cardiovascular disease is the leading cause of death in the united states . a significant portion of these deaths are caused by coronary artery disease , the clogging of arteries due to cholesterol buildup . a method for combating this vessel blockage is balloon angioplasty coupled with stenting . using a catheter guidewire , surgeons insert a balloon into a blocked vessel . this balloon is attached to a stent . the balloon expands , pushing away cholesterol , while leaving the stent in place . this expandable mesh cylinder then supports the damaged blood vessel after the balloon and guidewire are withdrawn . in general , to provide effective treatment for coronary artery disease , the material creating the stent must be flexible , supportive , capable of expansion , and biocompatible . biocompatibility is the property of not incurring a toxic or detrimental immunological response . the normal host response to an implant includes trauma , inflammation , the immune system &# 39 ; s reaction , and eventual healing or scarring . biomaterials exhibiting a lack of biocompatibility could induce many complications , which might include long - lasting chronic inflammation or cytotoxic chemical buildup . to avoid these potential difficulties , scientists must test for the biocompatibility of substances , first in vitro and then in vivo . a few of the medical complications arising from coronary stents today include thrombosis , cholesterol accumulation , restenosis , inflammation , and hyperplasia . thrombosis is the formation of a clot , or the presence of a blood clot within a blood vessel . cholesterol , which accumulates from saturated fat buildup within the blood vessels , can reform its original plaques atop the inserted stents . restenosis is the re - closing or the collapsing of an artery . inflammation might be caused by the body &# 39 ; s immune response , warding off the invasive material . hyperplasia is an abnormal increase in the number of cells in the surrounding tissue . presently , most stents consist of a stainless steel framework . however , this 316l steel is not fully biocompatible , and has induced high occurrences of restenosis and thrombosis . scientists are therefore researching more biocompatible options , which include gold , titanium , cobalt - chromium alloys , tantalum alloys , nitinol , and various polymers . materials that are not biocompatible induce many complications in the body . chemical or physical properties can cause prolonged chronic inflammation , resulting in local cell damage . movement between the implant and the tissue would disrupt cells at any point of contact . as the body wears down plastics , small particles can cause irritation and also clog macrophage lysosomes . if the white blood cells cannot break down these particles , the particles will remain within the cells . stainless steel , the most common inexpensive stent material in use today has much room for improvement regarding biocompatibility . the current metal options available seem to incur high restenosis and thrombosis rates , and a need for repeat revascularization . polymer materials in use today also have much room for increasing biocompatibility . therefore the present disclosure relates to a biocompatible polymer for coating or fabricating an implantable medical device comprising : a first monomer and a second monomer wherein the first monomer is a hydroxyalkyl methacrylate and the second monomer is an acrylate monomer . the present biocompatible polymeric coatings comprise polymers having at least two monomers . a polymer is a large molecule ( macromolecule ) composed of repeating structural units typically connected by covalent chemical bonds . monomer is a small molecule that can become chemically bonded to other monomers to form a polymer . as used herein a “ copolymer ” will be defined as a macromolecule produced by the simultaneous or step - wise polymerization of two or more dissimilar units such as monomers . copolymer shall include biopolymers ( two dissimilar unit ), terpolymer ( three dissimilar units ), etc . because the first monomer is hydroxyalkyl methacrylate and the second monomer is an acrylate monomer in one embodiment , the biocompatible polymeric coatings are made of copolymers . by varying the amount of monomers used as well the reaction conditions the properties of the polymers can be fine tuned for drug delivery , mores specifically controlled drug release rates . the biocompatible polymers of the present disclosure are suitable for the controlled release of both hydrophobic and hydrophilic drugs , either independently or in combination . as used herein in reference to the bioactive agent or drugs , “ hydrophilic ” refers to a bioactive agent that has a solubility in water of more than 200 micrograms per milliliter . as used herein in reference to the bioactive agent or drug the term “ hydrophobic ” refers to a bioactive agent that has a solubility in water of no more than 200 micrograms per milliliter . as used herein “ controlled release ” refers to the release of a bioactive compound from a medical device surface at a predetermined rate . controlled release implies that the bioactive compound does not come off the medical device surface sporadically in an unpredictable fashion and does not “ burst ” off of the device upon contact with a biological environment ( also referred to herein a first order kinetics ) unless specifically intended to do so . however , the term “ controlled release ” as used herein does not preclude a “ burst