plga plga plga, plg, or poly(lactic-co-glycolic acid) is a copolymer which is used in a host of food and drug administration (fda) approved therapeutic devices, owing to its biodegradability and biocompatibility. plga is synthesized by means of ring-opening co-polymerization of two different monomers, the cyclic dimers (1,4-dioxane-2,5-diones) of glycolic acid and lactic acid. polymers can be synthesized as either random or block copolymers thereby imparting additional polymer properties. common catalysts used in the preparation of this polymer include tin(ii) 2-ethylhexanoate, tin(ii) alkoxides, or aluminum isopropoxide. during polymerization, successive monomeric units (of glycolic or lactic acid) are linked together in plga by ester linkages, thus yielding a linear, aliphatic polyester as a product. structure of poly(lactic-co-glycolic acid). x= number of units of lactic acid; y= number of units of glycolic acid. copolymer depending on the ratio of lactide to glycolide used for the polymerization, different forms of plga can be obtained: these are usually identified in regard to the molar ratio of the monomers used (e.g. plga 75:25 identifies a copolymer whose composition is 75% lactic acid and 25% glycolic acid). the crystallinity of plgas will vary from fully amorphous to fully crystalline depending on block structure and molar ratio. plgas typically show a glass transition temperature in the range of 40-60°c. plga can be dissolved by a wide range of solvents, depending on composition. higher lactide polymers can be dissolved using chlorinated solvents whereas higher glycolide materials will require the use of fluorinated solvents such as hfip. plga degrades by hydrolysis of its ester linkages in the presence of water. it has been shown that the time required for degradation of plga is related to the monomers' ratio used in production: the higher the content of glycolide units, the lower the time required for degradation as compared to predominantly lactide materials. an exception to this rule is the copolymer with 50:50 monomers' ratio which exhibits the faster degradation (about two months). in addition, polymers that are end-capped with esters (as opposed to the free carboxylic acid) demonstrate longer degradation half-lives. this flexibility in degradation has made it convenient for fabrication of many medical devices, such as, grafts, sutures, implants, prosthetic devices, surgical sealant films, micro and nanoparticles. plga undergoes hydrolysis in the body to produce the original monomers: lactic acid and glycolic acid. these two monomers under normal physiological conditions, are by-products of various metabolic pathways in the body. lactic acid is metabolized in the tricarboxylic acid cycle and eliminated via carbon dioxide and water. glycolic acid is metabolized in the same way, and also excreted through the kidney. the body also can metabolize the two monomers, which in the case of glycolic acid produces small amounts of the toxic oxalic acid, though the amounts produced from typical applications are minuscule and there is minimal systemic toxicity associated with using plga for biomaterial applications. however, it has been reported that the acidic degradation of plga reduces the local ph low enough to create an autocatalytic environment. it has been shown that the ph inside a microsphere can become as acidic as ph 1.5. biocompatibility generally plga is considered to be quite biocompatible. its high biocompatibility results from its composition due to lactic and glycolic acid fermentation from sugars, making them eco-friendly and less reactive in the body. plga also degrades into non-toxic and non-reactive products that makes them quite useful for various medical and pharmaceutical applications. the biocompatibility of plga has been tested both in vivo and in vitro. the biocompatibility of this polymer is generally determined by the products that it degrades into, as well as the rate of degradation into degradation products. the way that plga degrades is by means of an enzyme known as esterase, which forms lactic acid and glycolic acid. these acids then undergo the krebs cycle to be degraded as carbon dioxide (co2) and water (h2o). these byproducts then get removed from the body through cellular respiration and through the digestive process. while the byproducts usually do not accumulate in the body, there are instances where these byproducts (lactic and glycolic acid) can be dangerous to the body when accumulated in high local concentrations. there can also be small pieces of the polymers as the polymer degrades, causing an immune response by macrophages. these adverse effects can be reduced by using lower concentrations of the polymer, so that it gets naturally released throughout the body. something else to consider regarding plga biocompatibility is the location at which the polymer is implanted or placed in the body. there are different immune responses that the body could have depending on where the polymer is placed. for example, in drug delivery systems (dds), plga and pla implants with high surface area and low volume of injection can increase one’s chance of immune response as the polymers degrade in the body. biodegradability the biodegradation of plga makes it useful for plenty of medical practices. plga undergoes bulk degradation, which is when a catalyst such as water inserts itself throughout the matrix of the polymer. a 75:25 lactide to glycolide plga ratio can be made as microspheres that degrade via bulk erosion. this allows degradation throughout the whole polymer to occur equally. another injectable form of plga was developed to have eroding systems. this form can be used in lupron depot. to achieve this, plga is mixed with an organic water-miscible solvent approved by the food and drug administration (fda). once the plga is mixed into the solvent with the drug of choice to create a homogenous solution or suspension. when this mixture is injected, the plga solidifies due to water insolubility and is replaced by the water. slowly, the drug is delivered from the solution. a problem that may occur is during the initial injection, the drug may be released in a quick burst instead of gradually. examples specific examples of plga's use include: synthetic barrier membrane by powerbone: this device is a resorbable synthetic membrane that acts as an alternative to polytetrafluoroethylene (ptfe), which is a synthetic polymer often used in dental implants and many other applications. the synthetic barrier membrane is used specifically in dental implants and for guided tissue regeneration (gtr) as well as guided bone regeneration (gbe). some are biodegradable membranes, while others are not, and are typically correlated with more surgical complications. in general, these membranes are important to provide biocompatibility, biosafety, barrier function, and mechanical properties to the implant. they are also typically bioactive, promoting the regeneration of tissues around the site of implantation. lupron depot: this is a drug delivery device that helps treat prostate cancer and has been used to treat other types of similar cancers. it is also known as leuprorelin or leuprolide. plga is used as a key component in this drug, in the form of microparticles to deliver the drug into the body over a period of 1 week to 6 months. this drug is typically used as an alternative to radiation therapy, and is considered to be quite effective as it reduces the levels of testosterone in the body, slowing the effects of the cancer. there are many side effects of this drug, including muscle loss, hot flashes, fatigue, osteoporosis, growth of breast tissue, and many others. prophylactic delivery: this refers to preventative healthcare that is meant to prevent infections or other illnesses. one case of prophylactic delivery involving plga is for the antibiotic vancomycin, which is typically injected after brain surgery to prevent infections from bacteria including staphylococcus aureus.