Title of Invention: ANTIBACTERIAL COATINGS THAT INHIBIT BIOFILM FORMATION ON IMPLANTS Abstract: Orthopedic and dental implants coated with an antibacterial coating and methods of making and using, are described herein. The implant can be coated with a hydrophobic, polycationic antibacterial polymer. The polymer can be covalently or non-covalently associated with the surface; however, in particular embodiments, the polymer is non-covalently associated with the surface. As shown in the examples below, clinical observations, digital radiography, and a battery of well-accepted ex vivo analytical methods show that the presence of a hydrophobic polycationic polymer coating, such as N,N-dodecyl,methyl-PEI coating on the surface of a metal implant, was effective in eliminating the clinical signs of infection in vivo in a large animal infection model. Moreover, the coated plates supported bone healing, and in fact decreased healing times, even in the presence of significant bacterial contamination compared to a control. Detailed Description: CROSS-REFERENCE TO RELATED APPLICATIONS This application is a continuation of copending application Ser. No. 13/647,107, filed Oct. 8, 2012, which was a continuation-in-part (CIP) of application Ser. No. 11/107,412, filed Apr. 14, 2005, which was a continuation of application Ser. No. 10/123,860, filed Apr. 15, 2002, which claims priority to U.S. Ser. No. 60/285,883, filed Apr. 23, 2001; U.S. Ser. No. 60/340,078, filed Dec. 10, 2001; and U.S. Ser. No. 60/368,495, filed Mar. 29, 2002, and also claims priority to Application Ser. No. 61/543,981, filed on Oct. 6, 2011, the entire contents of which are hereby incorporated by reference. STATEMENT REGARDING FEDERALLY SPONSORED RESEARCH OR DEVELOPMENT This invention was made with Government Support under Contract No. W911NF-07-D-0004, awarded to Massachusetts Institute of Technology by the Army Research Office. The Government has certain rights in the invention. FIELD OF THE INVENTION This invention is in the field of biomedical implant, such as orthopedic and dental implants, implants for ears, nose, and throat applications, and cardiovascular implants that exhibit antibacterial properties, prevent biofilm formation in vivo, and decrease healing times in mammals in the presence of infection. BACKGROUND OF THE INVENTION For many patients, surgical implantation of medical devices can be life-saving. However, implantation of these foreign bodies carries risk of infection. Although the risk of infection of these devices is in general only between 1 and 7%, the consequences of implant-associated infection are of great concern. Implant-associated infections are a major cause of fixation failure and result in increased morbidity, mortality, and treatment cost. The mortality of prosthetic valve endocarditis ranges up to 30%, and mortality rates associated with an infected aortic graft have approached 40%. A critical step in the pathogenesis of device infections is bacterial adherence to the foreign body surface and the formation of a bacterial biofilm. A biofilm is defined as a structured community of bacterial cells enclosed in a self-produced polymeric matrix and adherent to an inert or living surface. Biofilms are characterized by high concentrations of organisms with little turnover and low metabolic activity. Bacteria within the biofilm communicate with each other through the elaboration and recognition of small molecules, a process called “quorum sensing”. In orthopedic trauma for example, some 5-10% of orthopedic hardware facilitates host infection with increasing incidences for open fractures, combat related injuries, and revision joint replacements. As more soldiers from current armed conflicts around the globe survive serious blast trauma due to improved body armor, many sustain debilitating and life-threatening wound-related infections. Thus the need for improved implant surface protection in both civilian and military trauma patients has spurred recent research. In the past, localized antimicrobial delivery systems have been developed for the treatment and prevention of implant-associated infections, including poly(methylmethacrylate) cements, biodegradable polymers, and regional limb perfusions. The elution kinetics of antimicrobials from these carrier systems typically exhibit an initial supra-therapeutic release that ultimately drops below the minimal inhibitory concentration (MIC). Such sub-MIC antimicrobial levels favor the emergence of drug-resistant bacterial strains. In addition, antimicrobials are typically ineffective in penetrating biofilms and may trigger quorum sensing and altered gene expression. In the field of Ear Nose and Throat (ENT), for example, 8 out of 16 “failed” osteointegrating screws were found to have biofilm as determined by scanning electron microscopy (SEM). (Monksfiled P, Chapple I et al. J Laryngol Otol 125; 2011). Children undergoing treatment for otitis media, at an estimated cost of greater than $5 billion annually and a demographic distribution in the United States of 83% of children, will have at least one episode post-tympanostomy tube otorrhea, with 16% early postoperative, 26% late postoperative, 4% chronic and 7% recurrent. Fluorocarbon and silicone polymers constitute some of the substrates of tympanostomy tubes which are susceptible to bacterial adhesion. The “Biofilm Hypothesis” states that persistent bacterial infection in the absence of positive culture and recalcitrance to antibiotic treatment is at the core of the failure of systemic therapies. In general the most common treatment for any implant infection today is re-operation, often requiring staged surgical interventions to clean or exchange the implant, debridement of infected tissues, followed by antimicrobial therapy, in some cases for several years. In the United States alone, at least 100,000 out of over two million fixation device implants result in some form of postoperative infection. The cost of treating an implant-associated infection ranges from $30,000 to $300,000 and often involves repeated hospitalizations for treatment. Despite concerted efforts to resolve infections, there remains a very high rate of failure associated with initial infection treatment. Commonly, first course failure approaches 30% and results in a high rate of second and third course failure, multiplying costs and often leading to an ex-plant of the fixation device. There exists a need for improved coatings that inhibit or prevent biofilm formation on implants, including orthopedic and dental implants, implants for ear, nose, and throat applications, and cardiovascular devices. There also exists a need for improved coatings that inhibit or prevent biofilm formation on implants designed for long term implantation and/or decrease healing times in vivo in the presence of infection or other complications, e.g., open contaminated wounds and infections or closed wounds at risk for infection. Therefore, it is an object of the invention to provide improved coatings for biomedical implants that inhibit or prevent biofilm formation. It is also an object of the invention to provide improved coatings for implants that decrease healing times in vivo in the presence of infection or other