phenomenon ” associated with deployment . in some embodiments of the present invention an initial burst of drug may be desirable followed by a more gradual release thereafter . the release rate may be steady state ( commonly referred to as “ timed release ” or zero order kinetics ), that is the drug is release in even amounts over a predetermined time ( with or without an initial burst phase ) or may be a gradient release . a gradient release implies that the concentration of drug released from the device surface changes over time . controlling drug release rates from the polymers of the present disclosure requires adjusting the properties of the polymers . one non - limiting method of controlling drug release rates in the polymers of the present disclosure involves controlling the glass transition temperature ( tg ) of the polymers . as used herein , glass transition temperature ( tg ) refers to a temperature wherein a polymer structurally transitions from an elastic pliable state to a rigid and brittle state . medical devices suitable for coating with the present biocompatible polymers of the present disclosure include , but are not limited to , vascular stents , stent grafts , urethral stents , bile duct stents , catheters , guide wires , pacemaker leads , bone screws , sutures and prosthetic heart valves . medical devices which can be manufacture from the present biocompatible polymers include , but are not limited to , vascular stents , stent grafts , urethral stents , bile duct stents , catherters , guide wires , pacemaker leads , bone screws , sutures and prosthetic heart valves . the present biocompatible polymers include hydroxyalkyl methacrylate as a first monomer . in one embodiment of the present biocompatible polymer for coating or fabricating an implantable medical device , first monomer is 4 - hydroxybutyl methacrylate . a second monomer of the present biocompatible polymers may be an acrylate monomer . in one embodiment , the second monomer is hexyl methacrylate . the structure of hexyl methacrylate is represented below : in one embodiment , n and m can be the same or different and is an integer that is greater than equal to 1 and less than or equal to 20 , 000 . without being bound to any theory , the above polymer exhibits superior biocompatibility maybe due to its amphiphilic nature with combination of hydrophobic and hydrophilic groups in the chemical structure . methacrylates ( ch 2 ═ cmecoo − ) are the salts or esters of methacrylic acid . methacrylates contain methyl - vinyl groups , that is , two carbon atoms double bonded to each other , directly attached to the carbonyl carbon , and wherein the vinyl group is substituted with a non - terminal methyl group . methacrylates are common monomers in polymer plastics , forming the acrylate polymers . methacrylates easily form polymers because the double bonds are very reactive . in one embodiment of the present biocompatible polymers , the second monomer is an acrylate monomer selected from the group consisting of hexyl methacrylate , butyl methacrylate , ethyl methacrylate , lauryl methacrylate , hydroxypropyl methacrylate , and 2 - hydroxyethyl methacrylate . implantable medical devices suitable for coating or being made with the present biocompatible polymers include , but are not limited to vascular stents , stent grafts , urethral stents , bile duct stents , catheters , guide wires , pacemaker leades , bone screws , sutures and prosthetic heart valves . the polymers of the present disclosure are also suitable for fabricating implantable medical devices . medical devices which can be fabricated from the present biocompatible polymers include , but are not limited to , vascular stents , stent grafts , urethral stents , bile duct stents , catheters , guide wires , pacemaker leads , bone screws , sutures and prosthetic heart valves . the polymer coatings of the present disclosure are intended for medical devices deployed in a hemodynamic environment and possess excellent adhesive properties . that is , the coating must be stably linked to the medical surface . many different materials can be used to fabricate the substrate of implantable medical devices including , but not limited to , stainless steel , nitinol , aluminum , chromium , titanium , gold , cobalt , ceramics , and a wide range of synthetic polymeric and natural materials including , but not limited to , collagen , fibrin and plant fibers . all of these materials , and others , may be used with the polymeric coatings made in accordance with the teachings of the present disclosure . furthermore , the polymers of the present disclosure may be used to fabricate an entire medical device . there are many theories that attempt to explain or contribute to our understanding of how polymers adhere to surfaces . the most important forces include electrostatic and hydrogen bonding . however , other factors including wettability , absorption and resiliency also determine how well a polymer will adhere to different surfaces . therefore , polymer base coats , or primers are often used in order to create a more uniform coating surface . the polymeric coatings of the present disclosure can be applied to medical device surfaces , either primed or bare , in any manner known to those of ordinary skill in the art . application methods compatible with the present invention include , but are not limited to , spraying , dipping , brushing , vacuum - deposition , and others . moreover , the polymeric coatings of the present invention may be used with a