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Dania Koleilat Khatib. Retain current filters. Filter by Author - Remove Dr. Dania Koleilat Khatib filter Dr. Filter by Category. Clear filters. A high-ranking Hamas official last week announced that the group would dissolve its military wing and turn into a political party if Israel accepted a Palestinian state along the pre borders. Khalil Al-Hayya shocked the world with this statement, which comes as Israel is readying to invade In return, Tehran has promised that it will not harm Americans. US must restrain Netanyahu before he extends war to Lebanon. The Israeli government is threatening war with Lebanon. The Americans do not want a strike that could extend the Gaza conflict into a regional war. Hezbollah does not want a war and neither does Iran. Especially since mo US must coerce Israel into accepting a ceasefire. The brave secretary general of the UN, Antonio Guterres, last week invoked Article 99 of the UN Charter to ask for a ceasefire in Gaza in order to preserve international peace and security. This article had not been invoked in more than 50 years. US is punishing itself by undermining international law. Mike Johnson, the speaker of the House of the Representatives, last week said he was considering introducing legislation to sanction International Criminal Court officials. He added that the US does not consider any legal system to be above American sovereignty. However, this attitude greatly h Arab News, in collaboration with YouGov, the leading polling agency, launched a survey of 3, participants from 18 countries in September to answer the following question: What are Arabs expecting from the next US administration? The poll, which spans North Africa, the Levant and the Gulf, w US engagement necessary to keep Iran in check. This might have been a tactical move, but it could also be the tip of a comprehensive strategy. So far, there is no clarity on US policy toward Iran. The people in charge, whethe Assad is becoming more and more of a liability. The situation in US broke Iraq, now it must own its mistakes. Iraqi protesters hold a candlelight vigil for those killed during anti-government demonstrations in Karbala, south of Baghdad. Well, there is nothing new about Mohammed Tawfiq Allawi. UN-run safe zones could offer way out of Syria conflict. The area that has witnessed heavy figh Filter by author: - Remove Dr. Filter by main category:. Search form Search. Print Edition Read pdf version Subscribe now.

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Official websites use. Share sensitive information only on official, secure websites. Over the past decade, metallic drug-eluting implants have gained significance in orthopedic and dental applications for controlled drug release, specifically for preventing infection associated with implants. Recent studies showed that metallic implants loaded with drugs were substituted for conventional bare metal implants to achieve sustained and controlled drug release, resulting in a desired local therapeutic concentration. A number of secondary features can be provided by the incorporated active molecules, including the promotion of osteoconduction and angiogenesis, the inhibition of bacterial invasion, and the modulation of host body reaction. This paper reviews recent trends in the development of the metallic drug-eluting implants with various drug delivery systems in the past three years. There are various types of drug-eluting implants that have been developed to meet this purpose, depending on the drug or agents that have been loaded on them. These include anti-inflammatory drugs, antibiotics agents, growth factors, and anti-resorptive drugs. Keywords: implants, localized drug delivery, bioactive coatings, infection, biomaterials, bone tissue engineering. Joint reconstruction represents the largest share A majority of orthopedic implants are made of metals and their alloys, such as titanium Ti , tantalum Ta , magnesium Mg , zinc Zn , stainless steels, and cobalt Co -based alloys, due to their low-cost and stability \[ 5 , 6 \]. They offer an excellent combination of plasticity and toughness, along with favorable mechanical properties, that make them highly efficient \[ 7 \]. There are two types of implants: temporary fixation devices, such as bone plates, pins, and screws, and permanent implants, such as total joint replacements in orthopedics \[ 8 \]. There is the clinical application of common metal implants as shown in Figure 1 \[ 9 \]. The clinical application of common metal implants. Reprinted with permission from the reference \[ 9 \]. Implant stabilization and long-term success, largely depend