2007-06-19 2012-11-13 Zimmer, Inc. Spacer with a coating thereon for use with an implant device
US9192697B2 (en) 2007-07-03 2015-11-24 Hemoteq Ag Balloon catheter for treating stenosis of body passages and for preventing threatening restenosis
US8052745B2 (en) 2007-09-13 2011-11-08 Boston Scientific Scimed, Inc. Endoprosthesis
US8608049B2 (en) 2007-10-10 2013-12-17 Zimmer, Inc. Method for bonding a tantalum structure to a cobalt-alloy substrate
US8602290B2 (en) 2007-10-10 2013-12-10 Zimmer, Inc. Method for bonding a tantalum structure to a cobalt-alloy substrate
US7998192B2 (en) 2008-05-09 2011-08-16 Boston Scientific Scimed, Inc. Endoprostheses
US8236046B2 (en) 2008-06-10 2012-08-07 Boston Scientific Scimed, Inc. Bioerodible endoprosthesis
US7985252B2 (en) 2008-07-30 2011-07-26 Boston Scientific Scimed, Inc. Bioerodible endoprosthesis
US8382824B2 (en) 2008-10-03 2013-02-26 Boston Scientific Scimed, Inc. Medical implant having NANO-crystal grains with barrier layers of metal nitrides or fluorides
US20100087783A1 (en) * 2008-10-07 2010-04-08 Boston Scientific Scimed, Inc. Medical devices for delivery of therapeutic agents to body lumens
US8267992B2 (en) 2009-03-02 2012-09-18 Boston Scientific Scimed, Inc. Self-buffering medical implants
US10369256B2 (en) 2009-07-10 2019-08-06 Boston Scientific Scimed, Inc. Use of nanocrystals for drug delivery from a balloon
US11278648B2 (en) 2009-07-10 2022-03-22 Boston Scientific Scimed, Inc. Use of nanocrystals for drug delivery from a balloon
US10080821B2 (en) 2009-07-17 2018-09-25 Boston Scientific Scimed, Inc. Nucleation of drug delivery balloons to provide improved crystal size and density
US8668732B2 (en) 2010-03-23 2014-03-11 Boston Scientific Scimed, Inc. Surface treated bioerodible metal endoprostheses
US8889211B2 (en) 2010-09-02 2014-11-18 Boston Scientific Scimed, Inc. Coating process for drug delivery balloons using heat-induced rewrap memory
US8669360B2 (en) 2011-08-05 2014-03-11 Boston Scientific Scimed, Inc. Methods of converting amorphous drug substance into crystalline form
US9056152B2 (en) 2011-08-25 2015-06-16 Boston Scientific Scimed, Inc. Medical device with crystalline drug coating
WO2016154050A1 (en) * 2015-03-20 2016-09-29 The Trustees Of Dartmouth College System and methods for enhancing uptake of therapeutic agent from bloodstream into disease site
US10485481B2 (en) 2015-03-20 2019-11-26 The Trustees Of Dartmouth College Systems and methods for enhancing uptake of therapeutic agent from bloodstream into disease site
US10010400B2 (en) 2015-03-30 2018-07-03 Taris Biomedical Llc Devices and methods for local delivery of drug to upper urinary tract

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