complications, e.g., open contaminated wounds and infections or closed wounds at risk for infection. SUMMARY OF THE INVENTION Implants coated with an antimicrobial coating and methods of making and using, are described herein. The coating or the polymer in the coating is non-leaching, hemocompatible, and stable in vivo, e.g., non-degradable for a specified period of time. The material may be non-biodegradable or may degrade after a certain period of time. In one embodiment, the implant is an orthopedic or dental implant, such as implants that replace bone or provide fixation to bone, replace articulating surfaces of a joint, provide abutment for a prosthetic, or combinations thereof. In another embodiment, the implant is for ear, nose, and/or throat (“ENT”) applications. In yet another embodiment, the implant is a cardiovascular device such as cardiac valves, alloplastic vessel wall supports, or total artificial heart implant. In some embodiments, the implant is an ophthalmological implant. In some embodiments, the implant is not an ophthalmological implant. The polymer can be covalently or non-covalently associated with the surface; however, in particular embodiments, the polymer is non-covalently associated with the surface. The polymer can be applied by a variety of techniques in the art including, but not limited to, spraying, wetting, immersing, dipping, such as dip coating (e.g., intraoperative dip coating), painting, or otherwise applying a hydrophobic, polycationic polymer to a surface of the implant. The implant can be made from a variety of materials including, but not limited to, metallic materials (e.g., NiTi alloys, stainless steel, titanium or alloys thereof); metal oxides; non-degradable polymeric materials (e.g., polypropylene (PP), polyethylene (PE), polyacetylene, polystyrene, TEFLON®, poly(vinyl chloride) (PVC), polyolefin copolymers, poly(methyl methacrylate)); biodegradable/bioresorbable materials (e.g., collagen, cellulosic polymers, polysaccharides, poly(glycolic acid), poly(L-lactic acid) (PLLA), a polydioxanone (PDA), or racemic poly(lactic acid), polyurethane (PU), polycarbonates, polyetherketone (PEEK), polyesters (e.g., poly(ethylene terephthalate), polyamides (nylon); fluoroplastics, and other materials, such as porcelain; ceramic; allogenic or xenogenic bone or bone matrix; genetically engineered bone; and combinations thereof. In some embodiments, the implants is a prostheses, implant as artificial substitutes for body parts, and materials inserted into tissue for functional, cosmetic, or therapeutic purposes. Prostheses can be functional, as in the case of artificial arms and legs; cosmetic, as in the case dermal filler; and therapeutic as in the case of implants surgically inserted or grafted into the body and intended to replace non-functioning organs. Exemplary orthopedic and dental implants include, but are not limited to, wires, Kirschner wires, bone plates, screws, pins, tacks, rods, nails, nuts, bolts, washers, spikes, buttons, wires, fracture plates, reconstruction and stabilizer devices, endo- and exoprostheses (articulating and non-articulating), intraosseous transcutaneous prostheses, spacers, mesh, implant abutments, anchors, barbs, clamps, suture, interbody fusion devices, tubes of any geometry, scaffolds, and combinations thereof. Exemplary dental implants include root devices, such as those made from titanium, used to support restorations that resemble a tooth or group of teeth to replace missing teeth. Exemplary cardiovascular implants are cardiac valves or alloplastic vessel wall supports, total artificial heart implants, ventricular assist devices, vascular grafts, stents, electrical signal carrying devices such as pacemaker and neurological leads, defibrillator leads, and the like. Exemplary ENT implants include, but are not limited to, ear tubes, ventilation tubes, endotracheal tubes, cochlear implants and bone anchored hearing devices. In some embodiments, the antimicrobial coating is a hydrophobic, polycationic polymer. In some embodiments, the hydrophobic polycationic polymer is an N-alkylated polyethylenimine with various alkyl chain lengths such as N,N-dodecyl,methyl-polyethylenimine or N,N-hexyl,methyl-polyethylenimine. In other embodiments, the polymer is an poly(4-vinyl-N-alkylpyridine). As shown in the examples below demonstrating in vivo efficacy, clinical observations, digital radiography, and a battery of well-accepted ex vivo analytical methods show that the presence of a hydrophobic polycationic polymer coating, such as N,N-dodecyl,methyl-PEI coating on the surface of a metal implant, was effective in eliminating the clinical signs of infection in vivo in a large animal infection model. Moreover, the coated plates supported bone healing, and in fact decreased healing times, even in the presence of significant bacterial contamination compared to a control. Animals treated with coated implants also exhibited overall less inflammation of the soft tissue envelope, more bridging callus formation, no macroscopic evidence of purulent debris, and a macroscopically more stable osteotomy at one month. The implants described herein can be used to treat open fractures or wounds where infection is present or which are prone to infection, particular traumatic injuries, such as battlefield injuries or injuries that occur at a location which is removed from medical facilities. In such situations, treatment must be rendered immediately in order to stabilize the fracture. The conditions under which treatment is rendered are typically not sterile and so the potential for infection is high. Further, it may be some time before the patient reaches a medical facility where the wound can be closed. Therefore, the use of the implants descried herein can be used to effectively treat such injuries in the presence of infection. BRIEF DESCRIPTION OF THE DRAWINGS FIG. 1 a schematic showing the protocols for in vitro validation, animal model testing, and equine trial of coated implants. FIG. 2 is a schematic showing cohort breakdown of animals used in the study in Example 1. FIG. 3 is a graph showing colony counts from coated (treatment) and uncoated (control) LCP chips challenged with S. aureus in vitro. To examine and compare the activity of the N,N-dodecyl,methyl-PEI-coated and uncoated LCP chips against adherent organisms samples were incubated in 5 mL of 104 11 CFU of S. aureus for 16 h at 37ÿC. The medium was then removed, and plate samples were washed to remove loose, non-adherent bacteria prior to re-incubation for 4 h to encourage adherent bacteria to proliferate. Sonicates were cultured for microbiological analysis, serial diluted and spiral plated for cfu enumeration. Mean viable cfu (+SEM) recovered from inoculum of LCP chip cultures are shown for growth control (grey bars) with sonicates of uncoated and coated LCP chips respectively (black bars). FIG. 4 is a graph showing the mean radiographic scores for all sheep by three independent reviewers. Resultant scores for the control group were significantly higher when compared to scores obtained from animals treated with N,N-dodecyl,methyl-PEI-coated LCPs (p<0.00012). Treatment group animals overall showed signs of normal bone healing while control animals