Patent Application
20160361472
The present invention relates to a medical device having a bioactive material coated thereon and a method for manufacturing said device.
Conditions and diseases of the body may be treated by implanting a medical device within the patient. Such medical devices may be coated with a bioactive material suitable for treating the condition or disease, or for preventing further conditions or diseases from arising as a result of the surgery. For example, stenosed blood vessels may be treated by inserting a stent into the vessel so as to open the vessel and allow proper blood flow through it. However, after the procedure the presence of the stent in the vessel may cause fibrosis of the surrounding tissue and development of thrombi, which together may cause further stenosis or occlusion of the vessel. In order to reduce the chances of such restenosis occurring, the stent may be coated with a drug such as Paclitaxel to inhibit cell proliferation around the implanted device.
Other conditions and diseases are treatable with stents, catheters, cannulae and other medical devices inserted into the esophagus, trachea, colon, biliary tract, urinary tract and other locations in the body, or with orthopedic devices, implants, or replacements. Any of these devices may be coated with bioactive materials to be delivered in the vicinity of the implantable device. Polymer based carrier materials have been used to adhere drugs to stents for delivery into a patient, however the polymer carriers can have adverse side effects which are undesirable for the patient.
The present invention seeks to provide an improved implantable medical device having a bioactive material coated thereon, and an improved method for manufacturing said device.
According to an aspect of the invention, an implantable medical device including at least one contact surface having a bioactive material coated directly thereon is provided, wherein the at least one contact surface has a defined total surface energy density, wherein the bioactive material has a defined total surface energy density, and wherein the total surface energy densities of the contact surface and the bioactive material are substantially matched.
The surface energies of the at least one contact surface and of the bioactive material may each comprise a polar component and a dispersive (otherwise known as non-polar) component. The polar components of the surface energies may be substantially matched and the dispersive (non-polar) components of the surface energies may be substantially matched.
The surface energies and components thereof may be measured using the Owens, Wendt, Rabel and Kaelble method (OWRK method).
Where the medical device comprises nitinol, and the bioactive material is predominantly non-polar, the non-polar component of the surface energy of the at least one contact surface may be greater than 40%, and preferably substantially 50% of the surface energy of the at least one contact surface.
According to another aspect of the invention, a method is provided for making an implantable medical device including a contact surface having a bioactive material coated directly thereon, the contact surface having a defined surface energy density and the bioactive material having a defined surface energy density; the method comprising the steps of:
substantially matching the total surface energy densities of the contact surface and the bioactive material.
Where the surface energies of the at least one contact surface and of the bioactive material each comprise a polar component and a dispersive (otherwise known as non-polar) component the method may comprise the steps of:
substantially matching the polar components of the surface energies; and
substantially matching the dispersive (non-polar) components of the surface energies.
The medical device may include a structure comprising a base material. The at least one contact surface may be a surface of the base material. The contact surface may comprise at least one of non-polar and polar components. The polar and non-polar components of the at least one contact surface may be present in a given proportion or ratio. The polar components may provide the polar component of the surface energy, while the non-polar components may provide the non-polar component of the surface energy.
The bioactive material may be predominantly polar or non-polar. The polar and non-polar components of the bioactive material may be present in a given proportion or ratio. The at least one contact surface may be a modified surface. The surface may have been modified to alter the ratio or proportion of polar and non-polar components in the direction of, or closer to the ratio or proportion of polar and non-polar components in the bioactive material. The surface may have been modified to increase a proportion of non-polar components where the bioactive material is predominantly non-polar and to decrease the proportion of non-polar components where the bioactive material is predominantly polar.
According to another aspect of the invention an implantable medical device is provided, the implantable medical device including a structure comprising a base material, the structure including at least one contact surface of the base material, the contact surface comprising at least one of non-polar and polar components; and a bioactive material coating disposed directly on the at least one contact surface, the bioactive material being predominantly polar or non-polar; the at least one contact surface being modified to alter the proportion of polar and non-polar components in the direction of the proportion of polar and non-polar components in the bioactive material.
A surface energy of the at least one contact surface may be above about 40 Dynes/cm (40 mN/m).
Altering the proportion of polar and non-polar components in the direction of the proportion of polar and non-polar components in the bioactive material can be increasing a proportion of non-polar components where the bioactive material is predominantly non-polar and decreasing the proportion of non-polar components where the bioactive material is predominantly polar.
