ライフサイエンスコーパス: drug release

1 igh drug loading and significantly prolonged drug release.

2 high-throughput drug screening and prolonged drug release.

3 diagnostics, tissue scaffolding and targeted drug release.

4 s, water uptake occurred simultaneously with drug release.

5 local hyperthermia to achieve heat-triggered drug release.

6 thereby a considerable change in the rate of drug release.

7 lular uptake, intracellular trafficking, and drug release.

8 pies of cancer by promoting tumour-selective drug release.

9 art" MNPs for stimulus-responsive controlled drug release.

10 experimental therapeutic approach to control drug release.

11 a general drug carrier model for controlled drug release.

12 o peroxidation of liposomal lipids, allowing drug release.

13 hemistry, increased drug binding and altered drug release.

14 eld was sufficient to remotely trigger rapid drug release.

15 ch can sense and overcome MDR prior to local drug release.

16 tumor penetration, cell internalization, and drug release.

17 n real-time and were a reliable predictor of drug release.

18 ygen species (ROS) triggered degradation and drug release.

19 have been developed to trigger site-specific drug release.

20 ative called ZWC (Z) to trigger pH-sensitive drug release.

21 NIR light exposure, causing 2-5x increase in drug release.

22 sulting hydrogels demonstrated ROS-dependent drug release.

23 ion, nanostructure templates, biosensors and drug release.

24 mechanical effects of focused ultrasound for drug release.

25 s that are stable throughout the duration of drug release.

26 at shrinkage enhanced tissue penetration and drug release.

27 isk of release of Gd ions, and NIR-triggered drug release.

28 This approach also enables controlled drug release.

29 ion was developed to allow the prediction of drug release.

30 d endocytosis and intracellular sequentially drug release.

31 complex features laser-triggered responsive drug release.

32 on both the bioactivity and the kinetics of drug release.

33 onitoring drug concentration kinetics during drug release.

34 eep MCCs are crucial to induce the sustained drug release.

35 re exposed disulfide bond sand intracellular drug release.

36 ible phase-change material for NIR-triggered drug release.

37 erature was utilized to trigger subcutaneous drug release.

38 ty, cellular uptake, and photoregulated dual drug release.

39 g and technologically relevant to sensing or drug release.

40 ts at the tablet-medium interface that drive drug release.

41 gn of optimisation strategies for controlled drug release.

42 their phase transition behavior, and in-vivo drug release; a coarse emulsion-forming ME (CE-ME), an o

43 ysiological sensors, non-volatile memory and drug-release actuators.

44 potential for cell targeting and controlled drug release after administration, here we investigated

45 lso made a brief excursion into the field of drug release and delivery.

46 uch interactions to be able to delay/control drug release and for polymer architecture and compositio

47 -link PEG hydrogels, and demonstrate tunable drug release and hydrogel erosion rates over a very wide

48 take by tumor cells, sustained intracellular drug release and in vitro efficacy superior to free ther

49 ropagation in polymeric materials to control drug release and its first demonstration are reported.

50 are applicable to in vivo photocontrollable drug release and other biophotonic applications.

51 h has shown promising results for controlled drug release and shape memory devices.

52 ibility of SiO2, the feature of controllable drug release and simultaneous carrier decomposition achi

53 Sustained drug release and strong MRI T2 and CT contrast effects w

54 The DNA device could be used for controlled drug release and the building of synthetic cell-like or

55 te-specific chemotherapy, but also triggered drug release and thus greater spatial and temporal contr

56 modeling the drug-binding site to facilitate drug release and to reset the transporter for a new tran

57 ghly promising to control the time-course of drug release and ultimately optimize drug concentration

58 Drug-releasing and control CGM implants were compared in

59 Ds are promising for localized and sustained drug release, and can effectively enhance the proliferat

60 surface morphology, respirability, in-vitro drug release, and evaluated for in vivo absorption, alve

61 s for imaging, for light delivery to trigger drug release, and for monitoring drug concentration kine

62 fficacy, determine the mode and mechanism of drug release, and identify alternatives to avoid toxicit

63 ibility, high selectivity of redox-triggered drug release, and significant anticancer performance.

64 interesting application is for controllable drug release, and this has been realized previously usin

65 r biodistribution, target site accumulation, drug release, and treatment efficacy.

