ライフサイエンスコーパス: PLGA

1 PLGA 50/50 microspheres encapsulating ~5% w/w leuprolide

2 PLGA microspheres are widely studied for controlled rele

3 PLGA NPs were found non-uniformly distributed on the epi

4 PLGA with different lactide to glycolide (50:50 and 65:3

5 PLGA-b-PEG copolymer was synthesized and characterized b

6 PLGA-b-PEG NPs with desirable size, polydispersity, and

7 PLGA-b-PEG-b-PLGA sol-gels are a first-generation platfo

8 PLGA-b-PEG-NH2 and PLGA-b-mPEG NPs were prepared by nano

9 PLGA-LL37 NP improved angiogenesis, significantly up-reg

10 PLGA-LL37 NP-treated wounds displayed advanced granulati

11 PLGA-PEG nanoparticles with a wide range of PEG MW (1, 2

12 PLGAs remain today as one of the few "real world" biodeg

13 Here, 200nm PLGA/PVA nanospheres were formulated for the systemic de

14 tive loading of vaccine antigen in Al(OH)(3)-PLGA microspheres was found to: a) increase with an incr

15 within poly(lactic-co-glycolic acid) 50:50 (PLGA) microspheres by using a solid-in-oil-in-water emul

16 was concluded that the addition of PVP in a PLGA matrix resulted in vivo in a more sustained release

17 ed by a core-shell structure consisting of a PLGA matrix core coated with lamellar DOTAP structures w

18 Solid dispersions, based on a PLGA/PVP matrix, were compared to solid dispersions in a

19 -transmission electron microscopy revealed a PLGA core coated with one or several concentric lipid bi

20 In summary, a PLGA-b-PEG-b-PLGA sol-gel has loading and release capaci

21 used for the conjugation with ascorbic acid (PLGA-b-PEG-Asc) to facilitate SVCT2 mediated transportat

22 osan shell and poly lactic-co-glycolic acid (PLGA) core for enhancing localized chemo-radiotherapy to

23 pacity of poly (DL)-lactic-co-glycolic acid (PLGA) microspheres containing glycosaminoglycan-like bio

24 Lycopene-loaded polylactic-co-glycolic acid (PLGA) NPs were prepared by the same method.

25 e-modified polylactic acid-co-glycolic acid (PLGA)-Chitosan nanoparticle (CSNP) for integrin alphavbe

26 consisting of poly(lactic-co-glycolic) acid (PLGA) microsphere dispersed in poly(vinyl alcohol) (PVA)

27 Poly(d,l-lactic-co-glycolic) acid (PLGA) nanoparticles containing phenolic extract of guabi

28 d agent-doped poly(lactic-co-glycolic) acid (PLGA) particles by using a single-emulsion evaporation t

29 dable polymer poly(lactic-co-glycolic) acid (PLGA) using an electrojetting technique.

30 capsulated in poly(lactic-co-glycolic) acid (PLGA)-based nanoparticles (NPs) induce robust and durabl

31 ionic lipid-poly(lactide-co-glycolide) acid (PLGA) hybrid nanoparticles as antigen delivery carriers

32 g comprised of poly(lactic-coglycolic acid) (PLGA) nanofibers embedded in a poly(epsilon-caprolactone

33 arriers using poly(lactic-co-glycolic acid) (PLGA) and PLGA-polyethylene glycol (PLGA-PEG) polymers t

34 ter-insoluble poly(lactic-co-glycolic acid) (PLGA) and water-soluble polyvinylpyrrolidone (PVP) was e

35 e antigens in poly(lactic-co-glycolic acid) (PLGA) by simple mixing of preformed active self-microenc

36 LPHNPs) with poly (lactic-co-glycolic acid) (PLGA) core and lipid layer containing docetaxel and clin

37 pores in poly(D,L-lactic-co-glycolic acid) (PLGA) drug delivery systems has been identified to play

