In vitro degradation of a poly(propylene fumarate)-based composite material

Yaszemski, Michael J.; Payne, Richard; Hayes, Wilson C.; Langer, Robert; Mikos, Antonios G.

doi:10.1016/0142-9612(96)00008-7

Cited by 194 publications

(140 citation statements)

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“…Besides, they are faster resorbed in vivo. 5 Therefore, these calcium orthophosphates were used instead of HA to prepare completely biodegradable biocomposites [376][377][378][379][380][381][382][383][384][385][386][387][388][389][390][391][392][393][394]. For example, a biodegradable and osteoconductive biocomposite made of b-TCP particles and gelatin was proposed [385].…”

Section: Tcp-based Biocompositesmentioning

confidence: 99%

Calcium orthophosphate-based biocomposites and hybrid biomaterials

Dorozhkin¹

2009

J Mater Sci

283

146

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Section: Tcp-based Biocompositesmentioning

confidence: 99%

Calcium orthophosphate-based biocomposites and hybrid biomaterials

Dorozhkin¹

2009

J Mater Sci

283

146

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“…5 We described the copolymer synthesis based on that of PPF as described by Peter et al [6][7][8] Poly(ethylene glycol), PEG, has been used for numerous biological applications, in part because low molecular weights (less than 20,000) are passively excreted by the body with no known toxic side effects. 9,10 We believed that a block copolymer consisting of these two homopolymers would be injectable and would degrade into bioresorbable degradation products.…”

Section: Introductionmentioning

confidence: 99%

In vitro andin vivo degradation of poly(propylene fumarate-co-ethylene glycol) hydrogels

Suggs

Krishnan

García

et al. 1998

J. Biomed. Mater. Res.

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The degradation of poly(propylene fumarate-co-ethylene glycol) hydrogels was examined in vitro in phosphate-buffered saline at pH 7.4 and in vivo in a subcutaneous rat model. These hydrogels have potential application as biodegradable, injectable cardiovascular stents, and, as such, their mass loss, dimensional changes, mechanical properties, morphology, and biocompatibility over a 12-week time course were evaluated. Three formulations were fabricated: one base formulation consisting of 25% (w/w) PEG, molecular weight 4,600; one high weight percent PEG formulation with 50% (w/w) PEG; and one high molecular weight PEG formulation, molecular weight 10,500. All three formulations showed significant weight loss (between 40 and 60%) on the first day due to leaching of the uncrosslinked fraction. Further weight loss was observed only for the low weight percent PEG copolymers in the in vivo case, and a slight increase in volume was observed due to degradative swelling. The mechanical properties of the P(PF-co-EG) hydrogels decreased significantly in the first 3 weeks, showing the biphasic pattern typical of bulk degradation. In vitro, the hydrogels showed at least a 20% retention of their initial ultimate tensile stress after 3 weeks. The dynamic mechanical properties showed similar retention, with the in vivo mechanical properties differing from the in vitro properties only after 6 weeks of degradation. Differences in PEG molecular weight appeared to have little effect, but increasing the weight percent PEG decreased the rate of degradation both in vitro and in vivo. The morphology of the copolymer films, based on scanning electron microscopy observation, was not significantly different either among the three formulations or over the time course of the study, suggesting there were no macroscopic structural changes during this time period. The P(PF-co-EG) hydrogels demonstrated good initial biocompatibility, showing responses characteristic of biomaterial implants.

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“…Similar phenomena was observed in poly(propylene fumarate) composites and were initially ascribed to the complexation of the carboxylic groups formed during degradation. 64,65 In our case, it could probably be related to the generation of new crosslinking/interaction points in the network due to the scission of ester linkages that increase free carboxylic acid salts (Fig. 5).…”

Section: 63mentioning

confidence: 99%

Mechanical properties and degradation studies of poly(mannitol sebacate)/cellulose nanocrystals nanocomposites

et al. 2015

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A., 2008, 105, 2307). However, PPS generally display poor mechanical properties, in particular a low modulus, that limit the true potential of these materials in the biomedical field. Here, we introduce an approach to obtain nanocomposites based on poly(mannitol sebacate) (PMS) matrices reinforced with cellulose nanocrystals (CNCs) in order to improve the application range of these materials. Different strategies were used based on varying the feed ratios between mannitol : sebacic acid (1 : 1 and 1 : 2), crosslinking conditions and CNCs content, resulting in different degrees of crosslinking and, therefore, mechanical and degradation behavior. All of the developed nanocomposites displayed the expected mass loss during the degradation studies in simulated body fluid (SBF) similar to the neat matrix, however, doubling the sebacic acid feed ratio or extending the curing temperature and time, resulted in higher mechanical properties, structural integrity, and shape stability during a degradation time lessening mass loss rate. Changing mannitol : sebacic acid reaction ratios from 1 : 1 to 1 : 2 and for low crosslinking degree neat samples, the Young's modulus increases four-fold, while mass loss after 150 days of incubation is reduced by half. The Young's modulus range obtained with this process covers the range of human elastic soft tissues to tough tissues (0.7-200 MPa). IntroductionIn the past few years, there has been steady progress in the development of biodegradable polymers for application in the medical eld because these materials provide new opportunities to design less invasive and resorbable implants, tissue scaffolds, and medical devices that are able to avoid second revision surgeries, that limit the risk of infection and results in less trauma for the patient.5-8 Moreover, biodegradable polymeric systems which offer the possibility to tailor their mechanical properties from so to stiffer as well as the biodegradability ratio by varying the processing conditions also have additional advantages. Medical devices based on different classes of biodegradable polymers such as polyesters, polyanhydrides and polyurethanes have been widely investigated and some of them are commercially available as resorbable sutures, drug delivery systems, vascular gras, wafers and orthopaedic xation devices based, among others, on polylactic acid (PLA), polyglycolic acid (PGA), poly(lactic-co-glycolic acid) (PLGA), poly(3-caprolactone) (PCL), poly(p-dioxanone) (PDO), or poly(trimethylene carbonate) (PTMC).9,10 However, most of these polymeric systems have degradation rates that are not optimal for short-medium term applications. For example, it takes more than 24 months for poly(caprolactones) and poly(Llactic acid) to degrade in a biological environment, and from 2 to 24 months, depending on the ratio, for copolymers of polylactic acid (PLA) and polyglycolic acid (PGA). Also, the degradation rate for polyanhydrides is slow, around 12 months. 6,9,11 Moreover, these polymers have a lack of exibility and elasticity at bod...

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In vitro degradation of a poly(propylene fumarate)-based composite material

Cited by 194 publications

References 4 publications

Calcium orthophosphate-based biocomposites and hybrid biomaterials

Calcium orthophosphate-based biocomposites and hybrid biomaterials

In vitro andin vivo degradation of poly(propylene fumarate-co-ethylene glycol) hydrogels

Mechanical properties and degradation studies of poly(mannitol sebacate)/cellulose nanocrystals nanocomposites

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