66 A-PEG), was highly stable, provided extended drug release, and was effective against F98 cells in vit

67 ease of surface modification and controlled drug release are additional advantages with polymeric mi

68 Similarly, the approaches toward controlled drug release are discussed.

69 ons of this approach for remote actuation of drug release as well as effects on biomacromolecules, bi

70 sidues Y506 and Y507 are not responsible for drug-release as suggested previously but rather for intr

71 Drug release assays confirmed pH responsive release of g

72 attachment of targeting ligands, dynamics of drug release, assessment of nanocarrier stability in bio

73 The ability to control drug release at a specific physiological target enables

74 was acid-responsive, as evidenced by faster drug release at low pH and with co-incorporation of PLGA

75 ure development of manufacturable TMUPS with drug release behavior similar to that of the original co

76 ear-infrared (NIR)-responsive remote control drug release behavior was designed for applications in t

77 The design, drug release behavior, and clinical potential of various

78 /PA imaging properties, pH-/photo-responsive drug release behavior, and promoted cellular endocytosis

79 i-responsive protein or nanoparticle arrays, drug releasing biomedical device surfaces and self-heali

80 heads, self-immolative disulfide linkers for drug release, biotin as the tumor-targeting moiety, and

81 The relevant DDS can be activated to promote drug release by different types of mechanical stimuli, i

82 g fluorescence spectroscopy to rapidly assay drug release by quantifying the time-dependent increase

83 hich better mimic this environment and cause drug release by the relevant mechanistic processes, ulti

84 ting the monomer(s)/initiator feed ratio and drug release can be encoded into the polymer by the choi

85 ications of water soluble PHAs in controlled drug release, cancer therapy, DNA/siRNA delivery and tis

86 e that the development of TSL with ultrafast drug release capabilities needs to progress in parallel

87 g capacity/release, magnetic field triggered drug release, cell uptake and localization) in order to

88 Our finding highlights the novel and unique drug release character of LbL systems in serum condition

89 are the most decisive factors in controlling drug release characteristics in our model.

90 ng and b) divisible without compromising the drug release characteristics of the individual units.

91 NPs with appropriate physical and sustained drug-release characteristics could be explored to treat

92 ful tool as a drug carrier or a pH sensitive drug-release compound.

93 ethods that are capable of mimicking in vivo drug release conditions.

94 ves as an Fe(II)-sensitive "trigger," making drug release contingent on Fe(II)-promoted trioxolane fr

95 A comparison of experimental and predicted drug release data revealed that in addition to surface a

96 phology and porosity, mechanical properties, drug release, degradation, and osteogenic differentiatio

97 wledge, this represents the first long-term, drug-releasing depot that can be administered as a tradi

98 by anisotropic stent structure or asymmetric drug release designed to yield homogeneous drug distribu

99 scale systems that utilize remote controlled drug release due to actuation of MNPs by static or alter

100 lated during persistent DNA damage and after drug release during the acquisition of the senescent phe

101 Drug release estimates for the fast releasing Taxotere f

102 SLs) and NTSLs (ENTSLs), 2) evaluate in vivo drug release following short duration ( 20min each) HIFU

103 SLs) and NTSLs (ENTSLs), 2) evaluate in vivo drug release following short duration (~20min each) HIFU

104 nstrated a sustained degradation of OPS with drug release for 3 months without evidence of toxicity;

105 icle porosity, drug entrapment, and produced drug release for 36h.

106 ivo disposition in the context of controlled drug release for achieving anatomical, physiological and

107 ted devices could exhibit sustained on-state drug release for at least 3 h, and could reproducibly de

108 50) in the PEU polymer effectively sustained drug release for at least 3months.

109 for 2 and 3weeks, respectively, despite fast drug release for g-EAR in vivo versus in vitro.

110 y tailoring of a particular drug combination/drug release for the needs of an individual.

111 ddition to surface area/mass when optimizing drug release from 3D printed designs.

112 plets with perforated channels to accelerate drug release from 3D printed tablets.

113 In this paper we present a general model of drug release from a drug delivery device and the subsequ

114 coustic lens, were introduced to trigger the drug release from alginate microgels encapsulated with d

115 s and/or the tumor microenvironment triggers drug release from an Fe(II)-reactive prodrug conjugate.

116 te results for the particular application of drug release from arterial stents.

117 nd the in vivo environment and how it causes drug release from biodegradable microspheres.

118 potentially crucial role for the control of drug release from coated pellets.

119 rlying mass transport mechanisms controlling drug release from coated pellets.

120 Drug release from fat was quantified by HPLC/MS/MS, and

121 of the influence of DNA architecture for the drug release from functional nano-sized surface.

122 We propose a new transport model of drug release from hydrophilic polymeric matrices, based

123 experiments were designed to investigate the drug release from liposome by Pluronic P85.