exhibited radiographic signs consistent with septic osteomyelitis. FIG. 5 is a graph showing mean histology scores for the treatment and control groups. DETAILED DESCRIPTION OF THE INVENTION I. Definitions “Biocompatible”, as used herein, means the ability of an implant to perform its desired function with respect to a medical therapy, without eliciting any undesirable local or systemic effects in the recipient or beneficiary of that therapy. “Contacting” as used herein refers to any means for coating a hydrophobic polymer, such as a hydrophobic polycationic polymer, on a surface. Contacting can include, but is not limited to, intraoperative dip-coating, spraying, wetting, immersing, dipping, painting, bonding or adhering, stepwise surface derivatization, or otherwise providing a surface with a compound with the hydrophobic, polycationic polymer. The polymer can be covalently or non-covalently attached to the surface. In some embodiments, the polymer is non-covalently associated with the surface. “Coating”, as used herein, refers to any temporary, semipermanent or permanent layer, covering or surface. A coating can be applied as a gas, vapor, liquid, paste, semi-solid or solid. In addition a coating can be applied as a liquid and solidified into a hard coating. Elasticity can be engineered into coatings to accommodate pliability, e.g. swelling or shrinkage, of the surface to be coated. A “component” is a part of an apparatus that is structurally integrated with that apparatus. A component may be applied to a surface of an apparatus, contained within the substance of the apparatus, retained in the interior of the apparatus, or any other arrangement whereby that part is an integral element of the structure of the apparatus. As an example, the silicone covering surrounding the mechanical part of a pacemaker is a component of the pacemaker. A component may be the lumen of an apparatus where the lumen performs some function essential to the overall function of the apparatus. The lumen of a tissue expander port is a component of the tissue expander. A component can refer to a reservoir or a discrete area within the apparatus specifically adapted for the delivery of a fluid to a surface of the apparatus. A reservoir within an implantable drug delivery device is a component of that device. The phrase “effective amount”, as used herein, generally refers to the amount of the antimicrobial coating applied to the implant in order to provide one or more clinically measurable endpoints, such as uncomplicated fracture healing or tissue remodeling in the presence of bacterial contamination or infection. An “implant” is any object intended for placement in the body of a mammal, such as a human, that is not a living tissue. Implants include naturally derived objects that have been processed so that their living tissues have been devitalized. As an example, bone grafts can be processed so that their living cells are removed, but so that their shape is retained to serve as a template for ingrowth of bone from a host. As another example, naturally occurring coral can be processed to yield hydroxyapatite preparations that can be applied to the body for certain orthopedic and dental therapies. An implant can also be an article comprising artificial components. The term “implant” can be applied to the entire spectrum of medical devices intended for placement in a human body or that of a mammal, including orthopedic applications, dental applications, ear, nose, and throat (“ENT”) applications, and cardiovascular applications. In some embodiments, the implant is an orthopedic implant. An “orthopedic implant” is defined as an implant which replaces bone or provides fixation to bone, replaces articulating surfaces of a joint, provides abutment for a prosthetic, or combinations thereof. In another embodiment, the implant is a dental implant. In other embodiments, the implant is an ENT implant. An ENT implant is defined as an implant which restores structure and/or function to ears, nose, and/or throat. In other embodiments the implant is a cosmetic implant. A cosmetic implant is defined as an implant that provides tissue support for example dermal fillers or structural support such as chins for reconstructive craniomaxillofacial surgery. The implants can be made of a variety of biocompatible materials, including: metals, ceramics, polymers, gels and fluids not normally found within the human body. Examples of polymers useful in fabricating medical devices/implants include such polymers as silicones, rubbers, latex, plastics, thermoplastics, polyanhydrides, polyesters, polyorthoesters, polyamides, polyacrylonitrile, polyurethanes, polyethylene, polytetrafluoroethylene, polyethylenetetraphthalate, polyphazenes, and fluoroplastics. Medical devices can also be fabricated using certain naturally-occurring materials or treated naturally-occurring materials. Implants can include any combination of artificial materials, combinations selected because of the particular characteristics of the components. For example, a hip implant can include a combination of a metallic shaft to bear the weight, a ceramic artificial joint and a polymeric glue to affix the structure to the surrounding bone. Implants can reside wholly in the body or partly in the body and partly outside the body. Implants can be intended for short-term or long-term residence where they are positioned. The terms “infectious microorganisms” or “infectious agents” as used herein refers to disease causing or contributing bacteria (including Gram-negative and Gram-positive organisms, such as Staphylococci (e.g. Staphylococcus aureus, Staphylococcus epidermis), Enterococcus sp. (e.g., E. faecalis), Pseudomonas sp. (e.g., P. aeruginosa), Escherichia sp. (e.g., E. coli), Proteus sp. (e.g., P. mirabilis)), fungi (including Candida albicans), viruses, and protists. The term “soluble” refers to the ability to be loosened or dissolved. The term “surface” or “surfaces” can mean any surface of any solid or semi-solid material, including glass, plastics, metals, polymers, and like. It can include surfaces constructed out of more than one material, including coated surfaces. Biofilm formation with health implications can involve those surfaces in all health-related environments, including surfaces found in medical environments and those surfaces in industrial or residential environments that are involved in those functions essential to well-being like nutrition, sanitation and the prevention of disease. A surface of an article adapted for use in a medical environment can be capable of sterilization using autoclaving, biocide exposure, irradiation or gassing techniques like ethylene oxide exposure. Surfaces found in medical environments include the inner and outer aspects of various instruments and devices, whether disposable or intended for repeated uses. Examples include the entire spectrum of articles adapted for medical use, including scalpels, needles, scissors and other devices used in invasive surgical, therapeutic or diagnostic procedures; implantable medical devices, including artificial blood vessels, catheters and other devices for the removal or delivery of fluids to patients, artificial hearts, artificial kidneys, orthopedic