38 Poly(lactic-co-glycolic acid) (PLGA) is a biodegradable FDA approved polymer and widely

39 psulated with poly(lactic-co-glycolic acid) (PLGA) microparticles loaded with vascular endothelial gr

40 accommodated poly(lactic-co-glycolic acid) (PLGA) microparticulate systems that controlled the relea

41 Here, two poly(lactic-co-glycolic acid) (PLGA) microsphere formulations encapsulating the model s

42 NEP1-40 into poly (lactic-co-glycolic acid) (PLGA) microspheres, obviating the need for invasive intr

43 sisting of poly(DL-lactic-co-glycolic acid) (PLGA) nanocarriers modified with the cationic lipid diol

44 he ability of poly(lactic-co-glycolic acid) (PLGA) nanoparticles (NP) to enhance lutein bioavailabili

45 mpound within poly(lactic-co-glycolic acid) (PLGA) nanoparticles (PLGA-EtNBS) was found to significan

46 ated in poly-(D, L-lactic-co-glycolic acid) (PLGA) nanoparticles adjuvanted with polyinosinic:polycyt

47 onstrate that poly(lactic-co-glycolic acid) (PLGA) nanoparticles carrying rapamycin, but not free rap

48 Poly(lactic-co-glycolic acid) (PLGA) nanoparticles containing dexamethasone sodium phos

49 Copolymer poly(lactic-co-glycolic acid) (PLGA) nanoparticles loaded with SA-2 provided a sustaine

50 t based on poly(dl-lactic-co-glycolic acid) (PLGA) nanoparticles modified with the cationic surfactan

51 dification of poly(lactic-co-glycolic acid) (PLGA) nanoparticles with peptide ligand alters the brain

52 h drug-loaded poly(lactic-co-glycolic acid) (PLGA) nanoparticles.

53 cently-tagged poly(lactic-co-glycolic acid) (PLGA) NPs were loaded with BODIPY, a fluorophore, and pe

54 e coating for poly(lactic-co-glycolic acid) (PLGA) NPs.

55 dable polymer poly(lactic-co-glycolic acid) (PLGA) or the biocompatible polymer polyethylene glycol (

56 hat inhalable poly(lactic-co-glycolic acid) (PLGA) particles of sildenafil prolong the release of the

57 Poly (lactic-co-glycolic acid) (PLGA) supplies lactate that accelerates neovascularizati

58 s composed of poly(lactic-co-glycolic acid) (PLGA) that can encapsulate IPV along with stabilizing ex

59 blended with poly(lactic-co-glycolic acid) (PLGA) to enhance electrostatic cellular attachment to th

60 s composed of poly(lactic-co-glycolic acid) (PLGA) with bright, spectrally defined quantum dots (QDs)

61 erapeutic and poly(lactic-co-glycolic acid) (PLGA) with similar molecular weight as that used in the

62 f the drug in poly(lactic-co-glycolic acid) (PLGA), a polymer that is used in children every day as a

63 onsist of poly(D,L-lactic-co-glycolic acid) (PLGA), polyethylene glycol (PEG), and bisphosphonate (or

64 composed of a poly(lactic-co-glycolic acid) (PLGA)-based core coated with poly(vinyl alcohol) rapidly

65 unctions: (i) poly(lactic-co-glycolic acid) (PLGA, P) serving as the main delivery platform, (ii) pol

66 ol)-block-poly(D,L-lactic-co-glycolic acid) (PLGA-b-PEG-b-PLGA) sol-gels have been extensively resear

67 ol)-block-poly(d,l-lactic-co-glycolic acid) (PLGA-b-PEG-b-PLGA) thermosensitive gel (g-E).