The polar and non-polar components at the contact surface may be formed from the bulk material, for example, such as the formation of a metal oxide layer at the surface of a metal material in air, or may comprise the bulk material. However, such surfaces may not be suitable for, or effective at binding a bioactive material to said surface. Providing a modified surface enables improved binding of the bioactive material to the surface without the need for an additional component such as a polymer layer to hold the bioactive material in place.
The surface energy of the at least one contact surface may be between about 40 and 60 Dynes/cm (40-60 mN/m), between about 40 and 50 Dynes/cm (40-50 mN/m), or between about 50 and 60 Dynes/cm (50-60 mN/m).
Providing a surface having a higher surface energy enables the bioactive material to better adhere to said surface. The inventors have found that providing a contact surface having a surface energy in these ranges enables good adhesion of the bioactive material to the surface, whilst still enabling the drug to be released from the surface and pass into the body. In particular, where the bioactive material is non-polar, a surface energy of between about 40 and 50 Dynes/cm (40-50 mN/m) can allow an effective amount of the bioactive material to be released from the surface, after delivery in the patient, into the body.
The surface energy of the at least one contact surface may be substantially matched to a surface energy of the bioactive material.
Substantially matching the surface energies or components may be matching to within ±15 Dynes/cm (15 mN/m). Preferably, matching is to within ±10 Dynes/cm (10 mN/m), and more preferably to within ±5 Dynes/cm (5 mN/m). Substantially matching the surface energies or components may be matching to within ±2 to 9%.
Where the surface energy of the contact surface is 40 Dynes/cm (40 mN/m), substantially matching the surface energy of the bioactive material may be matching to within ±2%, ±4%, or ±6% of the surface energy of the contact surface. Where the surface energy of the contact surface is 50 Dynes/cm (50 mN/m), substantially matching the surface energy of the bioactive material may be matching to within ±2.5%, ±5%, ±7.5% of the surface energy of the contact surface. Where the surface energy of the contact surface is 60 Dynes/cm (60 mN/m), substantially matching the surface energy of the bioactive material may be matching to within ±3%, ±6%, ±9% of the surface energy of the contact surface.
Matching the surface energies of the bioactive material and the contact surface can allow optimised bonding and elution of the material from the surface when in situ.
The at least one contact surface may be selectively etched to remove at least some of one of the polar and non-polar components at the at least one contact surface.
Etching is a relatively harsh technique which can strip layers off the surface of the device. Etching may allow new components to form from the base material at the surface. Etching can selectively remove specific polar or non-polar components from the surface. By tailoring the etching process, including the solution and time for etching etc., to remove selected amounts of specific compounds at the contact surface, the contact surface can be modified so as to optimise binding to a given bioactive material. The etching process may involve immersing the contact surface in an acid, or alkali solution.
The at least one contact surface may be selectively polished to remove at least some of one of the polar and non-polar components at the at least one contact surface. Selective polishing can provide the same advantages as selective etching. Selective polishing may include electro-polishing.
The at least one contact surface may be at least partially passivated or ionised to alter the proportion of polar to non-polar components at the at least one contact surface. Passivating has the advantage of preventing further reaction at the surface, thereby rendering the surface inert. Ionising the surface may include bombarding the surface with an ion beam of an inert gas, such as argon, for example.
Ion beam penetration may be used to alter the proportion of polar to non-polar components at the at least one contact surface. The at least one contact surface may be impregnated with a material by ion bean penetration. Such a process may therefore modify the at least one contact surface.
The base material may be selectively doped so as to modify the at least one contact surface, said doping altering the proportion of polar to non-polar components at the at least one contact surface. The doping element may be selected so as to modify the surface formed on the base material to more favourably bind to a particular bioactive material.
Any combination of these techniques may be used to modify the contact surface of the device.
The medical device may comprise an alloy or a polymer. The base material may comprise a nickel titanium alloy. The at least one contact surface may comprise nickel, in the form of nickel ions and also in nickel containing compounds. Some of the nickel containing compounds may be polar. The at least one contact surface may be chemically treated to reduce the amount of nickel at said surface. In particular, the at least one contact surface may comprise between 0 and 5 at %, preferably between 0 to 3 at %, and more preferably between 1.2 at % and 2.5 at % nickel. The at least one contact surface may comprise between about 1 and 2 at % nickel. The at least one contact surface may comprise no less than 1 at % nickel. The at least one contact surface may comprise and no more than 2, 2.5, 3, or 5 at % nickel. The percentage of nickel present at the surface may be measured by X-ray Photoelectron Spectroscopy (XPS). Where the bioactive material is non-polar, such a reduction in nickel and polar nickel containing compounds can facilitate optimised adherence of the bioactive material to the contact surface.