on the quality of integration with the surrounding tissue \[ 10 \]. The implant material, the quality and quantity of formed surrounding bone tissue and the presence of microbial infection all play a crucial role in the integration of the surrounding tissue with the implant \[ 11 \]. In spite of the fact that metallic implants have good mechanical properties and are generally affordable, their insufficient biological activity poses a disadvantage \[ 12 , 13 \]. The low corrosion resistance, tendency to infection, lack of proper biological activities, and subsequent weak integration with contacted bone tissue are some of the primary concerns that drive to develop multifunctional and bioactive metallic implants that act as local drug delivery platforms \[ 13 , 14 , 15 \]. In order to influence the regeneration process dynamically, they are first supposed to interfere with the response of the host body, then increase the integration with the implant, promote osteoconduction and the angiogenesis on the surface of them, and finally slow down the microbial infection process. All these steps will lead to increased tissue healing speed \[ 16 , 17 , 18 \]. It is particularly promising to use localized therapeutic strategies because they have a better bioavailability, and they result in immediate bone healing as opposed to systemic therapies \[ 19 , 20 , 21 \]. An effective way to enhance bone healing and regeneration is to administer biologically active compounds that induce messages that influence bone healing in a controlled manner \[ 22 , 23 \]. Different types of locally delivered molecules can be used to treat musculoskeletal syndromes, including nonviral genes DNAs, RNAs , antibiotics, anti-inflammatory ingredients, proteins, growth factors, and enzymes \[ 26 \]. One of the most notable applications of drug-eluting implants in bone tissue engineering is the prevention of associated infections with dental implants and orthopedic implants \[ 27 , 28 , 29 , 30 \]. The majority of metal-based drug delivery involves embedding drugs into polymeric or ceramic coatings applied to metallic implants \[ 31 \]. There are also methods of incorporating the drug itself onto the metallic implant surface using covalent bonds, self-assembled layers, and silver nanoparticles \[ 32 , 33 \]. Meanwhile, deposition of polymer-based layers are believed to cause complications, such as loosening from the implantation site, changes in chemical composition in physicochemical media, and likely side effects due to the corrosion products \[ 34 , 35 \]. For this reason, many researchers have been investigating the use of inorganic coatings as drug delivery systems \[ 36 \]. There has been little attention given to metallic drug eluting systems in comparison with polymeric systems. This mini-review aims to summarize recent advancement in drug delivery systems on the surface of metallic implants, mainly for orthopedic and dental applications. In this review, we do not intend to provide an exhaustive synopsis of the field of drug delivery—which is vast—but highlight curiosities and advances between — about drug delivery systems on metallic implants. In the mentioned time period, various therapeutics substances, such as anti-inflammatory drugs, antibiotics agents, growth factors, and anti-resorptive drugs, have been loaded and eluted from metallic implants. It should be noted that most of the studies in this period concerned the development of drug-eluting implants based on Ti as a substrate, loaded with gentamicin as a therapeutic agent. Moreover, some of the studies have been focused on development of smart coatings as drug delivery platform on metallic implants. Foreign bodies such as implantable medical materials commonly trigger immune reactions and inflammatory cascades \[ 37 , 38 \]. Anti-inflammatory and immunosuppressive drugs can be delivered in various ways to counter inflammation, which is a vital factor affecting regeneration \[ 40 \]. The matrix or surface of metallic implants has been profitably used to deliver multifunction drug and anti-inflammatory drugs, such as betamethasone and dexamethasone, to reduce the kinetics of foreign body reactions around the implantation site and the production of fibrous capsules \[ 41 , 42 \]. In nanomedicine, recent advances have made it possible to deliver drugs over time while maintaining their bioactivity \[ 43 \]. It has been reported that 3 weeks after implanting silicon and platinum-polyimide neural probes with dexamethasone-loaded nanoparticles on the implant surface, tissues are significantly less prone to react with them \[ 44 , 45 \]. It is worth mentioning that cytokine delivery has also been