pins, plates and implants; catheters and other tubes (including urological and biliary tubes, endotracheal tubes, ear tubes, peripherably insertable central venous catheters, dialysis catheters, long term tunneled central venous catheters peripheral venous catheters, short term central venous catheters, arterial catheters, pulmonary catheters, Swan-Ganz catheters, urinary catheters, peritoneal catheters), urinary devices (including long term urinary devices, tissue bonding urinary devices, artificial urinary sphincters, urinary dilators), shunts (including ventricular or arterio-venous shunts); prostheses (including breast implants, penile prostheses, vascular grafting prostheses, heart valves, artificial joints, artificial larynxes, otological implants), vascular catheter ports, wound drain tubes, hydrocephalus shunts, pacemakers and implantable defibrillators, and the like. Other examples will be readily apparent to practitioners in these arts. The term ‘Gram-positive bacteria’ is an art recognized term for bacteria characterized by having as part of their cell wall structure peptidoglycan as well as polysaccharides and/or teichoic acids and are characterized by their blue-violet color reaction in the Gram-staining procedure. Representative Gram-positive bacteria include: Actinomyces spp., Bacillus anthracis, Bifidobacterium spp., Clostridium botulinum, Clostridium perfringens, Clostridium spp., Clostridium tetani, Corynebacterium diphtheriae, Corynebacterium jeikeium, Enterococcus faecalis, Enterococcus faecium, Erysipelothrix rhusiopathiae, Eubacterium spp., Gardnerella vaginalis, Gemella morbillorum, Leuconostoc spp., Mycobacterium abcessus, Mycobacterium avium complex, Mycobacterium chelonae, Mycobacterium fortuitum, Mycobacterium haemophilium, Mycobacterium kansasii, Mycobacterium leprae, Mycobacterium marinum, Mycobacterium scrofulaceum, Mycobacterium smegmatis, Mycobacterium terrae, Mycobacterium tuberculosis, Mycobacterium ulcerans, Nocardia spp., Peptococcus niger, Peptostreptococcus spp., Proprionibacterium spp., Staphylococcus aureus, Staphylococcus auricularis, Staphylococcus capitis, Staphylococcus cohnii, Staphylococcus epidermidis, Staphylococcus haemolyticus, Staphylococcus hominis, Staphylococcus lugdanensis, Staphylococcus saccharolyticus, Staphylococcus saprophyticus, Staphylococcus schleiferi, Staphylococcus similans, Staphylococcus warneri, Staphylococcus xylosus, Streptococcus agalactiae (group B streptococcus), Streptococcus anginosus, Streptococcus bovis, Streptococcus canis, Streptococcus equi, Streptococcus milleri, Streptococcus mitior, Streptococcus mutans, Streptococcus pneumoniae, Streptococcus pyogenes (group A streptococcus), Streptococcus salivarius, and Streptococcus sanguis. The term “Gram-negative bacteria” is an art recognized term for bacteria characterized by the presence of a double membrane surrounding each bacterial cell. Representative Gram-negative bacteria include Acinetobacter calcoaceticus, Actinobacillus actinomycetemcomitans, Aeromonas hydrophila, Alcaligenes xylosoxidans, Bacteroides, Bacteroides fragilis, Bartonella bacilliformis, Bordetella spp., Borrelia burgdorferi, Branhamella catarrhalis, Brucella spp., Campylobacter spp., Chlamydia pneumoniae, Chlamydia psittaci, Chlamydia trachomatis, Chromobacterium violaceum, Citrobacter spp., Eikenella corrodens, Enterobacter aerogenes, Escherichia coli, Flavobacterium meningosepticum, Fusobacterium spp., Haemophilus influenzae, Haemophilus spp., Helicobacter pylori, Klebsiella spp., Legionella spp., Leptospira spp., Moraxella catarrhalis, Morganella morganii, Mycoplasma pneumoniae, Neisseria gonorrhoeae, Neisseria meningitidis, Pasteurella multocida, Plesiomonas shigelloides, Prevotella spp., Proteus spp., Providencia rettgeri, Pseudomonas aeruginosa, Pseudomonas spp., Rickettsia prowazekii, Rickettsia rickettsii, Rochalimaea spp., Salmonella spp., Salmonella typhi, Serratia marcescens, Shigella spp., Treponema carateum, Treponema pallidum, Treponema pallidum endemicum, Treponema pertenue, Veillonella spp., Vibrio cholerae, Vibrio vulnificus, Yersinia enterocolitica, Yersinia pestis. “Non-leaching”, as used herein, generally means that no appreciable amount of the bactericidal polymer is released from the coating on the implant over a particular time period. One way to ascertain that a coated material is non-leaching is to shake it in an aqueous solution over a certain period of time, e.g., 24 hours, or a week, or a month, then remove it, and inoculate the remaining solution with representative bacteria. If the bacteria thus introduced grow and multiply similarly to (e.g., statistically indistinguishably from) those in controls (i.e., the fresh aqueous solution and/or that fresh solution incubated with the uncoated material for the same time period and under the same conditions as the coated material), then the coating is considered non-leaching. In one embodiment, “non-leaching” means that the implant retains greater than 50%, 55%, 60%, 65%, 70%, 75%, 80%, 85%, 90%, 95%, 99% by weight of the coating over the course of 7, 14, 30, 60, 90, 100, or greater in phosphate buffered saline (PBS), media, serum, or in vivo. “Substantially non-toxic”, as used herein, means a surface that is substantially non-hemolytic and substantially non-cytotoxic. “Antimicrobial” refers to the ability of a material to inhibit the growth of (i.e., bacteriostatic) or kill (i.e., bacteriocidal) microorganisms, such as bacteria, yeast, fungi, mycoplasma, viruses or virus infected cells, and/or protozoa. “In vivo stability” refers to materials which are not degraded in an organism over a defined period of time. “Non-degradable” or “stable”, as used herein synonymously, refers to material compositions that do not react within a biological environment either hydrolytically, reductively, enzymatically or oxidatively to cleave into smaller pieces. Preferably non-degradable materials retain>25%, >50%, >75%, >90%, >95%, or >99% of their original material properties such as surface contact angle, non-fouling, and/or antimicrobial activity for a time of 7, 14, 30, 120, 365, or 1000 days in media, serum, or in vivo. “Coating”, as used herein, refers to any temporary, semi-permanent or permanent layer, or layers, treating or covering a surface. A coating can be a gas, vapor, liquid, paste, semi-solid or solid. In addition, a coating can be applied as a liquid and solidified into a solid coating. “Substantially hemocompatible”, as used herein, means that the composition is substantially non-hemolytic, in addition to being non-thrombogenic and non-immunogenic, as tested by appropriately selected assays for thrombosis, coagulation, and complement activation as described in ISO 10993-4. “Hydrophobic”, as used herein, generally means that the material has a greater affinity for, and thus solubility in, organic solvents compared to water. Hydrophobicity can be quantified by measuring its partition coefficient between water (or a buffered aqueous solution) and a water-immiscible organic solvent, such as octanol, ethyl acetate, methylene chloride, or methyl tert-butyl ether. If after equilibration a greater concentration of the compound is attained in the organic solvent than in