68 ed into poly(d,l-lactide-co-glycolide acid) (PLGA), and coated with a final outer layer of polyethyle

69 s well as with poly(lactic-co-glycolic acid)(PLGA)-based microparticles, co-loaded with OVA and CpG (

70 ene glycol)-b-poly(lactic-co-glycolic acid); PLGA-PEG-PLGA) for increasing the retention of RNA nanop

71 hane solution of polylatic-co-glyclic acids (PLGA) and emulsified in a polyvinyl alcohol (PVA) and Na

72 id end-group poly(lactic-co-glycolic acids) (PLGAs) used to achieve continuous peptide release kineti

73 Additionally, PLGA-b-PEG-Asc NPs resulted in significantly higher biod

74 Polymorphous low-grade adenocarcinoma (PLGA) is the second most frequent type of malignant tumo

75 mice, were similar when PNSN(OVA + CpG) and PLGA(OVA + CpG) were compared and the presence of CpG 18

76 onsive polymer, acetal-modified dextran, and PLGA (polylactide-co-glycolide), and ii) one compartment

77 Free extract and PLGA nanoparticles were effective inhibitors of Listeria

78 The bioavailability of free lutein and PLGA-NP lutein in rats was assessed by determining plasm

79 In summary, PEG-b-PLA micelles and PLGA-b-PEG-b-PLGA sol-gels may safely enable pre-clinica

80 clinical research on PEG-b-PLA micelles and PLGA-b-PEG-b-PLGA sol-gels that has focused on paclitaxe

81 PLGA-b-PEG-NH2 and PLGA-b-mPEG NPs were prepared by nanoprecipitation metho

82 NIH/3T3 cells as compared to plain PLGA and PLGA-b-mPEG NPs.

83 ing poly(lactic-co-glycolic acid) (PLGA) and PLGA-polyethylene glycol (PLGA-PEG) polymers to generate

84 argeting is achieved by coating FDA-approved PLGA-PEG NP with the peptide sequence RGD, which binds w

85 drugs and drug loaded plain PLGA as well as PLGA-b-mPEG NPs.

86 g polymer model drug nanoparticle as well as PLGA-PEG-NP into human colon cancer xenografts in mice.

87 In summary, a PLGA-b-PEG-b-PLGA sol-gel has loading and release capacities for EpoB

88 PLGA-b-PEG-b-PLGA sol-gels are a first-generation platform for the lo

89 summary, PEG-b-PLA micelles and PLGA-b-PEG-b-PLGA sol-gels may safely enable pre-clinical evaluation

90 earch on PEG-b-PLA micelles and PLGA-b-PEG-b-PLGA sol-gels that has focused on paclitaxel will be upd

91 y(D,L-lactic-co-glycolic acid) (PLGA-b-PEG-b-PLGA) sol-gels have been extensively researched for syst

92 y(d,l-lactic-co-glycolic acid) (PLGA-b-PEG-b-PLGA) thermosensitive gel (g-E).

93 a new, multispectral approach for barcoding PLGA, which enables simultaneous, quantitative analysis

94 ained based on the structure of these binary PLGA/PVP matrices where the pore network originating fro

95 We synthesized biodegradable PLGA polymer nanoparticles (NPs) that were loaded with m

96 Both PLGA and PLLA sheaths produced minimal (<30%) rapamycin

97 Both PLGA types improved fruit by-products delivery to pathog

98 20)] was accomplished by incubating blank BP-PLGA microspheres in low concentration protein solutions

99 ed <5 ml release volume for ~18 mg loaded BP-PLGA microspheres), ionic strength of release media and

100 Formulation parameters of BP-PLGA microspheres and loading conditions were studied to

101 Sulfated BP-PLGA microspheres were capable of loading LYZ (~2-7% w/w

102 The BP-PLGA microspheres (20-63 mum) were prepared by a double

103 2 mL and 63 mum, and c) change negligibly by PLGA concentration and initial incubation (loading) temp

104 dulation of the inflammatory response by CaP/PLGA nanoparticle-mediated siRNA delivery could be a pro

105 In cell culture, siRNA-loaded CaP/PLGA nanoparticles exhibited a rapid cellular uptake, al

106 wed similar trends as found with acid capped PLGA but with a longer lag time before release.