proven to be an efficient method of modulating the immune response to implants, since they play an essential role in regulating immune cell phenotypic changes. It is possible to create a smart biomaterial by simply immersing porous ceramic coated implants in pharmaceutical solutions and growth factors that penetrate directly into coating pores \[ 48 \]. Initially, drugs were carried by stand-alone calcium phosphate Ca-P compounds deposited onto metal substrates \[ 49 , 50 \]. This review does not cover these topics and they can be found elsewhere \[ 51 \]. In this method, the micro-porous oxide layers are grown on a metallic substrate during oxidation process \[ 52 \]. The porous oxide layer can act as a polymer-free drug delivery platform \[ 53 \]. It was recently reported that an anti-inflammatory betamethasone sodium phosphate BSP drug was loaded into a PEO layer of Mg alloy \[ 53 \]. Reprinted with permission from the reference \[ 53 \]. Up to now, nanostructured drug loaded surfaces have been demonstrated to have anti-inflammatory, cytokine producing, and macrophage polarizing effects. The development of nanostructured drug-eluting surfaces has been associated with the formation of polarized macrophages by modulating the shape and plasticity of macrophages, stimulated by integrin beta signaling pathways. However, it is still unclear exactly how these immune-modulating mechanisms operate at a nano-scale. It is estimated that over half of all hospital acquired infections are caused by post-surgical implant-associated infections \[ 54 \]. As a result, synthetic orthopedic implants are commonly used to deliver antibiotics locally at the implantation site \[ 55 \]. Surgery and irrigation are typically performed to manage such infections, implant removal is often required, and extended antibiotic treatments are often needed \[ 57 \]. This can lead to trauma to the patient, prolonged hospitalizations, and serious social and health problems \[ 58 \]. Therefore, the development of implants that are intrinsically antibacterial will decrease the risks of upcoming complications and possibly reduce the large social and economic burden that may be associated with these complications \[ 58 \]. Surface topography and surface chemistry have been used to achieve anti-biofouling properties by integrating antibacterial agents into implants \[ 59 \]. Several implant-based strategies exist, including coatings, bone cement, composite materials, or polymethylmethacrylate PMMA beads loaded with antibacterial agents \[ 60 \]. The success of such approaches has been largely attributed to lower infection rates. However, their initial release profiles and burst releases have not been optimized \[ 60 \]. There are several downsides to the current methods, including inadequate bonding between coating and substrate. The retrieval surgery is also required to remove PMMA beads with non-biodegradability properties \[ 61 \]. Among the many antibiotic agents available, choosing the appropriate agent is vital since few antibiotics have been demonstrated to adversely affect osteogenic cells at bactericidal dosages \[ 62 \]. Nanotechnology has led to advances in the field of nanoscale surface modification for Ti implants for drug delivery \[ 63 \]. These nanoscale modifications in the range of 1— nm can increase protein attachment, enhance bone-implant contact, and improve osseointegration \[ 63 \]. Acid etching, electrochemical anodization, and lithography can be used to fabricate nano-topography on Ti \[ 64 \]. It is important to recognize that among these strategies, electrochemical anodization has been found to be the most reliable, cost-effective, and scalable technique to fabricate nanostructures on the surface of the Ti implants, such as titanium oxide TiO 2 nanotubes NT \[ 65 \]. The use of TiO 2 NT on Ti implants is a superb surface engineering technique and drug therapies can be enabled by using such technologies, which are capable of achieving excellent results \[ 66 , 67 \]. The finding of the study demonstrated the ability of Gly to inhibit the inflammatory response, induce macrophages to polarize towards an anti-inflammatory M2 phenotype, and generate anti-inflammatory cytokines, which enhance tissue regeneration. Reprinted with permission from the reference \[ 68 \]. In osteointegration, bone formation, remodeling, and impaired healing, growth factors GFs play an indisputable role in cell function at the local level as a large number of polypeptides \[ 69 \]. By accelerating osteoclastic resorption and promoting cell proliferation and differentiation, GFs are known to increase bone healing rate by stimulating the intricate biological