124 pment of the LGFU as a stimulus for promoted drug release from microgels integrated with drug-loaded

125 racterize the time-course of light activated drug release from near infrared (NIR) activated photothe

126 etals is challenging, and short durations of drug release from polyketal particulate formulations lim

127 wed Higuchi's model that describes sustained drug release from polymeric matrices.

128 approach to model development for controlled drug release from polymeric microspheres is taken herein

129 to describe PLGA degradation and erosion and drug release from the bulk polymer.

130 Controlled drug release from the delivery system was mediated by ph

131 Drug release from the erythrocyte carrier was confirmed

132 ivering extrinsic liposomal ATP promoted the drug release from the fusogenic liposome in the acidic i

133 study investigates a possibility to enhance drug release from the liposomes and increase therapeutic

134 sis device (the receiver), instead of actual drug release from the nanoparticles inside the dialysis

135 Experimental data of drug release from various nanoparticle formulations obta

136 ith DOX showed cytotoxicity at 37 degrees C, drug released from films at lower temperature exhibited

137 The percentage of drug released from the delivery system was significantly

138 ma components identical to the normoisotopic drug released from the nanomedicine formulation.

139 the subcellular mechanism of action for each drug released from the NP mirrors that of the unbound, f

140 tained release as well as a higher amount of drug released from the polymeric matrix.

141 -transfer step, which determines the time of drug release, from as large as the dosage form itself to

142 omenon that has been intensely exploited for drug release, gene delivery, cancer thermotherapy, and e

143 Targeted delivery combined with controlled drug release has a pivotal role in the future of persona

144 The discipline of controlled drug release has grown to include most areas of medicine

145 less, the concurrent real time monitoring of drug release has not been widely studied.

146 nsive formulations or devices for controlled drug release have been developed.

147 depot formulations for long-term controlled drug release have improved therapy for a number of drug

148 internalization and implement the controlled drug release, herein an iRGD peptide-modified lipid-poly

149 here can be used to help control the pace of drug release; however, it remains to be seen whether an

150 Drug-releasing implants exhibited no significant differe

151 s they provide benefits including controlled drug release, improved biological half-life, reduced tox

152 igate how drug-carrier compatibility affects drug release in a tumour mouse model.

153 jugation per peptide could also regulate the drug release in addition to its apparent effect on drug

154 or by administrating mannitol, facilitating drug release in an acidic tumor environment and triggere

155 Existing methods to measure nanomedicine drug release in biological matrices are inadequate.

156 nanocarriers able to minimize the premature drug release in blood circulation while releasing drug o

157 luorescent switching that is proportional to drug release in malignant tissues.

158 TSLs did not impact size or caused premature drug release in physiological buffer.

159 studies: confocal microscopy, stability and drug release in physiological conditions, and biodistrib

160 r cells and can be used to image and monitor drug release in real time.

161 ibit prominent photothermal effect and quick drug release in response to NIR irradiation.

162 Taste masking techniques aim to prevent drug release in saliva and at the same time to obtain th

163 nly reaches the nucleus after acid-triggered drug release in the endo-lysosomes.

164 The simulated drug release in the peritoneal cavity linearly correlate

165 e gastrointestinal tract, while allowing for drug release in the proximity of a tumor.

166 titative understanding of the time-course of drug release in vivo and will be essential in the develo

167 ug release with approximately 75% cumulative drug released in 5h.

168 ting of the nanocarrier SERS sensor involved drug release induced by lowering pH and increasing GSH l

169 , which is an endogenous thiol that triggers drug release inside the cancer cells.

170 t efficiency (EE), in vitro permeability and drug release (investigated with Caco-2 monolayers and di

171 his problem of inefficient and unpredictable drug release is compounded by the present lack of low-co

172 -rich substances and glycoproteins when fast drug release is desired.

173 A model drug release is examined and control of degradation kine

174 rapid or not relevant, and additionally when drug release is not limited by its solubility.

175 Further optimization of drug release is required to minimize thrombosis risk whi

176 the core of the IVR whereby the mechanism of drug release is uncoupled from the interaction of the dr

177 g particles taken orally, in particular, the drug release kinetics and interaction with the gastroint

178 ic manner, but also potentially controls the drug release kinetics at the targeted tissues.

179 However, actual drug release kinetics of nanoparticles cannot be readily

180 g numerical deconvolution to evaluate actual drug release kinetics of nanoparticles inside the donor

181 ired treatment efficacy and safety profiles, drug release kinetics of nanoparticles must be controlle

182 The drug release kinetics were governed by the protonation s

183 of biostability, active targeting, desirable drug release kinetics, and combination therapies into Lb

184 of balloon-based delivery systems, including drug release kinetics, matrix coating transfer, transmur

185 ed by scanning electron microscopy, in vitro drug release kinetics, MSC uptake and internalization: a

186 ntion, providing tight control over embedded drug release kinetics.

