This paper reports the obtaining of poly (vinyl alcohol) and ι-carrageenan blend hydrogels by physical crosslinking (consecutive freeze–thaw cycles). The two polymers were completely miscible in the weight ratio interval used in this study, as determined by solution viscometry data. Strong interactions through hydrogen bonding and forming of mixed interpolymer crystalline domains were observed, which are responsible for the formation of stable drug release-tunable matrices. The release profiles of three model antibiotic drugs (amoxicillin, tetracycline hydrochloride, and gentamicin sulfate) were assessed in a pH interval between 3 and 7.3. They were found to be strongly dependent on the drug chemistry, mesh size of the hydrogels, swelling mechanism, and pH of the release medium. A decrease of up to 40% in the release rates and up to 10% in the diffusion coefficients of the model drugs was registered with the increase in ι-carrageenan content.
This paper reports the obtaining of poly (vinyl alcohol) and ι-carrageenan blend hydrogels by physical crosslinking (consecutive freeze–thaw cycles). The two polymers were completely miscible in the weight ratio interval used in this study, as determined by solution viscometry data. Strong interactions through hydrogen bonding and forming of mixed interpolymer crystalline domains were observed, which are responsible for the formation of stable drug release-tunable matrices. The release profiles of three model antibiotic drugs (amoxicillin, tetracycline hydrochloride, and gentamicin sulfate) were assessed in a pH interval between 3 and 7.3. They were found to be strongly dependent on the drug chemistry, mesh size of the hydrogels, swelling mechanism, and pH of the release medium. A decrease of up to 40% in the release rates and up to 10% in the diffusion coefficients of the model drugs was registered with the increase in ι-carrageenan content.
“…log q eq = log K f + 1 n log C eq (12) where K f and n represent the Freundlich constants; C eq (mg L −1 ) is the equilibrium concentration of 5-FU; and q eq (mg g −1 ) is the amount of 5-FU adsorbed at equilibrium concentration. The calculated K f , 1/n, and R 2 (correlation coefficients) values are summarized in Table 2.…”
Section: In Vitro Release Studiesmentioning
confidence: 99%
“…This allows for systemic toxicity to be reduced toward healthy cells and to localize 5-FU delivery only to selected tissue. Up to now, many 5-FU DDS have already been developed based on polymeric particles [ 6 , 7 , 8 , 9 ], hydrogels [ 10 , 11 , 12 ], magnetic nanoparticles [ 13 , 14 , 15 ], and clay minerals [ 16 , 17 , 18 ].…”
Trigger-responsive materials are capable of controlled drug release in the presence of a specific trigger. Reduction induced drug release is especially interesting as the reductive stress is higher inside cells than in the bloodstream, providing a conceptual controlled release mechanism after cellular uptake. In this work, we report the synthesis of 5-fluorouracil (5-FU) molecularly imprinted polymers (MIPs) based on poly(2-isopropenyl-2-oxazoline) (PiPOx) using 3,3′-dithiodipropionic acid (DTDPA) as a reduction-responsive functional cross-linker. The disulfide bond of DTDPA can be cleaved by the addition of tris(2-carboxyethyl)phosphine (TCEP), leading to a reduction-induced 5-FU release. Adsorption isotherms and kinetics for 5-FU indicate that the adsorption kinetics process for imprinted and non-imprinted adsorbents follows two different kinetic models, thus suggesting that different mechanisms are responsible for adsorption. The release kinetics revealed that the addition of TCEP significantly influenced the release of 5-FU from PiPOx-MIP, whereas for non-imprinted PiPOx, no statistically relevant differences were observed. This work provides a conceptual basis for reduction-induced 5-FU release from molecularly imprinted PiPOx, which in future work may be further developed into MIP nanoparticles for the controlled release of therapeutic agents.
“…[17] various strategies have been tested to overcome this limitation and develop a sustained release drug delivery system based on PNIPAAm hydrogel, including the production of composite hydrogels, [18,19] the preparation of Interpenetrating polymer network (IPN) hydrogels, [20,21] and the copolymerization of NIPAAm with other monomers. [22,23] In addition to these strategies, the formation of a chemical bond between the hydrogel matrix and drug is…”
Section: Introductionmentioning
confidence: 99%
“…But despite all these advantages, burst release of drug molecules from the PNIPAAm hydrogel matrix is an obstacle to utilizing it as an efficient drug carrier [17] . various strategies have been tested to overcome this limitation and develop a sustained release drug delivery system based on PNIPAAm hydrogel, including the production of composite hydrogels, [18,19] the preparation of Interpenetrating polymer network (IPN) hydrogels, [20,21] and the copolymerization of NIPAAm with other monomers [22,23] . In addition to these strategies, the formation of a chemical bond between the hydrogel matrix and drug is another way to prolong the duration of drug release from the hydrogel drug carrier [24] …”
The burst release of drugs limited the development of the thermo-responsive hydrogels based on poly N-isopropylacrylamide (NIPAAm) for application in drug delivery systems. To overcome this problem, the drug sulfadimethoxine (SDMO) was conjugated via amide bond to the PNIPAAm hydrogel instead of loaded into the system. Therefore, SDMO was modified using maleic anhydride to get N-maleyl sulfadimethoxine (NMSDMO) and then utilized that to synthesize the sulfadimethoxineconjugated PNIPAAm hydrogel (P[NIPAAm-co-NMSDMO]). The resultant monomer was then grafted into the hydrogel network at different weight percentage through radical polymerization. The NMSDMO monomer and the P[NIPAAm-co-NMSDMO] hydrogels were fully investigated. The in vitro drug released displayed sustained release in pH 5 and 7.4 for 24 h. Hydrolysis of the amide bond causes the release rate and total amount of drug to be greatest at pH 5, as compared to pH 7.4. As a result, the P[NIPAAm-co-NMSDMO] hydrogel was an effective sustained drug delivery system.
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