cascades that occur during bone regeneration \[ 70 \]. Many osteogenic growth factors, including bone morphogenetic proteins BMPs , recombinant human bone morphogenetic proteins rhBMPs , transforming growth factors TGFs , insulin-like growth factors IGFs , and platelet-derived growth factors PDGF assist bone injury repair with promoting angiogenesis, osteogenesis, and chondrogenesis by attracting progenitor cells \[ 71 , 72 \]. In addition to bone tissue, the osteoconductive BMP subfamily induces bone formation by stimulating pluripotent cells to differentiate into bone-forming cells \[ 73 \]. In cases of critical size defects, osteocunductive factors are particularly important. In the injured bone, GFs have been incorporated using a variety of approaches \[ 74 \]. GF-loaded Ca-P coatings have been widely applied to orthopedic and craniofacial implants made from collagen \[ 75 \]. It has been reported that rhBMP-2 performed very impressively in simulating the differentiation process of stem cells into bone-forming cells \[ 76 \]. Among metal agents used to combat bacteria, zinc is undoubtedly the most widely used \[ 77 \]. Studies have found that zinc ions have a longer-lasting bactericidal effect on viable bacteria populations \[ 78 , 79 \]. Most recently, through a combination of proteins and ions adhering together by mussel adhesion, as well as a molecular click strategy, an immunomodulatory coating containing immobilized metallic ions e. In general, the dual-effect coating can provide a novel concept for metallic implants intended for bone tissue engineering applications with osteoinductivity and immunoactivity properties. In order to facilitate osseointegration and bone healing, macrophages regulate the conversion of macrophage phenotypes and create a microenvironment for immune modulation. Reproduce and adapted from \[ 80 \] under Creative Commons Attribution 4. A dual-layered drug carrier was developed that uses a pore-closed poly lactic-co-glycolic acid microparticle-loaded rhBMP-2 rhBMP-2 filler and a photo-crosslinked CS hydrogel loaded with vancomycin to enhance the antibacterial S. Bone regeneration is stimulated by BMP The outputs of this study revealed that the double-layered drug carrier released vancomycin rapidly for a period of 2 days and rhBMP-2 for approximately 12 days in a sustained manner, thus exhibiting antibacterial and osteogenic effects. Seeing as how this sequential drug release system may improve the osteointegration of dental implants after surgery, this coating agent for dental implants could potentially be considered to be an attractive coating agent \[ 82 \]. Bisphosphonates BPs , usually referred to as antiresorptive drugs, are used in cases of osteoporosis, osteolysis, or hypercalcemia to treat musculoskeletal disorders \[ 81 \]. BPs can inhibit osteoclast activity, reduce osteoporosis risk, and promote osteogenesis by their structural backbone \[ 83 \]. BPs are less bioavailable when administered orally or intravenously, which has led to a focus on local delivery as a solution \[ 83 , 84 \]. An in vivo study using Ti implants coated with plasma-sprayed HaP revealed increased mechanical fixation and higher peri-implant bone density as a result of BPs added to the HaP coating \[ 85 \]. Through various signaling pathways, strontium ranelate and simvastatin inhibit bone resorption and promote bone formation \[ 86 \]. Recently, an inorganic—organic bioactive interface loaded by a newly-developed anti-osteoporosis drug technetium methylenediphosphonate, 99Tc-MDP with an anti-osteoporosis property was constructed \[ 88 \]. The substrate was porous Ti alloy that printed in three dimensions 3D and loaded with organic temperature-sensitive poloxamer hydrogel, as seen in Figure 5 \[ 88 \]. Since 3D printing was introduced in the field of biotechnology, it has shown excellent ability in the biomedical engineering and pharmaceutical field because of its high adaptability in utilizing various materials, its ability to develop intricate engineering parts, as well as its high efficiency in terms of time and cost \[ 89 , 90 \]. In high concentrations or following burst release of BPs, osteoclasts as well as osteoblasts can undergo apoptosis. The pulse electrodeposition technique allows a more controlled and slower release of zoledronate than the soaking method, so it is ideal for coating and incorporating the drug. In one-step electrochemical deposition of drug coated surfaces, osteoblasts have been shown to proliferate and differentiate osteogenically, but osteoclasts are not significantly inhibited. This may improve bone formation and decrease osteoporosis-related bone resorption near