107 ease, release of leuprolide from acid-capped PLGA microspheres appeared to be controlled initially by

108 a higher molecular weight, ester end-capped PLGA displayed an osmotically induced/pore diffusion mec

109 Release of leuprolide from the end-capped PLGA showed similar trends as found with acid capped PLG

110 er 10days, whereas by using the ester capped PLGA (Mw=38,000-54,000) the release lasted for over 4wee

111 Thus, large porous celecoxib-PLGA microparticles prepared using supercritical fluid t

112 hip between nanosphere size, surface charge, PLGA-polycation composition, and protein loading is also

113 First, triblock copolymers of PEG-CNA-PLGA are synthesized and then formulated into polymer na

114 s do not get encapsulated within the PEG-CNA-PLGA nanoparticles.

115 dhesive N-trimethyl chitosan chloride-coated PLGA nanoparticles (MNPs) that were loaded with conjugat

116 netration potential of eucalyptus oil coated PLGA-chitosan double walled nanogels.

117 The ZWC-coated PLGA NPs showed pH-dependent surface charge profiles and

118 ompound I-NP)] in poly(lactide-coglycolide) (PLGA) was developed that shows sustained maintenance of

119 ale were relevant to surface pores of common PLGA microspheres and could be easily monitored by light

120 In contrast, PLGA-NP lutein had a lower uptake and secretion of lutei

121 The P2Ns outclass conventional PLGA-GA nanosystems in cellular uptake using caco-2 inte

122 We use poly(lactide-co-glycolide) copolymer (PLGA) fiber microfilaments as a floating scaffold to gen

123 microparticles, co-loaded with OVA and CpG (PLGA(OVA + CpG)), an adenovirus encoding OVA (Ad5-OVA),

124 d many models have been proposed to describe PLGA degradation and erosion and drug release from the b

125 ratus 4 method was capable of discriminating PLGA microspheres that are equivalent in formulation com

126 olymer containing a fluorescent quantum dot, PLGA-b-PEG-QD.

127 gostin, we formulated mangostin-encapsulated PLGA nanoparticles (Mang-NPs) and examined the molecular

128 The fluorescent PLGA-GA NS exhibited significant intestinal transport an

129 n this study, serves as a novel platform for PLGA/polymer based tunable micro/nano particle and polym

130 e observed that small molecule delivery from PLGA nanoparticles varied by as much as 150% for differe

131 ulation and controlled release of drugs from PLGA microparticles.

132 degradation and drug release mechanism from PLGA microspheres embedded in a PVA hydrogel.

133 The drug release profile from PLGA NMP was tri-phasic, being sustained over 5days.

134 c, mathematical models for drug release from PLGA microspheres that specifically address interactions

135 -glycolic acid) pellet containing glutamine (PLGA-GLN) were also placed within the PCL chamber.

136 c acid) (PLGA) and PLGA-polyethylene glycol (PLGA-PEG) polymers to generate sub-100nm nanoparticles w

137 c-co-glycolic acid) and polyethylene glycol (PLGA-PEG) using low molecular weight (MW) emulsifiers fo

138 ic-coglycolic acid)-b-poly(ethylene glycol) (PLGA-b-PEG) and an endothelial-targeted peptide.