cap coat . a cap coat as used herein refers to the outermost coating layer applied over another coating . a polymer coating of the present disclosure is applied over the primer coat . then , a polymer cap coat is applied over the polymeric coating of the present disclosure . the cap coat may optionally serve as a diffusion barrier to control bioactive agent release . the cap coat may be merely a biocompatible polymer applied to the surface of the sent to protect the stent and have no effect on the bioactive agent release rates . the biocompatible polymers of the present disclosure are also useful for the delivery and controlled release of drugs . drugs that are suitable for release from the polymers of the present invention include , but are not limited to , anti - proliferative compounds , cytostatic compounds , toxic compounds , anti - inflammatory compounds , chemotherapeutic agents , analgesics , antibiotics , protease inhibitors , statins , nucleic acids , polypeptides , growth factors and delivery vectors including recombinant micro - organisms , liposomes , and the like . in one embodiment of the present invention the drugs controllably released include , but are not limited to , macrolide antibiotics including fkbp - 12 binding agents . exemplary drugs of this class include sirolimus ( rapamycin ) ( formula 2 ), tacrolimus ( fk506 ), everolimus ( certican or rad - 001 ), temsirolimus ( ccl - 779 or amorphous rapamycin 42 - ester with 3 - hydroxy - 2 -( hydroxymethyl )- 2 - methylpropionic acid and zotarolimus . additionally , and other rapamycin hydroxyesters may be used in combination with the polymers of the present disclosure . stainless steel stents were placed a glass beaker and covered with reagent grade or better hexane . the beaker containing the hexane immersed stents was then placed into an ultrasonic water bath and treated for 15 minutes at a frequency of between approximately 25 to 50 khz . next the stents were removed from the hexane and the hexane was discarded . the stents were then immersed in reagent grade or better 2 - propanol and vessel containing the stents and the 2 - propanol was treated in an ultrasonic water bath as before . following cleaning the stents with organic solvents , they were thoroughly washed with distilled water and thereafter immersed in 1 . 0 n sodium hydroxide solution and treated at in an ultrasonic water bath as before . finally , the stents were removed from the sodium hydroxide , thoroughly rinsed in distilled water and then dried in a vacuum oven over night at 40 ° c . after cooling the dried stents to room temperature in a desiccated environment they were weighed their weights were recorded . in the following example , ethanol is chosen as the solvent of choice . the bioactive agent is zotarolimus . both the polymer and zotarolimus are freely soluble in ethanol . persons having ordinary skill in the art of polymer chemistry can easily pair the appropriate solvent system to the polymer - drug combination and achieve optimum results with no more than routine experimentation . 250 mg of zotarolimus is carefully weighed and added to a small neck glass bottle containing 2 . 8 ml of ethanol . the zotarolimus - ethanol suspension is then thoroughly mixed until a clear solution is achieved . next 250 mg of the present biocompatible polymer is added to the zotarolimus - ethanol solution and mixed until the polymer is dissolved forming a drug / polymer solution . the cleaned , dried stents are coated using either spraying techniques or dipped into the drug / polymer solution . the stents are coated as necessary to achieve a final coating weight of between approximately 10 μg to 1 mg . finally , the coated stents are dried in a vacuum oven at 50 ° c . over night . the dried , coated stents are weighed and the weights recorded . the concentration of drug loaded onto ( into ) the stents is determined based on the final coating weight . final coating weight is calculated by subtracting the stent &# 39 ; s pre - coating weight from the weight of the dried , coated stent . a cleaned , dry stent is first coated with the present biocompatible polymer followed by a coating of zotarolimus . finally , a second coating of biocompatible polymer is provided to seal the stent thus creating a sandwich coated stent . 100 mg of biocompatible polymer is added to a 50 ml erlenmeyer containing 12 . 5 ml of ethanol . the flask was carefully mixed until all of the biocompatible polymer is dissolved . in a separate clean , dry erlenmeyer flask 250 mg of zotarolimus is added to 11 ml of ethanol and mixed until dissolved . a clean , dried stent is then sprayed with the present biocompatible polymer until a smooth confluent polymer layer was achieved . the stent was then dried in a vacuum oven at 50 ° c . for 30 minutes . next , successive layers of zotarolimus are applied to the polymer - coated stent . the stent is allowed to dry between each of the successive zotarolimus coats . after the final zotarolimus coating has dried , three successive coats of biocompatible polymer are applied to the stent followed by drying the coated stent in a vacuum oven at 50 ° c . over night . the dried , coated stent is weighed and its weight recorded . the concentration of drug in the drug / polymer solution and the final amount of drug loaded onto the stent determine the final coating weight . final coating weight is calculated by subtracting the stent &# 39 ; s pre - coating weight from the weight of the dried , coated stent . a glass bottle was charged with 1 . 