magnesium-based implants \[ 91 \]. Reproduce and adapted from \[ 88 \] under Creative Commons Attribution 4. Orthopedic infection prevention is generally achieved through the use of systemic antibiotics which is the most common and local antibiotics \[ 92 \]. There have been recent proposals to coat metallic implant surfaces with controlled antibiotic drug delivery systems \[ 93 , 94 \]. A number of advantages are associated with these systems, including controlled release rates and the possibility of coating surfaces with selective agents \[ 95 \]. It is important to develop antimicrobial surface coatings that maintain or enhance the material biological performance \[ 96 \]. The application of antimicrobial agents to dental implants may act as a monolithic system since the drug release should be homogenous throughout the whole implant \[ 97 , 98 \]. Bathaei group. The drug release of DEX is shown schematically in Figure 6 b. Bathaei research group, and b schematic representation of DEX release in implantation site. It is also necessary for this system to maintain stable and effective concentration of drug on the site of the implant to prevent the development of bacterial resistance \[ 99 , \]. Despite the fact that some drug delivery agents have the advantage of enhancing the release of drugs, such as polylactide acid PDLA , this coating method still suffers from some major disadvantages, including a short-term release and the inability to reload the drug \[ \]. There has been some promise in treating peri-implant infections with a local drug delivery system comprised of minocycline microspheres, a therapy that has been used for more than 20 years for periodontal disease in teeth \[ \]. Recently, however, engineering approaches have been developed for coating surfaces with modified materials that are loaded with antibiotics in order to control the formation of biofilms and, consequently, the development of infection associated with implants \[ \]. It has become increasingly common in recent years to incorporate antibiotics into surface coatings for Ti materials. There have been some difficulties using these coatings because, although they are being evaluated, they are susceptible to short-term release characteristics, resulting in reduced release as well as cytotoxicity because proteins adsorb on top of the coating. A suitable antimicrobial activity must also be determined by taking into account the surface topography properties of these treatments \[ \]. There seems to be no consensus on the optimal antibiotic and coating technique that should be applied to Ti material to minimize implant-related infections, based on antibiotic and coating technology employed on Ti material. It has also been explored if it is possible to release drugs in advanced ways, including triggered, sequential, and delayed releases \[ \]. Antibiotic releasing from metallic implants surface have also been shown to possess osseointegration, immunomodulatory, anticancer, and antibacterial properties in numerous in vivo studies \[ \]. Table 1 summarizes the in vivo studies of various drug coated Ti implants for bone tissue engineering applications. A unique characteristic of biopolymers such as CS that has been used as a drug delivery platform on the implant surface is its ability to inhibit bacterial growth, as well as promote osteoblast activity, thus providing dual synergistic benefits: osteogenic and antibacterial \[ \]. In , Gentamicin GM was introduced into parenteral use after being discovered in \[ \]. The use of GM in medicine has been widespread since then. Gram-negative bacterial infections are treated with aminoglycosides, the oldest antibiotic. In vitro studies showed that GM induces mesangial cell contraction and reduces filtration \[ \]. As well, a number of studies have demonstrated that calcium channel blockers may inhibit mesangial cell proliferation and contraction when used in conjunction with other therapies. A rise in calcium levels stimulates the phospholipases, nucleases, and proteases, which disrupt the function of cell membranes and result in more damage to the kidneys during the creation of GM nephrotoxicity \[ \]. As seen in Table 1 , GM is the most used antibiotics on coated implants described in the literature. Some of the metallic implants containing GM-based drug delivery are summarized in Table 2. In vivo and in vitro studies of GM-eluting metallic implants for reducing the bacterial activities in implantation site. Use of a combination of Ag-GM to kill the bacteria and eradicate the need for mammalian cells coverage. Cell proliferation was observed during the first 7 days but slowed down after that due to coating