139 = gold nanorod; PEG = poly(ethylene glycol); PLGA = poly(lactic-co-glycolic acid)) assembled from sma

140 delivery platform, (ii) polyethylene glycol-PLGA conjugate (PEG-PLGA, p) to help maintain an appropr

141 or its copolymer, polylactide-co-glycolide (PLGA), do not allow such optimization due to their termi

142 Here, we produce poly(lactide-co-glycolide) (PLGA) based microparticles with varying morphologies, an

143 ng GA conjugated poly(lactide-co-glycolide) (PLGA) have shown non-competitive affinity to TfR evaluat

144 ion, electrospun poly (lactic-co-glycolide) (PLGA) mats, which have excellent biocompatibility and me

145 red large porous poly(lactide-co-glycolide) (PLGA) microparticles of celecoxib using supercritical fl

146 Poly (dl-lactide-co-glycolide) (PLGA) nanoparticles of acerola, guava, and passion fruit

147 cles composed of poly(lactide-co-glycolide) (PLGA) or diblock copolymers of PEG-PLGA were similarly i

148 polymers, i.e., poly(lactide-co-glycolide) (PLGA), poly(lactic acid) (PLLA), PCL, and their blends,

149 ase biomaterials, poly(lactide-co-glycolide; PLGA) microparticles (MPs) encapsulating denatured insul

150 amine to the brain via ascorbic acid grafted PLGA-b-PEG nanoparticles (NPs) using SVCT2 transporters

151 ctives to the brain by ascorbic acid grafted PLGA-b-PEG NPs is a promising approach.

152 HA-PLGA microspheres were found to be not ideal for obtaini

153 ic-co-glycolic acid)/poly(L-lactic acid) (HA-PLGA/PLLA) scaffolds.

154 HDS-PLGA formulations were identified as having ideal loadin

155 Films of a less hydrophobic PLGA showed slower healing kinetics, attributed to a wea

156 with over 50% efficiency in the hydrophobic PLGA core and released specifically within the acidifyin

157 Immunologically, PLGA-KAg vaccine irrespective of not significantly boost

158 In PLGA-KAg vaccinated and heterologous SwIV H1N1 challenge

159 Encapsulation of compound 2 in PLGA nanoparticles or cyclodextrins resulted in lower in

160 ncapsulation of protein sorbing Al(OH)(3) in PLGA microspheres resulted in suppression of self-healin

161 ng microencapsulation of vaccine antigens in PLGA was investigated.

162 en-fluorescent dye) diffusion coefficient in PLGA.

163 All fruit by-products encapsulated in PLGA inhibited both bacteria at lower (P<0.05) concentra

164 ted SwIV H1N2 antigens (KAg) encapsulated in PLGA nanoparticles (PLGA-KAg) were prepared, which were

165 t the administration of LL37 encapsulated in PLGA nanoparticles (PLGA-LL37 NP) promotes wound closure

166 5-FU was first entrapped in PLGA core by solvent evaporation technique followed by c

167 extent of absorption/loading of peptides in PLGA particles/films was assayed by two-phase extraction

168 coincorporating hydrophobic plasticizers in PLGA.

169 wards the prediction of healing processes in PLGA and in related biomaterials for important biomedica

170 ven process for encapsulation of proteins in PLGA microspheres that showed low burst release was deve

171 lation of manufacturing process-labile TT in PLGA was found to: a) obviate micronization- and organic

172 igens, ovalbumin and tetanus toxoid (TT), in PLGA microspheres was adjusted by preparing blank micros

173 he hypothesis, this study shows that inhaled PLGA particles of sildenafil can be administered, as a s

174 ey concepts in the development of injectable PLGA controlled-release depots for peptides and proteins

175 or all encapsulated fruit by-products inside PLGA matrix.

176 erapeutic microRNA, miR-122, was loaded into PLGA-PEG-NP and the amount of delivered miR-122 was asse

177 Mtb), were exposed to encapsulated isoniazid-PLGA nanoparticles (NPs) using MA as a targeting ligand.

178 he release of sorbed peptide from leuprolide-PLGA particles was evaluated both in vitro (PBST+0.02% s

179 adsorbed and/or encapsulated cationic lipid-PLGA hybrid nanoparticles; we designated antigen-adsorbe

180 ture design of vaccines using cationic lipid-PLGA nanoparticles.