The medical device may be a stent. The bioactive material may be Paclitaxel. The Paclitaxel may be at least 80% amorphous.
The at least one contact surface may have a thickness of between 45 and 65×10−10 m.
The structure may include at least one second surface, the at least one second surface having a proportion of polar and non-polar components different from the proportion of polar and non-polar components of the at least one contact surface.
The at least one second surface may be coated with a second bioactive material for treating the patient. Taking the example of a luminal medical device for delivery into a vessel, the at least one first surface may be on the outer luminal surface of the device, and the at least one second surface on the inner luminal surface of the device. Such an arrangement can allow delivery of the first bioactive material into the lumen wall, and of the second bioactive material into the fluid flowing through the vessel.
According to another aspect of the present invention a method is provided for making an implantable medical device including a structure comprising a base material, the structure including at least one contact surface of the base material, the contact surface comprising non-polar and polar components; and a bioactive material coating disposed directly on the at least one contact surface, the bioactive material being predominantly polar or non-polar; the method including the steps of:
modifying the at least one contact surface by altering the proportion of polar and non-polar components in the direction of the proportion of polar and non-polar components in the bioactive material; and
applying the bioactive material directly to the at least one contact surface.
The surface energy of the at least one contact surface may be above 40 Dynes/cm (40 mN/m).
The step of treating the at least one contact surface prior to application of the bioactive material may limit the surface energy of the at least one contact surface to between 40 and 60 mN/m.
The method may include the step of substantially matching the surface energy of the at least one contact surface to a surface energy of the bioactive material.
The modification step may include chemically modifying at least a part of the at least one contact surface.
The modification step may include at least one of selectively etching, selectively polishing, passivating or ionising the at least one contact surface to remove at least some of one of the polar and non-polar components at the at least one contact surface. Selective polishing may include electropolishing.
The modification step may include selectively doping the base material so as to alter the proportion of polar to non-polar components at the at least one contact surface.
Wherein the at least one contact surface comprises nickel and nickel containing compounds, the step of modification may include chemically treating the at least one surface to reduce the amount of nickel at said surface.
The step of modification may include chemically treating the at least one surface to reduce the amount of nickel and nickel containing compounds at said surface such that the surface comprises no more than 1-2% nickel.
The modification step may modify the base material of the contact surface to a thickness of between 45 and 65×10−10 m.
The method may include the step of forming at least one second surface, the at least one second surface having a different proportion of polar to non-polar components than the proportion of polar to non-polar components of the at least one contact surface.
Another aspect of the invention provides a method of making an implantable medical device including at least one contact surface having a bioactive material coated directly thereon, the at least one contact surface having a defined surface energy density and the bioactive material having a defined surface energy density, the method comprising the steps of:
substantially matching the total surface energy densities of the at least one contact surface and the bioactive material; and
coating the bioactive material directly on the at least one contact surface.
Where the surface energies of the at least one contact surface and of the bioactive material each comprises a polar component and a non-polar component, the method may comprise the steps of:
Embodiments of the present invention are described below, by way of example only, with reference to the accompanying drawings, in which:
The components in the drawings are not necessarily to scale, emphasis instead being placed upon illustrating the principles of the teachings herein.
Where the medical device is a stent, the contact surface may be the abluminal surface of the stent. The amount of bioactive material on the surface can be determined by High Performance Liquid Chromatography (HPLC).
The contact surface 14 is an outer layer of the base material of the device 10; the contact surface may have a thickness or depth of, for example, several atoms or molecules. The surface may have a thickness in the region of several nanometres. The chemical composition of the contact surface largely determines how the device 10 interacts with materials placed on that device. Components of the contact surface are classified as polar or non-polar. By polar it is meant that a dipole moment exists between atoms in a component at the surface. By non-polar it is meant that no dipole moment exists between the atoms.
The surface energy of the bioactive material will depend on the polar or non-polar nature of the material. Where the material is a powder, the surface energy may be determined by a theoretical method such as the Parachor method, for example.
The surface energy density of a solid surface can be measured by various known methods. One method, known as the Owens, Wendt, Rabel and Kaelble (OWRK) method, involves measuring the contact angle of the surface with several known liquids, such as water, diiodomethane and 1,5-pentanediol, then using the OWRK equations to calculate the surface energy. This method breaks the surface energy density of the contact surface down into polar and non-polar components, each component representing the energy contributed by the respective polar and non-polar components at that surface. In a preferred embodiment, the at least one contact surface of the device has a surface energy of at least 40 Dynes/cm (40 mN/m).