water, then the compound is considered hydrophobic. Hydrophobicity can also be evaluated by measuring the surface contact angle. In some embodiments, the surface angle is greater than about 70, 75, 80, 85, 90, 95, 100, 105, 110, or 115 degrees when measured using a goniometer. An amphipathic molecule or compound is an art recognized term where one end of the molecule or compound is polar and another end is non-polar. The term “polar” is art-recognized and generally means that the compound has a dipole moment greater than zero. A polar compound contains substances with asymmetric charge distribution (i.e., electron density). In general, a non-polar solvent will dissolve non-polar compounds, and a polar solvent will dissolve polar compounds, e.g. water, a polar substance, dissolves other polar substances, for example, sugars, amino acids, most salts, and proteins. An amphipathic (Amphiphilic) compound has a portion which is soluble in aqueous solvents, and a portion which is insoluble aqueous solvents. For example, sodium dodecyl sulfate, CH3(CH2)11OSO3Na is amphipathic (or amphiphilic) because its polar sodium sulfate moiety is highly soluble in water and its non-polar dodecyl moiety is highly insoluble in water. The term “ligand” refers to a compound that binds at the receptor site. The term “heteroatom” as used herein means an atom of any element other than carbon or hydrogen. Preferred heteroatoms are boron, nitrogen, oxygen, phosphorus, sulfur and selenium. The term “electron-withdrawing group” is recognized in the art, and denotes the tendency of a substituent to attract valence electrons from neighboring atoms, i.e., the substituent is electronegative with respect to neighboring atoms. A quantification of the level of electron-withdrawing capability is given by the Hammett sigma (.sigma.) constant. This well known constant is described in many references, for instance, J. March, Advanced Organic Chemistry, McGraw Hill Book Company, New York, (1977 edition) pp. 251-259. The Hammett constant values are generally negative for electron donating groups (σ [P]=−0.66 for NH2) and positive for electron withdrawing groups (σ [P]=0.78 for a nitro group), σ [P] indicating para substitution. Exemplary electron-withdrawing groups include nitro, acyl, formyl, sulfonyl, trifluoromethyl, cyano, chloride, and the like. Exemplary electron-donating groups include amino, methoxy, and the like. The term “alkyl” refers to the radical of saturated aliphatic groups, including straight-chain alkyl groups, branched-chain alkyl groups, cycloalkyl(alicyclic) groups, alkyl substituted cycloalkyl groups, and cycloalkyl substituted alkyl groups. In preferred embodiments, a straight chain or branched chain alkyl has 30 or fewer carbon atoms in its backbone (e.g., C1-C30 for straight chain, C3-C30 for branched chain), and preferably 20 or fewer, more preferably 10 or fewer. Likewise, preferred cycloalkyls have from 3-10 carbon atoms in their ring structure, and more preferably have 5, 6 or 7 carbons in the ring structure. Unless the number of carbons is otherwise specified, “lower alkyl” as used herein means an alkyl group, as defined above, but having from one to ten carbons, more preferably from one to six carbon atoms in its backbone structure. Likewise, “lower alkenyl” and “lower alkynyl” have similar chain lengths. Preferred alkyl groups are lower alkyls. In preferred embodiments, a substituent designated herein as alkyl is a lower alkyl. The term “aralkyl”, as used herein, refers to an alkyl group substituted with an aryl group (e.g., an aromatic or heteroaromatic group). The terms “alkenyl” and “alkynyl” refer to unsaturated aliphatic groups analogous in length and possible substitution to the alkyls described above, but that contain at least one double or triple bond respectively. The term “aryl” as used herein includes 5-, 6- and 7-membered single-ring aromatic groups that may include from zero to four heteroatoms, for example, benzene, pyrrole, furan, thiophene, imidazole, oxazole, thiazole, triazole, pyrazole, pyridine, pyrazine, pyridazine and pyrimidine, and the like. Those aryl groups having heteroatoms in the ring structure may also be referred to as “aryl heterocycles” or “heteroaromatics.” The aromatic ring can be substituted at one or more ring positions with such substituents as described above, for example, halogen, azide, alkyl, aralkyl, alkenyl, alkynyl, cycloalkyl, hydroxyl, alkoxyl, amino, nitro, sulfhydryl, imino, amido, phosphonate, phosphinate, carbonyl, carboxyl, silyl, ether, alkylthio, sulfonyl, sulfonamido, ketone, aldehyde, ester, heterocyclyl, aromatic or heteroaromatic moieties, —CF3, —CN, or the like. The term “aryl” also includes polycyclic ring systems having two or more cyclic rings in which two or more carbons are common to two adjoining rings (the rings are “fused rings”) wherein at least one of the rings is aromatic, e.g., the other cyclic rings can be cycloalkyls, cycloalkenyls, cycloalkynyls, aryls and/or heterocyclyls. The terms ortho, meta and para apply to 1,2-, 1,3- and 1,4-disubstituted benzenes, respectively. For example, the names 1,2-dimethylbenzene and ortho-dimethylbenzene are synonymous. The terms “heterocyclyl” or “heterocyclic group” refer to 3- to 10-membered ring structures, more preferably 3- to 7-membered rings, whose ring structures include one to four heteroatoms. Heterocycles can also be polycycles. Heterocyclyl groups include, for example, thiophene, thianthrene, furan, pyran, isobenzofuran, chromene, xanthene, phenoxathin, pyrrole, imidazole, pyrazole, isothiazole, isoxazole, pyridine, pyrazine, pyrimidine, pyridazine, indolizine, isoindole, indole, indazole, purine, quinolizine, isoquinoline, quinoline, phthalazine, naphthyridine, quinoxaline, quinazoline, cinnoline, pteridine, carbazole, carboline, phenanthridine, acridine, pyrimidine, phenanthroline, phenazine, phenarsazine, phenothiazine, furazan, phenoxazine, pyrrolidine, oxolane, thiolane, oxazole, piperidine, piperazine, morpholine, lactones, lactams such as azetidinones and pyrrolidinones, sultams, sultones, and the like. The heterocyclic ring can be substituted at one or more positions with such substituents as described above, as for example, halogen, alkyl, aralkyl, alkenyl, alkynyl, cycloalkyl, hydroxyl, amino, nitro, sulfhydryl, imino, amido, phosphonate, phosphinate, carbonyl, carboxyl, silyl, ether, alkylthio, sulfonyl, ketone, aldehyde, ester, a heterocyclyl, an aromatic or heteroaromatic moiety, —CF3, —CN, or the like. The terms “polycyclyl” or “polycyclic group” refer to two or more rings (e.g., cycloalkyls, cycloalkenyls, cycloalkynyls, aryls and/or heterocyclyls) in which two or more carbons are common to two adjoining rings, e.g., the rings are “fused rings”. Rings that are joined through non-adjacent atoms are termed “bridged” rings. Each of the rings of the polycycle can be substituted with such substituents as described above, as for example, halogen, alkyl, aralkyl, alkenyl, alkynyl, cycloalkyl, hydroxyl, amino, nitro, sulfhydryl, imino, amido, phosphonate, phosphinate, carbonyl, carboxyl, silyl, ether, alkylthio, sulfonyl, ketone, aldehyde, ester, a heterocyclyl, an aromatic or heteroaromatic moiety, —CF3, —CN, or the like. The term “carbocycle”, as used herein, refers to an aromatic or nonaromatic ring in which each atom of the ring is carbon. As used herein, the term “nitro” means —NO2; the term “halogen” designates —F, —Cl, —Br or —I; the term “sulfhydryl” means —SH; the term “hydroxyl” means —OH; and the term “sulfonyl” means —SO2—. The terms “amine” and “amino” are art-recognized and refer to both unsubstituted and substituted amines, e.g., a moiety that can be represented by the general formula: wherein R9, R10, and R′10 each independently represent a group permitted by the rules of valence. The term “acylamino” is art-recognized and refers to a moiety that can be represented by the general formula: wherein R9 is as defined above, and R′11 represents a hydrogen, an alkyl, an alkenyl or —(CH2)m—R8, where m and R8 are as defined above. The term “amido” is art recognized as an amino-substituted carbonyl and includes a moiety that can be represented by the general formula: wherein R9, R10 are as defined above. Preferred embodiments of the amide will not include imides which may be unstable. The term “alkylthio” refers to an alkyl group, as defined above, having a sulfur radical attached thereto. In preferred embodiments, the “alkylthio” moiety is represented by one of —S-alkyl, —S-alkenyl, —S-alkynyl, and S—(CH2)8—R8, wherein m and R8 are defined above. Representative alkylthio groups include methylthio, ethyl thio, and the like. The term “carbonyl” is art recognized and includes such moieties as can be represented by the general formula: wherein X is a bond or represents an oxygen or a sulfur, and R11 represents a hydrogen, an alkyl, an alkenyl, —(CH2)m—R8 or a pharmaceutically acceptable salt, R′11 represents a hydrogen, an alkyl, an alkenyl or —(CH2)m—R8, where m and R8 are as defined above. Where X is an oxygen and R11 or R′11 is not hydrogen, the formula represents an “ester”. Where X is an oxygen, and R11 is as defined above, the moiety is referred to herein as a carboxyl group, and particularly when R11 is a hydrogen, the formula represents a “carboxylic acid”. Where X is an oxygen, and R′11 is hydrogen, the formula represents a “formate”. In general, where the oxygen atom of the above formula is replaced by sulfur, the formula represents a “thiolcarbonyl” group. Where X is a sulfur and R11 or R′11 is not hydrogen, the formula represents a “thiolester.” Where X is a sulfur and R11 is hydrogen, the formula represents a “thiolcarboxylic acid.” Where X is a sulfur and R′11 is hydrogen, the formula represents a “thiolformate.” On the other hand, where X is a bond, and R11 is not hydrogen, the above formula represents a “ketone” group. Where X is a bond, and R11 is hydrogen, the above formula represents an “aldehyde” group. The terms “alkoxyl” or “alkoxy” as used herein refers to an alkyl group, as defined above, having an oxygen radical attached thereto. Representative alkoxyl groups include methoxy, ethoxy, propyloxy, tert-butoxy and the like. An “ether” is two hydrocarbons covalently linked by an oxygen. Accordingly, the substituent of an alkyl that renders that alkyl an ether is or resembles an alkoxyl, such as can be represented by one of —O-alkyl, —O-alkenyl, —O-alkynyl, —O—(CH2)m—R8, where m and R8 are described above. The term “sulfonate” is art recognized and includes a moiety that can be represented by the general formula: in which R41 is an electron pair, hydrogen, alkyl, cycloalkyl, or aryl. The terms triflyl, tosyl, mesyl, and nonaflyl are art-recognized and refer to trifluoromethanesulfonyl, p-toluenesulfonyl, methanesulfonyl, and nonafluorobutanesulfonyl groups, respectively. The terms triflate, tosylate, mesylate, and nonaflate are art-recognized and refer to trifluoromethanesulfonate ester, p-toluenesulfonate ester, methanesulfonate ester, and nonafluorobutanesulfonate ester functional groups and molecules that contain said groups, respectively. The abbreviations Me, Et, Ph, Tf, Ts, Ms represent methyl, ethyl, phenyl, trifluoromethanesulfonyl, nonafluorobutanesulfonyl, p-toluenesulfonyl and methanesulfonyl, respectively. A more comprehensive list of the abbreviations utilized by organic chemists of ordinary skill in the art appears in the first issue of each volume of the Journal of Organic Chemistry; this list is typically presented in a table entitled Standard List of Abbreviations. The abbreviations contained in said list, and all abbreviations utilized by organic chemists of ordinary skill in the art are hereby incorporated by reference. The term “sulfate” is art recognized and includes a moiety that can be represented by the general formula: in which R41 is as defined above. The term “sulfonylamino” is art recognized and includes a moiety that can be represented by the formula The term “sulfamoyl” is art-recognized and includes a moiety that can be represented by The term “sulfonyl”, as used herein, refers to a moiety that can be represented by the general formula: in which R44 is selected from the group consisting of hydrogen, alkyl, alkenyl, alkynyl, cycloalkyl, heterocyclyl, aryl, or heteroaryl. The term “sulfoxido” as used herein, refers to a moiety that can be represented by the general formula: in which R44 is selected from the group consisting of hydrogen, alkyl, alkenyl, alkynyl, cycloalkyl, heterocyclyl, aralkyl, or aryl. Analogous substitutions can be made to alkenyl and alkynyl groups to produce, for example, aminoalkenyls, aminoalkynyls, amidoalkenyls, amidoalkynyls, iminoalkenyls, iminoalkynyls, thioalkenyls, thioalkynyls, carbonyl-substituted alkenyls or alkynyls. As used herein, the definition of each expression, e.g. alkyl, m, n, etc., when it occurs more than once in any structure, is intended to be independent of its definition elsewhere in the same structure. It will be understood that “substitution” or “substituted with” includes the implicit proviso that such substitution is in accordance with permitted valence of the substituted atom and the substituent, and that the substitution results in a stable compound, e.g., which does not spontaneously undergo transformation such as by rearrangement, cyclization, elimination, etc. As used herein, the term “substituted” is contemplated to include all permissible substituents of organic compounds. In a broad aspect, the permissible substituents include acyclic and cyclic, branched and unbranched, carbocyclic and heterocyclic, aromatic and nonaromatic substituents of organic compounds. Illustrative substituents include, for example, those described herein above. The permissible substituents can be one or more and the same or different for appropriate organic compounds. For purposes of this invention, the heteroatoms such as nitrogen may have hydrogen substituents and/or any permissible substituents of organic compounds described herein which satisfy the valences of the heteroatoms. This invention is not intended to be limited in any manner by the permissible substituents of organic compounds. The phrase “protecting group” as used herein means temporary substituents which protect a potentially reactive functional group from undesired chemical transformations. Examples of such protecting groups include esters of carboxylic acids, silyl ethers of alcohols, and acetals and ketals of