181 LMWP/PLGA NP effectively arrested tumor growth in mice harbor

182 responsible for the anti-MDR effects of LMWP/PLGA NP.

183 efficiency of intracellular delivery of LMWP/PLGA/DOX NP, suggesting that delivery of LMWP-based NP w

184 When delivering miR-122 loaded PLGA-PEG-NP using optimal acoustic settings with minimum

185 The resulting BCNU-loaded PLGA microcapsules have significantly higher drug encaps

186 de, we engineered MSC with budesonide loaded PLGA microparticles.

187 rapeutic and sustained action by drug loaded PLGA-b-PEG-Asc NPs than free drugs and drug loaded plain

188 tion media on release from leuprolide-loaded PLGA microspheres to understand the influence of externa

189 significantly increased in vivo miRNA-loaded PLGA-NP delivery in human HCC xenografts compared to con

190 titate successful intracellular miRNA-loaded PLGA-NP delivery.

191 miRNA-loaded PLGA-NP were internalized in HCC cells and anti-apoptoti

192 s study, model drug (vitamin D3, VD3)-loaded PLGA nano- and microparticles (NMP) were prepared by a s

193 Compared to free lutein, PLGA-NP increased the maximal plasma concentration (Cmax

194 In comparison with micellized lutein, PLGA-NP lutein improved the Cmax in rat plasma by 15.6-f

195 G/chitosan NPs, but not improved by lycopene/PLGA/chitosan NPs.

196 -molecular-weight protamine (LMWP) to modify PLGA NP for enhanced drug delivery.

197 stable nanosphere complexes contain multiple PLGA-polycation nanoparticles, surrounded by large amoun

198 tantly, absorption of leuprolide into low MW PLGA-COOH particles yielded ~17 wt.% leuprolide loading

199 poly(lactic-co-glycolic acid nanoparticles (PLGA NPs), for improving doxorubicin (DOX) delivery and

200 oly (lactic-co-glycolic acid) nanoparticles (PLGA-NP), administered by an ultrasound-guided and micro

201 poly(lactic-co-glycolic acid) nanoparticles (PLGA-PEG-NP) has significant clinical value because thes

202 ns (KAg) encapsulated in PLGA nanoparticles (PLGA-KAg) were prepared, which were spherical in shape w

203 of LL37 encapsulated in PLGA nanoparticles (PLGA-LL37 NP) promotes wound closure due to the sustaine

204 ctic-co-glycolic acid) (PLGA) nanoparticles (PLGA-EtNBS) was found to significantly reduce EtNBS dark

205 rolide loading in the polymer (i.e., ~70% of PLGA-COOH acids occupied), and the absorbed peptide was

206 could be delayed by increasing the amount of PLGA in the formulation.

207 f cells treated with blended NPs composed of PLGA-b-PEG-TPP and a triblock copolymer containing a flu

208 a commercially available suture composed of PLGA.

209 nd acidic buffers accelerated degradation of PLGA and pore-network development and increased BODIPY d

210 ans-/intramucosal and lymph-node delivery of PLGA-PEG nanoparticles was demonstrated in a porcine mod

211 elatively wide particle size distribution of PLGA NMP was shown to be important in producing a compac

212 ng alteration likely constitutes a driver of PLGA.

213 wn to have a complex role in the dynamics of PLGA erosion and drug transport and can lead to size-dep

214 Here we report the engineering of PLGA-polycation nanoparticles with a core-shell structur

215 and ii) one compartment composed entirely of PLGA.

216 s resulted in suppression of self-healing of PLGA pores, which was then overcome by improving polymer

217 To examine healing of PLGA, pores were created of defined size and depth on th

218 lease at low pH and with co-incorporation of PLGA.

219 vestigated the intratumoral CED infusions of PLGA BPNPs in animals bearing either U87 or RG2 intracra

220 In this study, the material properties of PLGA have been characterized using mechanical tests, and

221 ine +0.02% Tween 80 pH7.4, including rate of PLGA hydrolysis, mass loss and water uptake.