187 manipulate the geometry of the patch and the drug release kinetics.

188 as to understand the polymer degradation and drug release mechanism from PLGA microspheres embedded i

189 , a mathematical model can help identify key drug release mechanisms and uncover the rate limiting pr

190 It is independent of particle formulations, drug release mechanisms, and testing conditions.

191 release systems and establishing controlled drug release mechanisms.

192 A novel drug release method utilizing a stable isotope tracer ha

193 iffusible signal molecules delivered through drug-releasing microparticles.

194 peutic efficacy integrated with a controlled drug-release modality.

195 unctionalization, nanotopography, responsive drug release, motion-based responses, and permeation enh

196 Providing fast drug release, nanocrystals significantly accelerated the

197 Burst drug release occurred followed by pore forming from the

198 axel and rubone, respectively, controlling a drug release of 60.20% +/- 2.67% and 60.62% +/- 4.35% re

199 In vitro study showed more sustained drug release of CM-AL-containing scaffolds than these of

200 oblems associated with thrombosis and due to drug release only postpone their advance for a longer pe

201 ture applications in multikinetic control of drug release, or as patterned scaffolds for directed tis

202 solution, these meshes exhibit slow initial drug release over 10days corresponding to media infiltra

203 f 200 nm, 8 wt.% drug loading, and sustained drug release over 15 days in vitro under sink conditions

204 ore, a drug delivery device that can achieve drug release over several months can be highly beneficia

205 l for understanding mechanisms and designing drug release particles.

206 g delivery to the vessel wall, such that the drug release per unit surface area is kept constant alon

207 adation of the core continued throughout the drug release period.

208 water uptake at the later stages and in the drug release phase.

209 tion and swelling occurred before the second drug release phase.

210 us offers a convenient and robust controlled drug release platform and has attracted increasing atten

211 applied as bioactive coatings and provide a drug-release platform in in vitro cell culture studies.

212 a surge of reports utilizing periadventitial drug-releasing polymer platforms, most commonly bioresor

213 ety of external stimuli used to meditate the drug release process have also been investigated.

214 thioether bond is monitored to visualize the drug release process, and effective targeted delivery of

215 nce read-out to enable quantification of the drug release process.

216 escence read-out capability also enabled the drug-release process to be followed in living cells with

217 The drug release profile from PLGA NMP was tri-phasic, being

218 ment, the RBC-nanogels showed an accelerated drug release profile, which resulted in more effective b

219 Drug release profiles and distribution in the polymer, a

220 Predictions of drug release profiles by mechanistic models are useful f

221 ake into the microspheres coincided with the drug release profiles for both formulations.

222 of the experimental polymer dissolution and drug release profiles in a system of Theophylline/cellul

223 Nanofilms designed to drug release profiles in programmable fashion are promis

224 and hence surface area to enable control of drug release profiles without the need to alter the form

225 roperties of photosensitizers (PSs), optimal drug release profiles, and the photosensitivity of surro

226 oximately 25 and 7 kDa) to achieve different drug release profiles, with a 9-day lag phase and withou

227 al to obtain combined therapies with desired drug release profiles.

228 polymers may provide enhanced control of the drug release profiles.

229 ng efficiency, stability and redox-sensitive drug release profiles.

230 ized premature drug leakage and synchronized drug release profiles.

231 ection and enables precise modulation of the drug release profiles.

232 Further drug release prolongation was reached with formation of

233 Rhein-containing nanocarriers have sustained drug release, prolonged circulation, increased tolerated

234 embrane stability, in vivo interactions, and drug release properties of a liposome.

235 targeting, increased stealth, and controlled drug-release properties.

236 ellular accumulation efficiency and the free drug release rate are two important factors that determi

237 onally designed, looking at drug loading and drug release rate by adequate linker design, always cons

238 In most cases, the free drug release rate is controlled by the use of various ch

239 iency but boosts initial transport speed and drug release rate, which may facilitate efficient multid

240 the importance of assessing a wide range of drug release rates during formulation screening as a cri

241 Surprisingly, the drug release rates of these conjugates were tailorable b

242 duce initial drug burst, and further control drug release rates over a broader range.