reaction or growth starting below the coating. The bacterial colonies reduced to 1. In vivo studies of various drug coated metallic implants for bone tissue engineering applications. In recent decades, the development of smart metallic implants has become a popular research frontier in biomedical engineering, capable of responding to stimuli and adapting their responses in response to their surroundings. Through smart surfaces in drug-eluting implants, the frequency of dosing can be reduced, therapeutic concentrations can be maintained during a single dose, and non-target tissues can be protected from drug accumulation \[ \]. As a result, smart surfaces are capable of reacting to external stimuli, such as pH, temperature, electric and magnetic fields, light, as well as the concentration of biomolecules, thereby inducing a controlled release of the drug that has been loaded. The schematic illustration of smart drug delivery systems on metallic implants is shown in Figure 7 \[ \]. The schematic representation of smart bacteria-responsive drug delivery systems. Scaffolds, hydrogels, nanoparticles, nanosphere, micelles, multiple-layer films and TiO 2 NT loaded with drugs are triggered by the changes specific to the infection microenvironment, including the a pH decreasing, b elevated local temperature, c bacteria-specific enzymes and toxins and d products of host immune response, aiming to kill the bacteria. Reproduce and adapted from \[ \] under Creative Commons Attribution 4. A cocktail of enzymes, such as hyaluronidase HAase and chymotrypsin, is secreted by pathogens at various stages of colonization and biofilm formation at implant sites. It has been shown that coating implant surfaces in biopolymers or using linkers that can degrade enzymatically with the aid of enzymes can help to facilitate local therapy as soon as an infection occurs. The incorporation of these polymers onto drug-loaded implant surfaces can also enable triggered release since several natural and synthetic polymers can be degraded by enzymes. HA-gen-grafted hyaluronic acid coatings on deferoxamine DFO -loaded nanotubes on Ti implants have been reported by Yu et al. It was found that this structure is able to function as a triggered drug release system in the absence of HAase, but a burst release of DFO was observed in the presence of HAase. As a result of bacterial infection, the pH of the local environment may change from a normal physiological value of 7. As a result of this shift in pH, local therapy from the implant surfaces has been attempted in several ways. In a recent study by Wang et al. It was used to load antibacterial nanoparticles and vancomycin into NTs, and these nanotubes were then sealed with antibacterial polymers. Since the coordination bonds are extremely stable at a neutral pH, it is unlikely that much drug will be released. Bacterial infections are known to cause an increase in local temperatures, a factor that is also considered to be a trigger for infection. There has been a great deal of interest in smart polymers that undergo phase transitions within a specific range of temperatures when exposed to an abrupt change in temperature. This smart polymer is a good example of such a polymer. The study by Choi et al. Due to the lower critical solution temperature behavior of the brushes, the localized rise in temperature of the infected site triggers the onset of drug release. In vivo tests with rats infected with S. Some limitations of the technologies described herein have already been addressed, but many more must be resolved in order to enhance bench-to-bedside progression. To adapt to varying implant environments, the drug industry is constantly innovating based on advances in pharmacology and pharmacokinetics. As metallic materials science develops, Ti implant processing technology continues to improve, and a variety of devices that conform to human biomechanics and are capable of storing and slowly releasing drugs have been prepared, resulting in a longer acting time, even up to several months for drug delivery systems and greater stability. A great deal of future research should focus on how Ti implants interact with their drug-loading systems in order to achieve a more holistic approach to the synergy. As such, the implants should be developed that will improve their antibacterial properties, their ability to promote osseointegration, their balance of physical properties, and other tailored requirements, thereby providing comprehensive solutions to the numerous implant properties that are required. Another area of study in drug-eluting implants will be on the adhesion mechanisms of drug molecules on the uncoated and