222 The particle size of PLGA NMP ranged from 300nm to 3.5mum and they retained t

223 the viscosity and slow the healing times of PLGA films at intermediate temperatures above the glass-

224 ey issues impeding greater widespread use of PLGA depots for this class of drugs.

225 tical barriers to the more widespread use of PLGA LARproducts, particularly for delivery of more pept

226 t mutations encoding p.Glu710Asp in 72.9% of PLGAs but not in other salivary gland tumors.

227 the method's applicability was evaluated on PLGA nanoparticles and human plasma.

228 more dependent on by-product extract than on PLGA type.

229 ol)-block-poly(lactic-co-glycolic acid) (PEG-PLGA) copolymers have been used successfully for targete

230 e glycol)-poly(lactic-co-glycolic acid) (PEG-PLGA) microparticles were engineered to release TGF-beta

231 The bone-binding ability of Ald-PEG-PLGA NPs was investigated by hydroxyapatite binding assa

232 ulation, and bone homing of targeted Ald-PEG-PLGA NPs, compared with nontargeted PEG-PLGA NPs.

233 (ii) polyethylene glycol-PLGA conjugate (PEG-PLGA, p) to help maintain an appropriate level of polari

234 acid (FTA) loaded (lipid-cationic) lipid-PEG-PLGA hybrid nanoparticles (HNPs) after IN application in

235 -PEG-PLGA NPs, compared with nontargeted PEG-PLGA NPs.

236 ycolide) (PLGA) or diblock copolymers of PEG-PLGA were similarly immobilized when coated with PVA (sl

237 l)-b-poly(lactic-co-glycolic acid); PLGA-PEG-PLGA) for increasing the retention of RNA nanoparticles

238 mplementary to the CNA sequence, whereas PEG-PLGA alone shows minimal DNA loading, and non-complement

239 ial epithelial cells were incubated with PEG-PLGA based formulations.

240 new kind of ultrasmall dissociable AuNR@PEG/PLGA vesicles ( approximately 60 nm) (AuNR = gold nanoro

241 sc NPs than free drugs and drug loaded plain PLGA as well as PLGA-b-mPEG NPs.

242 xpressing NIH/3T3 cells as compared to plain PLGA and PLGA-b-mPEG NPs.

243 ug and a clinically tested polymer platform (PLGA-b-PEG) promote long drug circulation and alter accu

244 LGA-b-PEG and alendronate-conjugated polymer PLGA-b-PEG-Ald, which ensured long circulation and targe

245 ing Poly dl-lactic-co-glycolic acid polymer (PLGA), via a double emulsion solvent evaporation techniq

246 Next, the biocompatible polymers PLGA-PEG-A were synthesized and used as base to conjugat

247 varying ratios of the synthesized polymers: PLGA-b-PEG and alendronate-conjugated polymer PLGA-b-PEG

248 PP) particles and non-porous (NP) and porous PLGA (PP) microspheres.

249 r better attachment of rMSCs than non-porous PLGA/PEI1.8k (NPP) particles and non-porous (NP) and por

250 Thus, we prepared porous PLGA particles of sildenafil using a water-in-oil-in-wat

251 The porous PLGA/PEI1.8k (PPP) particles demonstrated an average par

252 PTX-PLGA-CSNP-RGD displayed favorable physicochemical proper

253 PTX-PLGA-CSNP-RGD showed less toxicity in lung fibroblasts t

254 san was synthesized and then coated onto PTX-PLGA nanoparticles prepared by emulsion-solvent evaporat

255 The PTX-PLGA-CSNP-RGD system showed increased uptake via integri

256 expression showed negligible toxicity to PTX-PLGA-CSNP-RGD, at equivalent drug concentrations used in

257 were compared to solid dispersions in a pure PLGA matrix.