243 allows the cellular dosage forms to achieve drug release rates over an order of magnitude faster com

244 This may be due to different drug release rates resulting from steric hindrance to th

245 The drug release rates, robust superhydrophobicity, in vitro

246 onal gels typically have little control over drug release rates.

247 of nanocomposites and optimizing controlled drug release, resulting in better cell in-growth and ost

248 onjugated to DUPA via a peptide linker and a drug-release segment that facilitates intracellular clea

249 The drug release showed sustained release pattern noted up t

250 e extended from smart coatings to controlled drug release, smart windows, self-repair and other field

251 ute an appealing means to direct and confine drug release spatiotemporally at the site of interest wi

252 s provide spatially and temporally localized drug-release strategies that can facilitate high local c

253 can switch to an outward facing (drug off or drug releasing) structure of lower affinity.

254 Drug release studies indicated that PTX released from th

255 In vivo drug release study demonstrated that free DNR in the vit

256 tility of this method, we performed a plasma drug release study with both a fast releasing commercial

257 soft, hydrogel-based vehicles for triggered drug release suggest their broad potential uses in biome

258 This ATP-triggered drug release system provides a more sophisticated drug d

259 Externally controlled drug release systems hold potential to selectively enhan

260 uding rewritable liquid patterns, controlled drug release systems, lab-on-a-chip devices, and biosens

261 Epicardial (EC) drug releasing systems were used to apply epinephrine to

262 ens new ways to design autonomous actuators, drug-release systems and active implants.

263 ffered for designing effective intracellular drug-release systems, holding great promise for future c

264 (8.6mm) were more efficient at accelerating drug release than longer channels (18.2mm) despite havin

265 mphiphilic beads act as depots for sustained drug release that is integrated into the fibrillar scaff

266 a large portion of polymer, which slows down drug release through erosion and diffusion mechanisms.

267 le excipients for drug formulation to enable drug release to a targeted lesion site effectively, main

268 2O2 level and self-sufficing H2O2-responsive drug release to achieve novel synergistic oxidation-chem

269 rform on-demand magnetoelectrically assisted drug release to kill cancer cells.

270 o promote device adhesion and unidirectional drug release toward epithelial tissue, thereby prolongin

271 ontaining ATP was developed for ATP-mediated drug release triggered by liposomal fusion.

272 The degree of drug release triggered by NIR laser light could be adjus

273 r cell death by controlled, stimulus-induced drug release under acidic conditions in endosomal compar

274 The enhanced rate of drug release under acidic conditions, successful uptake

275 s of saccharide-modified polymers to mediate drug release under desired conditions.

276 he particle and prevents undesired premature drug release until the shedding of the shell, which acce

277 olymer, which allows noninvasively triggered drug release using brief, low-power light exposure.

278 retinal pigment epithelial cells, studies of drug release using radiochemical approaches showed that

279 The printed polypills were evaluated for drug release using USP dissolution testing.

280 or droplet shells) allowing adequate rate of drug release via drug diffusion and/or copolymer biodegr

281 nanosystem design in mediating drug storage, drug release (via heat), and killing of HeLa cells in cu

282 External control of drug release was achieved via NIR laser light and plasma

283 vantage of the magnetism, remotely triggered drug release was facilitated by magnetic attraction acco

284 dent on the stiffness of the phantoms, while drug release was found to be dependent on both phantom p

285 Notably, drug release was influenced by liposome composition and

286 predictions and the experimental studies of drug release was obtained.

287 these polymer-drug conjugates concluded that drug release was unnecessary for activity, highlighting

288 rate constants resulting from intravascular drug release were detectable by MRI.

289 over, in vitro cell uptake and intracellular drug release were determined via FRET intensity changes.

290 thermal treatment or by remote triggering of drug release when there is retardation of antibiotic dif

291 ed LDLs can also enable metabolism-triggered drug release while preventing the payloads from lysosoma

292 herapy by enabling spatiotemporal control of drug release while reducing systemic drug exposure and a

293 eful treatment strategy to achieve long-term drug release with a single intramuscular (IM) injection,

294 Devices showed steady drug release with approximately 75% cumulative drug rele

295 phyrin-phospholipid, which enables on-demand drug release with near-infrared irradiation.

296 al relationship between in vitro and in vivo drug release, with the latter often estimated by deconvo

297 vitro release kinetic data showed sustained drug release within the therapeutic window for 168h (NP

298 orubicin demonstrated sustained intravitreal drug release without ocular toxicity, which may be usefu

299 ld be disrupted by laser irradiation so that drug release would be triggered remotely at the tumor si

300 delivery platform would allow for sustained drug release yet exert minimal mechanical and inflammato