Preferably, the total surface energy density of the contact surface and the total surface energy density of the bioactive material are substantially matched to one another. Even more preferably, the polar components of the surface energy of the contact surface and the polar components of the surface energy density of the bioactive material are substantially matched to one another, and the non-polar components of the surface energy of the contact surface and the non-polar components of the surface energy density of the bioactive material are substantially matched to one another. The at least one contact surface may be modified such that the total surface energy of the contact surface substantially matches that of the bioactive material.
Once the energies have been matched, the bioactive material may be coated directly on the at least one contact surface.
According to aspects of the present invention the surface of the device can be modified by adjusting the proportions of polar and non-polar components at the surface to optimise bonding of the surface with the bioactive material selected for the coating. When considering the modification to be made, regard is had not just to the strength of the bond the bioactive material can make with the contact surface of the device but also to the ability of the surface to release the bioactive material once the device is in position inside the patient. If the bioactive material is adhered to the medical device excessively strongly, it cannot be released from the device into the patient and thus cannot treat the condition or disease it is provided to treat. In an embodiment an upper limit of approximately 60 Dynes/cm (60 mN/m) is preferred.
Where the bioactive material is non-polar, the inventors have found that adherence of the bioactive material to a surface can be improved, even optimised, by increasing the proportion of non-polar components at the contact surface. This may be done, for example, by selectively removing polar components from the surface. For polar bioactive materials, the inventors have found that increasing the proportion of polar components at the surface improves bonding of said bioactive material to said surface.
In general, a polar surface component has a higher energy than a non-polar surface as a dipole moment increases the Gibbs free energy of the surface (surface energy). As such, a given percentage of polar components at the surface will contribute a greater percentage of the total surface energy. The inventors have found that for non-polar bioactive materials, bonding to a nitinol surface is optimised by increasing the proportion of non-polar components at the surface such that approximately 50% of the total surface energy is provided by them.
Nitinol is an alloy of nickel and titanium, where the two elements are present in roughly equal atomic percentages, for example nitinol 55 and nitinol 60. Nitinol a biocompatible superelastic shape-memory material which is used in stents for its ability to be delivered into a patient in a collapsed configuration and to self-expand when released inside the body.
During manufacture the stent is exposed to the atmosphere, heated, and generally handled. Metal atoms at the surface spontaneously oxidise, with formation of titanium dioxide being particularly energetically favourable. X-ray Photoelectron Spectroscopy (XPS) has been used to characterise the contact surface 24 of a nitinol stent 20. The surface was found to comprise, amongst other components, titanium dioxide, titanium, nickel, nickel oxides and hydroxides. Oxides of carbon, calcium and silicon were also observed using the XPS method. Table 1 shows the components and their relative amounts at the contact surface, as determined by X-ray Photoelectron Spectroscopy (XPS).
The contact surface of the nitinol stent was shown to have a thickness of between 45 and 65×10−10 m using Auger Electron Spectroscopy (AES).
Of the components at the surface, titanium dioxide, and nickel monoxide are considered non-polar, whereas titanium, nickel, and nickel hydroxide are considered polar. Table 2 shows the polar and non-polar components of the surface energy, together with the total surface energies for nitinol stents having different surface compositions.
The surface energy of Paclitaxel may be determined theoretically by the Parachor method, for example, or via experimental techniques. The surface energy of Paclitaxel has been shown to be between 40 and 60 Dynes/cm (40-60 Nm/m).
In the step of modifying the at least one contact surface of the device, the surface is modified by selectively removing nickel and nickel hydroxide from the surface. This can be achieved by etching the surface using a hydrofluoric acid solution for a number of minutes. This first step may remove at least some of the oxides present on the surface of the stent following the manufacturing process. The method may include further steps of etching the surface using a mixture of hydrofluoric acid, nitric acid, and methanol, or etching the surface using sulfuric acid and methanol solution, for example. Each etching step may be carried out for a number of minutes. The later etching steps may allow controlled growth of a titanium dioxide layer on the surface of the base nitinol material.
In another embodiment a nitinol contact surface may be polished using a solution of Hydrofluoric acid and methanol. This method may be carried out at, for example, −30° C.
Preferably, nickel is removed from the surface until only 1 at % to 2 at % nickel remains. The amount of nickel can be measured by X-ray Photoelectron Spectroscopy (XPS). Generally, a small amount of nickel on the surface of the stent is desirable to prevent corrosion of the surface.