aldehydes and ketones, respectively. The field of protecting group chemistry has been reviewed (Greene, T. W.; Wuts, P. G. M. Protective Groups in Organic Synthesis, 2.sup.nd ed.; Wiley: New York, 1991). Contemplated equivalents of the compounds described above include compounds which otherwise correspond thereto, and which have the same general properties thereof (e.g., functioning as analgesics), wherein one or more simple variations of substituents are made which do not adversely affect the efficacy of the compound in binding to opioid receptors. In general, the compounds of the present invention may be prepared by the methods illustrated in the general reaction schemes as, for example, described below, or by modifications thereof, using readily available starting materials, reagents and conventional synthesis procedures. In these reactions, it is also possible to make use of variants which are in themselves known, but are not mentioned here. For purposes of this invention, the chemical elements are identified in accordance with the Periodic Table of the Elements, CAS version, Handbook of Chemistry and Physics, 67th Ed., 1986-87, inside cover. II. Compositions Orthopedic implants coated with one or more non-leaching, antimicrobial, hydrophobic polymers particularly one or more polycationic polymers, are described herein. “Polycationic polymer”, as used herein, refers to polymers whose net charge is electropositive. The coated implants described herein show no evidence of leaching of the antimicrobial coating at 90 days post-op as plates coated with the antimicrobial polymer(s) exhibit the same or a similar level of antimicrobial activity compared to freshly prepared plates. In one embodiment, the coated implants described herein, when implanted in vivo, result in decreased healing times or tissue remodeling in the presence of bacterial contamination or infection compared to a control. A. Implants Implants coated with one or more hydrophobic, polycationic polymer coatings are described herein. In one embodiment, “implant” as used herein refers to a macroscopic composition including an device for implantation or a surface of a device for implantation and one or more hydrophobic, polycationic polymer coatings. In this embodiment, the term “implant” does not encompass nanoparticles and/or microparticles. “Macroscopic” as used herein generally refers to devices, implants, or compositions that can be viewed by the unaided eye. The implants can be formed from a variety of materials include polymers, metals, glass, ceramics, and combinations thereof. In one embodiment, the implant is an orthopedic implant. An “orthopedic implant” is defined as an implant which replaces bone or provides fixation to bone, replaces articulating surfaces of a joint, provides abutment for a prosthetic, or combinations thereof or assists in replacing bone or providing fixation to bone, replacing articulating surfaces of a joint, providing abutment for a prosthetic, and combinations thereof. Suitable orthopedic implants include, but are not limited to, wire, Kirschner wire, bone plates, screws, pins, tacs, rods, nails, nuts, bolts, washers, spikes, buttons, wires, fracture plates, reconstruction and stabilizer devices, endo- and exoprostheses (articulating and non-articulating), intraosseous transcutaneous prostheses, spacers, mesh, implant abutments, anchors, barbs, clamps, suture, interbody fusion devices, tubes of any geometry, scaffolds, and combinations thereof. In other embodiments, the implant is an ear, nose, and/or throat (“ENT”) implant. Exemplary ENT implants include, but are not limited to, ear tubes, endotracheal tubes, ventilation tubes, cochlear implants and bone anchored hearing devices. In other embodiments, the implant is a cardiovascular implant. Exemplary cardiovascular implants are cardiac valves or alloplastic vessel wall supports, total artificial heart implants, ventricular assist devices, vascular grafts, stents, electrical signal carrying devices such as pacemaker and neurological leads, defibrillator leads, and the like. The implant(s) can be prepared from a variety of materials. In some embodiments, the material is biocompatible. In some embodiments, the material is biocompatible and non-biodegradable. Exemplary materials include metallic materials, metal oxides, polymeric materials, including degradable and non-degradable polymeric materials, ceramics, porcelains, allogeneic, xenogenic bone or bone matrix; genetically engineered bone; and combinations thereof. Suitable metallic materials include, but are not limited to, metals and alloys based on titanium (such as nitinol, nickel titanium alloys, thermo-memory alloy materials), stainless steel, tantalum, palladium, zirconium, niobium, molybdenum, nickel-chrome, or certain cobalt alloys including cobalt-chromium and cobalt-chromium-nickel alloys such as ELGILOY® and PHYNOX®. Suitable ceramic materials include, but are not limited to, oxides, carbides, or nitrides of the transition elements such as titanium oxides, hafnium oxides, iridium oxides, chromium oxides, aluminum oxides, and zirconium oxides. Silicon based materials, such as silica, may also be used. Suitable polymeric materials include, but are not limited to, polystyrene and substituted polystyrenes, polyethylene, polypropylene, polyacetylene, polystyrene, TEFLON®, poly(vinyl chloride) (PVC), polyolefin copolymers, poly(urethane)s, polyacrylates and polymethacrylates, polyacrylamides and polymethacrylamides, polyesters, polysiloxanes, polyethers, poly(orthoester), poly(carbonates), poly(hydroxyalkanoate)s, polyfluorocarbons, PEEK®, Teflon® (polytetrafluoroethylene, PTFE), silicones, epoxy resins, Kevlar®, Dacron® (a condensation polymer obtained from ethylene glycol and terephthalic acid), nylon, polyalkenes, phenolic resins, natural and synthetic elastomers, adhesives and sealants, polyolefins, polysulfones, polyacrylonitrile, biopolymers such as polysaccharides and natural latex, collagen, cellulosic polymers (e.g., alkyl celluloses, etc.), polysaccharides, poly(glycolic acid), poly(L-lactic acid) (PLLA), a polydioxanone (PDA), or racemic poly(lactic acid), polycarbonates, (e.g., polyamides (nylon); fluoroplastics, carbon fiber, and blends or copolymers thereof. In one embodiment, the orthopedic implant is one designed to promote healing of any bone or bones in the mammalian skeleton in the presence of infection. The implants can be used to promote healing of large bones, such as the femur. In other embodiments, the implant is designed to restore structure, and/or function and/or to promote healing of the cardiovascular system (e.g., heart), ears, nose, and/or throat, particularly in the presence of bacterial contamination or infection. B. Hydrophobic Polymers The implants described herein are coated with an antimicrobial hydrophobic polymer. In particular embodiments, the hydrophobic polymer is a hydrophobic, polycationic polymer. The coating or the polymer in the coating is preferably non-leaching, hemocompatible, and stable in vivo, e.g., non-biodegradable for a specified period of time. The material may be non-biodegradable or may biodegrade after a certain period of time. In some embodiments, the hydrophobic polymer is a polycationic