258 tion of FGF2 levels using controlled release PLGA microspheres improves expression of stem cell marke

259 Dexamethasone-releasing PLGA poly(lactic-co-glycolic acid) microsphere/PVA (poly

260 of pores in Poly(lactic-co-glycolic acid)s (PLGA) plays an important role in the encapsulation and c

261 ble poly(lactic-co-glycolic acid) scaffolds (PLGA), and hydroxyapatite powder (HA) were used to mimic

262 reformed active self-microencapsulating (SM) PLGA microspheres in a low concentration aqueous antigen

263 lds embedded with the drug delivery systems (PLGA microspheres and lipid microtubes) were capable of

264 Considering efficacy, the targeted PLGA-b-PEG-TPP NP provides a remarkable improvement in t

265 Taken together, our study demonstrates that PLGA-CSNP-RGD is a promising nanoplatform for integrin t

266 These results suggest that PLGA nanoparticles can be used as a delivery system for

267 The PLGA polymer, when emulsified in Pluronic F127/dextran A

268 The PLGA-GA NS loaded with cyclosporine A (CsA), a model pep

269 , radical-mediated process that degrades the PLGA nanoparticles and releases the molecule.

270 while the controlled release of GLN from the PLGA-GLN pellet resulted in A-GD-PLL microcapsule degrad

271 t storage stability when encapsulated in the PLGA microspheres.

272 f stable IPV release upon degradation of the PLGA matrix.

273 The internal structure of the PLGA microspheres was evaluated using low temperature sc

274 nor were controlled by the bioerosion of the PLGA microspheres.

275 of infectious challenge virus in most of the PLGA-KAg vaccinated pig lung airways were observed.

276 ace curvature and the surface tension of the PLGA.

277 Depending on the PLGA concentration, the particles either formed a core-s

278 Both cell types seeded on the PLGA/PLLA especially with 5% w/v HA recapitulated the ti

279 It was evident that the PLGA/PVA hydrogel composite was able to form a uniform c

280 We found that when the PLGA-COOH chains are sufficiently mobilized, therapeutic

281 e sensors (0.5x0.5x5mm) were coated with the PLGA/PVA composites using a mold fabrication process.

282 As these PLGA-encapsulated EtNBS nanoparticles are capable of pen

283 efined size and depth on the surface of thin PLGA films by stamping with blunt-tip microneedles.

284 nactivated influenza virus delivered through PLGA-NPs reduced the clinical disease and induced cross-

285 ith a minimum rate of thrombosis compared to PLGA and PLLA.

286 and altered distribution profile compared to PLGA NS in vivo.

287 cantly accelerated wound healing compared to PLGA or LL37 administration alone.

288 The kinetics of peptide sorption to PLGA was examined by incubating peptide solutions of 0.2

289 By using an uncapped PLGA (Mw=24,000-38,000) SNAP was slowly released for ove

290 The feasibility of utilizing PLGA microsphere/PVA hydrogel composites as coatings for

291 ug into the different polymers or by varying PLGA:PCL polymer ratios.

292 In vitro, PLGA-LL37 NP induced enhanced cell migration but had no

293 chemotherapeutic potential of double walled PLGA-chitosan biodegradable nanogel entrapped with 5-flu

294 ere prepared with different molecular weight PLGA polymers (approximately 25 and 7 kDa) to achieve di

295 ure forming a salt with low-molecular weight PLGA-COOH.

296 ration of CsA at 6 h as opposed to 24 h with PLGA-NS with at least 2-fold higher levels in brain at 7

297 f concept, microparticles were prepared with PLGA [poly(d,l-lactide-co-glycolide), 50:50, MW.

298 ckness excisional wounds, the treatment with PLGA-LL37 NP significantly accelerated wound healing com

299 Pigs vaccinated twice with PLGA-KAg via intranasal route showed increased antigen s

300 nt amounts of DNA can be encapsulated within PLGA-containing nanoparticles through the use of a new s