In another embodiment a stainless steel contact surface may be passivated in a solution of, for example nitric acid.
In the step of applying the bioactive material directly to the at least one contact surface, the Paclitaxel is deposited on the contact surface of the stent by spraying a solution of the Paclitaxel dissolved in ethanol, acetone or chloroform, for example, onto the surface using an airbrush type applicator. Such a spray has been found to provide a coating of reliable uniformity and provides the greatest control over the amount of bioactive material deposited on the surface. Multiple sprays may be required to provide the desired coating. Surfaces which are not to be coated may be masked prior to spraying, and the mask subsequently removed. Preferably approximately 2.5 to 3 micrograms per square millimetre is deposited on the surface of the stent.
Paclitaxel 26 is an anti-proliferative agent which has been found to reduce smooth muscle cell proliferation and migration. It has been found that stents coated with such bioactive materials are beneficial in preventing restenosis after implantation of a stent or similar device in a patient. Preferably, the Paclitaxel present on the surface of the stent, after evaporation of the carrier solution, is at least 80% amorphous. In certain circumstances the amorphous form of the drug may be more effective than the crystalline form. The percentage of amorphous drug can be determined by removal of the drug from the surface. Firstly, the surface is dipped in a media which removes only the amorphous form of the drug from the surface, and secondly the surface is dipped in a solvent which removes all forms of the drug from the surface. A simple calculation is then performed to determine the percentage of the total drug present provided by the amorphous form.
Various embodiments of the invention are described with reference to the arrangement of the device shown in
The base material 12 should be suitable for the intended use of the device. Preferably, the base material is biocompatible. It may be biodegradable or non-biodegradable. The base material may include a radiopaque material for identifying the location of the device 10 by X-ray or fluoroscopy during or after its introduction into the patient.
The base material 12 may comprise a metal, an alloy or a polymer, for example. The base material may include at least one of stainless steel, tantalum, titanium, nitinol, gold, platinum, inconel, iridium, silver, tungsten, colbolt, chromium, or another biocompatible metal, or alloys of any of these; carbon or carbon fiber; cellulose acetate, cellulose nitrate, silicone, polyethylene teraphthalate, polyurethane, polyamide, polyester, polyorthoester, polyanhydride, polyether sulfone, polycarbonate, polypropylene, high molecular weight polyethylene, polytetrafluoroethylene, or another biocompatible polymeric material, or mixtures or copolymers of these; polylactic acid, polyglycolic acid or copolymers thereof, a polyanhydride, polycaprolactone, polyhydroxybutyrate valerate or another biodegradable polymer, or mixtures or copolymers of these; a protein, an extracellular matrix component, collagen, fibrin or another biologic agent; or a suitable mixture of any of these.
Nitinol is particularly useful as the base material 12 when the device is a stent.
The contact surface may substantially entirely comprise either polar or non-polar components, and others may comprise a mix of polar and non-polar components. In the case of a device comprising a metal or metal alloy base material 12, the contact surface may comprise an oxide layer comprising oxides of the metals of the base material. In fact the majority of the contact surface may comprise such oxides. The contact surface 14 may comprise the base material itself, and/or other compounds derived from the base material or from the atmosphere. Of course impurities, or any compounds derived from the impurities may also exist at the contact surface.
Where the medical device comprises a polymer bulk material, the contact surface may comprise an oxide of the polymer. The contact surface of a polymer may comprise polar and non-polar components, or may comprise only non-polar components.
Where the bioactive material is predominantly polar and the contact surface is modified to increase the polar component, the surface may be, for example, bombarded with oxygen ions to as to ionise components at the surface and therefore render them polar.
Whether the surface is modified to increase the polar or non-polar component, roughening the surface has the effect of increasing the surface area exposed for bonding and therefore has the effect of magnifying the polar or non-polar nature of the surface.
As mentioned hereinbefore, the bioactive material 16 may be any drug, medicament or material, or combination thereof which can be coated onto a contact surface. The bioactive material may be coated onto the surface by a number of known techniques including, for example, spraying, vaccum deposition, and rolling the surface in the bioactive material.