98 g of 4 - hydroxybutyl methacrylate , 6 . 0 g of n - hexyl methacrylate , 11 . 2 ml 2 - butanone , 4 . 8 ml n - propanol and 64 mg azobisisobutyronitrile ( aibn ). the bottle was sealed and purged with nitrogen gas for 30 minutes and heated in an oil bath kept at 60 ° c . for three hours . the polymer was purified by repeated precipitations in methanol from dichloromethane solution and dried in the oven at 45 ° c . overnight . an elastomeric material with a glass transition temperature of 6 . 5 ° c . was obtained . a glass bottle was charged with 2 . 57 g of 2 - hydroxyethyl methacrylate , 2 . 5 g of n - hexyl methacrylate , 7 ml 2 - butanone , 3 ml of n - propanol and 80 mg aibn . the bottle was sealed and purged with nitrogen gas for 30 minutes and heated in an oil bath kept at 60 ° c . for five hours . the polymer was purified by repeated precipitations in methanol from dichloromethane solution and dried in the oven at 45 ° c . overnight . an elastomeric material with a glass transition temperature of 25 ° c . was obtained . unless otherwise indicated , all numbers expressing quantities of ingredients , properties such as molecular weight , reaction conditions , and so forth used in the specification and claims are to be understood as being modified in all instances by the term “ about .” accordingly , unless indicated to the contrary , the numerical parameters set forth in the specification and attached claims are approximations that may vary depending upon the desired properties sought to be obtained by the present invention . at the very least , and not as an attempt to limit the application of the doctrine of equivalents to the scope of the claims , each numerical parameter should at least be construed in light of the number of reported significant digits and by applying ordinary rounding techniques . notwithstanding that the numerical ranges and parameters setting forth the broad scope of the invention are approximations , the numerical values set forth in the specific examples are reported as precisely as possible . any numerical value , however , inherently contains certain errors necessarily resulting from the standard deviation found in their respective testing measurements . the terms “ a ,” “ an ,” “ the ” and similar referents used in the context of describing the invention ( especially in the context of the following claims ) are to be construed to cover both the singular and the plural , unless otherwise indicated herein or clearly contradicted by context . recitation of ranges of values herein is merely intended to serve as a shorthand method of referring individually to each separate value falling within the range . unless otherwise indicated herein , each individual value is incorporated into the specification as if it were individually recited herein . all methods described herein can be performed in any suitable order unless otherwise indicated herein or otherwise clearly contradicted by context . the use of any and all examples , or exemplary language ( e . g ., “ such as ”) provided herein is intended merely to better illuminate the invention and does not pose a limitation on the scope of the invention otherwise claimed . no language in the specification should be construed as indicating any non - claimed element essential to the practice of the invention . groupings of alternative elements or embodiments of the invention disclosed herein are not to be construed as limitations . each group member may be referred to and claimed individually or in any combination with other members of the group or other elements found herein . it is anticipated that one or more members of a group may be included in , or deleted from , a group for reasons of convenience and / or patentability . when any such inclusion or deletion occurs , the specification is deemed to contain the group as modified thus fulfilling the written description of all markush groups used in the appended claims . certain embodiments of this invention are described herein , including the best mode known to the inventors for carrying out the invention . of course , variations on these described embodiments will become apparent to those of ordinary skill in the art upon reading the foregoing description . the inventor expects skilled artisans to employ such variations as appropriate , and the inventors intend for the invention to be practiced otherwise than specifically described herein . accordingly , this invention includes all modifications and equivalents of the subject matter recited in the claims appended hereto as permitted by applicable law . moreover , any combination of the above - described elements in all possible variations thereof is encompassed by the invention unless otherwise indicated herein or otherwise clearly contradicted by context . furthermore , numerous references have been made to patents and printed publications throughout this specification . each of the above - cited references and printed publications are individually incorporated herein by reference in their entirety . in closing , it is to be understood that the embodiments of the invention disclosed herein are illustrative of the principles of the present invention . other modifications that may be employed are within the scope of the invention . thus , by way of example , but not of limitation , alternative configurations of the present invention may be utilized in accordance with the teachings herein . accordingly , the present invention is not limited to that precisely as shown and described .