coated metallic materials. Moreover, with predictable release kinetics and more particular therapeutic actions, we may be able to attain more specific therapeutic effects. This proof-of-concept, which incorporates sensing systems to indicate regeneration and healing progresses, predicts the development of multifaceted orthopedic implantable devices that will eventually serve as supplementary functions as well as stimuli-responsive drug delivery for a variety of smart applications. As a result of this future trend, resourceful orthopedic therapies will be fabricated, thereby reducing the social and financial burdens associated with current practices by a significant amount. Providing timely, customized, intelligent treatment, reducing hospitalization time, minimizing cytotoxicity, maximizing long-term implant utility, and reducing post-surgical complications and revision surgeries. In conclusion, the latest developments in pharmacology and metal materials science, combined with the perspective of orthopedics thus far, can aid in the solving of more orthopedic problems in a synergistic manner. A synthetic orthopedic and craniofacial implant that will offer impeccable structural support will also be able to assist in the natural healing process by stimulating new bone formation. There are several types of metallic drug-eluting implants that are used in orthopedic applications. Generally, the drugs are incorporated into a coating whether it is either polymeric or ceramic that is applied onto the metal surface in order to deliver the drug. If bacteria are exposed to suboptimal concentrations for an extended period, they may develop resistance to antibacterial drugs. Therefore, it is imperative not to allow the drug concentration to fall below the therapeutic window. Antibacterial drugs are delivered to implants to prevent bacterial growth and infection, but they should be released within a specific range to provide maximum benefit. Stimuli-responsive or smart drug delivery systems can be substantially expanded with further progress in this field. All authors have read and agreed to the published version of the manuscript. This section collects any data citations, data availability statements, or supplementary materials included in this article. As a library, NLM provides access to scientific literature. Find articles by Sadeq Alshimaysawee. Find articles by Rasha Fadhel Obaid. Find articles by Moaed E Al-Gazally. Find articles by Masoud Soroush Bathaei. Dong Keun Han : Academic Editor. Open in a new tab. Titanium GM loaded nanotubes coated over the implant surface In-vivo S. Epidermidis Allowed surface cover with mammalian cells by eradicating bacterial contamination. Epidermidis cell via spread plate method Resistance to bacterial adhesion and biofilm formation Enhanced biocompatibility and mitogenic activity \[ \] TiO 2 Porous walls of scaffold impregnated with GM loaded poly lactide- co -glycolide microparticles In-vitro S. Practical compatibility with osteoblast cells. Aureus via plate counting method The bacterial colonies reduced to 1. Decrease in corrosion rates of the alloy \[ \]. Similar articles. Add to Collections. Create a new collection. Add to an existing collection. Choose a collection Unable to load your collection due to an error Please try again. Add Cancel. GM loaded nanotubes coated over the implant surface. Enhanced Bacterial inhibition. GM loaded on the surface via immersion in GM solution. Allowed surface cover with mammalian cells by eradicating bacterial contamination. Epidermidis cell via spread plate method. Resistance to bacterial adhesion and biofilm formation Enhanced biocompatibility and mitogenic activity. TiO 2. Porous walls of scaffold impregnated with GM loaded poly lactide- co -glycolide microparticles. Epidermidis via Agar diffusion test. Resistance to bacterial activities. Magnesium foam. Porous Mg scaffold immersion in GM solution. Tested under PBS solution. Stainless Steel. The growth of bacteria was inhibited during and after 30 h of immersion. AZ31 Magnesium alloy. Aureus via plate counting method. Decrease in corrosion rates of the alloy. Soaking method. Manual application PH. Beadblasted and etched. Covalent immobilization. Machined and nanotubular anodized surface. PDLLA suspension. Covalently link. TiO 2 nanotubes. Drug adsorption. Clindamycin or Teicoplanin. Layered double hydroxides suspension. Electrophoretic deposition. Plasma chemical oxidation. Covalently bond. Sandblasted and etched. Impregnated on the plasma-sprayed coating. Polyelectrolyte deposition. Coaxial electrospinning. Vancomycin or Tigecycline. Dip coating.

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