A vast range of bioactive materials are known and maybe used, for example heparin, covalent heparin, or another thrombin inhibitor, hirudin, hirulog, argatroban, D-phenylalanyl-L-poly-L-arginyl chloromethyl ketone, or another antithrombogenic agent, or mixtures thereof; urokinase, streptokinase, a tissue plasminogen activator, or another thrombolytic agent, or mixtures thereof; a fibrinolytic agent; a vasospasm inhibitor; a calcium channel blocker, a nitrate, nitric oxide, a nitric oxide promoter or another vasodilator; Hytrin(R) or other antihypertensive agents; an antimicrobial agent or antibiotic; aspirin, ticlopidine, a glycoprotein IIb/IIIa inhibitor or another inhibitor of surface glycoprotein receptors, or another antiplatelet agent; colchicine or another antimitotic, or another microtubule inhibitor, dimethyl sulfoxide (DMSO), a retinoid or another antisecretory agent; cytochalasin or another actin inhibitor; or a remodelling inhibitor; deoxyribonucleic acid, an antisense nucleotide or another agent for molecular genetic intervention; methotrexate or another antimetabolite or antiproliferative agent; tamoxifen citrate, Taxol(R) or the derivatives thereof, or other anti-cancer chemotherapeutic agents; dexamethasone, dexamethasone sodium phosphate, dexamethasone acetate or another dexamethasone derivative, or another anti-inflammatory steroid or non-steroidal antiinflammatory agent; cyclosporin or another immunosuppressive agent; trapidal (a PDGF antagonist), angiopeptin (a growth hormone antagonist), angiogenin, a growth factor or an anti-growth factor antibody, or another growth factor antagonist; dopamine, bromocriptine mesylate, pergolide mesylate or another dopamine agonist; <60>Co(5.3 year half life), <192>Ir (73.8 days), <32>P(14.3 days), <111>In(68 hours), <90>Y(64 hours), <99m>Tc(6 hours) or another radiotherapeutic agent; iodine-containing compounds, barium-containing compounds, gold, tantalum, platinum, tungsten or another heavy metal functioning as a radiopaque agent; a peptide, a protein, an enzyme, an extracellular matrix component, a cellular component or another biologic agent; captopril, enalapril or another angiotensin converting enzyme (ACE) inhibitor; ascorbic acid, alpha tocopherol, superoxide dismutase, deferoxamine, a 21-aminosteroid (lasaroid) or another free radical scavenger, iron chelator or antioxidant; a <14>C—, <3>H—, <131>1—, <32>P— or <36>S— radiolabelled form or other radiolabelled form of any of the foregoing; estrogen or another sex hormone; AZT or other antipolymerases; acyclovir, famciclovir, rimantadine hydrochloride, ganciclovir sodium, Norvir, Crixivan, or other antiviral agents; 5-aminolevulinic acid, meta-tetrahydroxyphenylchlorin, hexadecafluoro zinc phthalocyanine, tetramethyl hematoporphyrin, rhodamine 123 or other photodynamic therapy agents; an IgG2 Kappa antibody against Pseudomonas aeruginosa exotoxin A and reactive with A431 epidermoid carcinoma cells, monoclonal antibody against the noradrenergic enzyme dopamine beta-hydroxylase conjugated to saporin or other antibody targeted therapy agents; gene therapy agents; and enalapril and other prodrugs; Proscar(R), Hytrin(R) or other agents for treating benign prostatic hyperplasia (BHP) or a mixture of any of these; and various forms of small intestine submucosa (SIS). No coating is required over the bioactive material to control the elution rate of the bioactive material from the medical device.
The bioactive material 16 may be coated on one surface of the device 10. Second and further surfaces of the device may be coated with second and further bioactive materials, and others may have no bioactive material coated thereon. The contact surfaces with no bioactive material coated thereon may be left bare, or may be coated with other materials, depending on the application of the device. The second and further contact surfaces of the device may have a proportion of polar and non-polar components different from the proportion of polar and non-polar components of the at least one contact surface. Each surface may be modified to optimise bonding with the particular bioactive material which is to be coated thereon. The different bioactive materials can be coated on different regions of the device so as to target delivery of the materials into specific regions of the body.
All optional and preferred features and modifications of the described embodiments and dependent claims are usable in all aspects of the invention taught herein. Furthermore, the individual features of the dependent claims, as well as all optional and preferred features and modifications of the described embodiments are combinable and interchangeable with one another.
| Number | Date | Country | Kind |
|---|---|---|---|
| 1510015.9 | Jun 2015 | GB | national |
This application claims the benefit of U.S. Provisional Application No. 62/172,972 and Great Britain Application No. 1510015.9 both filed on Jun. 9, 2015 entitled “Bioactive Material Coated Medical Device” the entire contents of which are incorporated herein by reference.
| Number | Date | Country | |
|---|---|---|---|
| 62172972 | Jun 2015 | US |