polymer. Suitable cationic polymers include, but are not limited to, poly(4-vinyl-N-alkylpyridinium halides), poly(methacryloyloxydidecylpyridinium halides), N-alkyl branched or linear polyethylene imine (PEI), and combinations thereof. Suitable poly(4-vinyl-N-alkylpyridinium halides) include polymers having the formula: Wherein, R represents individually for each occurrence hydrogen, alkyl, alkenyl, alkynyl, acyl, aryl, carboxylate, alkoxycarbonyl, aryloxycarbonyl, carboxamido, alkylamino, acylamino, alkoxyl, acyloxy, hydroxyalkyl, alkoxyalkyl, aminoalkyl, (alkylamino)alkyl, thio, alkylthio, thioalkyl, (alkylthio)alkyl, carbamoyl, urea, thiourea, sulfonyl, sulfonate, sulfonamido, sulfonylamino, or sulfonyloxy; R′ represents independently for each occurrence is substituted or unsubstituted alkyl, heteroalkyl, cycloalkyl, heterocycloalkyl, aryl, or heteroaryl; an alkylidene tether to a surface; or an acyl tether to a surface; Z represents independently for each occurrence Cl, Br, or I; and n is an integer less than or equal to about 5000, 4500, 4000, 3500, 3000, 2500, 2000, or 1500. In some embodiments, R′ is C4-C12, preferably C6-C12, more preferably C6-C10. In other embodiments, the polymer is a N,N-dialkyl branched or linear polyethylene imine (PEI) having the chemical structure shown below: wherein R and R′ are independently substituted or unsubstituted alkyl, heteroalkyl, cycloalkyl, heterocycloalkyl, aryl, or heteroaryl and n is an integer less than or equal to about 5000, 4500, 4000, 3500, 3000, 2500, 2000, or 1500. In some embodiments, R and R′ are the same. In other embodiments, R and R′ are different. In particular embodiments, R and R′ are different where R is a methyl group and R′ is a C6-C25, alkyl group, preferably C6-C20, more preferably C6-C18, most preferably C8-C18. In particular embodiments, R′ is hexyl, octyl, decyl, or dodecyl. Exemplary polymers include, but are not limited to, N,N-hexyl,methyl-PEI and N,N-dodecyl,methyl-PEI. In contrast, unmodified polyethylene imine (PEI) is generally characterized as a hydrophilic polymer. In still other embodiments, the polymer has the structural formula: wherein each of R1-R3 are independently hydrogen or substituted or unsubstituted alkyl, heteroalkyl, cycloalkyl, heterocycloalkyl, aryl, or heteroaryl, and n is an integer less than or equal to about 5000, 4500, 4000, 3500, 3000, 2500, 2000, or 1500. In some embodiments, at least one of R1-R3 is an alkyl group. In one embodiment, R1 and R3 are lower alkyl, such as methyl, and R2 is at least C10-C25, preferably C15-C25, more preferably C20-C25, most preferably C22. In still other embodiments, the polymer has the structural formula: wherein R is as defined above and is preferably C10-C25, preferably C15-C25, more preferably C20-C25, most preferably C18, n is an integer less than or equal to about 5000, 4500, 4000, 3500, 3000, 2500, 2000, or 1500, and m is an integer from 1-10, preferably 3-10, more preferably 3-6. In some embodiments, m is 3. In still other embodiments, the polymer has the structural formula: wherein each of R1-R3 are independently as defined above for R and n is an integer less than or equal to about 5000, 4500, 4000, 3500, 3000, 2500, 2000, or 1500. In one embodiment, R1-R3 are C6-C10, preferably C8-C10, more preferably about C8. The polymer can be any molecular weight provided the polymer is antimicrobial, i.e., bacteriostatic and/or bacteriocidal. The polymers above generally have a weight average molecular weight of at least 10,000 g/mol, at least 20,000 g/mol, at least 25,000 g/mol, at least 40,000 g/mol, at least 50,000 g/mol, at least 60,000 g/mol, at least 75,000 g/mol, at least 90,000 g/mol, at least 100,000 g/mol, at least 120,000 g/mol, at least 150,000 g/mol, at least 200,000 g/mol, at least 250,000 g/mol, at least 400,000 g/mol, at least 500,000 g/mol, or at least 750,000 g/mol. The polymer can be covalently and/or non-covalently associated with the surface. In one embodiment, the polymer is non-covalently associated with the surface. Non-covalent interactions include, but are not limited to, hydrophobic interactions, hydrophilic interactions, ionic interactions, hydrogen bonding, and binding partners which interact non-covalently. The hydrophobic nature of the polymer repels water and other aqueous solvent thus preventing dissolution of the polymer from the surface of the implant. In some embodiments, the polymer, such as a polycationic polymer, is non-covalently associated with the surface. In other embodiments, the polymer is non-covalently adhered or attached to the surface and is applied to the surface in the absence of a polyanionic polymer (e.g., polyelectrolyte complex). The polymer composition may contain one or more additives which modify the mechanical or physical properties of the polymer, such as plasticizers. The coated implants exhibit antimicrobial properties and prevent biofilm formation in vivo. For example, in one embodiment, bacterial cells are sprayed onto a substrate coated with a polymer. The percentage of bacteria killed is at least 90%, 91%, 92%, 93%, 94%, 95%, 96%, 97%, 98%, 99%, or greater. The range 90-99% includes all values between 90% and 99% including integer and non-integer values. Immobilized amphipathic polycations described herein and soluble cationic antimicrobials likely share a similar mechanism of attacking bacteria. Polycations, such as polymyxin B and antimicrobial cationic peptides, displace the divalent cations that hold together the negatively charged surface of the lipopolysaccharide network, thereby disrupting the outer membrane of Gram-negative bacteria like P. aeruginosa and E. coli. This in itself might be sufficient for a lethal outcome. It is also possible that, having destroyed the outer membrane permeability barrier, the cationic groups of the tethered polymers further penetrate into the inner membrane, producing leakage. Such “self-promoted penetration” with the subsequent damage of the inner membrane has been described for polymyxin. The action of immobilized polycations against the Gram-positive bacteria S. aureus and S. epidermidis probably requires penetration of the cationic groups across the thick cell wall to reach the cytoplasmic membrane. Bactericidal action of amphipathic cationic antiseptics, such as benzalkonium chloride or biguanidine chlorhexidine, against Gram-positive bacteria is due primarily to the disruption of the cytoplasmic membrane. The cell wall of S. aureus is some 30 nm thick. Therefore, polymers having an average length of at least 10-20, preferably 15-20 nm should be able to penetrate the cell wall. The antimicrobial activity of the claimed coatings is a consequence of their polymeric composition. Hydrophobic polycationic polymers possess a combination of charge and hydrophobicity that allows them to resist, by means of electrostatic repulsion, hydrophobic interchain aggregation, and yet able to penetrate bacterial cell membranes. III. Methods of Making Coated Substrates As discussed above, the polymer can be covalently or non-covalently associated with the surface. For those embodiments where the polymer is covalently associated with the surface, the polymer can
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