ライフサイエンスコーパス: drug release

1 S becomes hydrophilic and degrades to enable drug release.

2 higher payloads and 27-times faster initial drug release.

3 t yield, entrapment efficiency, and in-vitro drug release.

4 nerated parameterised mathematical models of drug release.

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

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

7 This approach also enables controlled drug release.

8 antibody was found to affect the kinetics of drug release.

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

10 d endocytosis and intracellular sequentially drug release.

11 complex features laser-triggered responsive drug release.

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

13 onitoring drug concentration kinetics during drug release.

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

15 re exposed disulfide bond sand intracellular drug release.

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

17 erature was utilized to trigger subcutaneous drug release.

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

19 d into three stages according to the rate of drug release.

20 g and technologically relevant to sensing or drug release.

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

22 gn of optimisation strategies for controlled drug release.

23 igh drug loading and significantly prolonged drug release.

24 high-throughput drug screening and prolonged drug release.

25 diagnostics, tissue scaffolding and targeted drug release.

26 th potential for spatiotemporally controlled drug release.

27 mbrane structure, which results in very slow drug release.

28 n the context of factors associated with the drug release.

29 three-layered fibrous scaffold for prolonged drug release.

30 ly water-soluble drugs and achieve sustained drug release.

31 half ester moieties to improve intracellular drug release.

32 limited by solubility and undesirable burst drug release.

33 CL gels in a wet environment and sustainable drug release.

34 ncing rapid interface-assisted diffusion and drug release.

35 od to enhance physical stability and control drug release.

36 ting feature, and extremely long duration of drug release.

37 o cytotoxicity and, where tested, sufficient drug release and a competent release profile.

38 ALDC1 exhibited improved drug release and cytotoxicity compared to ALDC3 in vitro

39 or ultrasound activated, macrophage-directed drug release and delivery.

40 ed a predictive model of in vivo stent based drug release and distribution that is capable of providi

41 s were optimized for their impact on in vivo drug release and drug degradation.

42 Drug release and effectiveness of melatonin using PolyRa

43 ly of FDA-compliant constituents to optimize drug release and expedite clinical translation.

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

45 criteria that impact the rate and extent of drug release and hence the occurrence or not of LLPS upo

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

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

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

49 lasma, CVF, and cervical tissue samples, and drug release and plasma drug exposure were higher for th

50 ein, where the peptoid modulated the rate of drug release and prolonged protein stability against pro

51 ited improved colloidal stability, prolonged drug release and remarkable cytotoxicity in human pancre

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

53 re have been no previous reports on in vitro drug release and the release mechanism from LNG-IUSs.

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

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

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

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

58 ersally accepted method for testing in vitro drug release, and only one non-compendial shaking incuba

59 icient drug-loading capacity and inefficient drug release, and require complex modification processes

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

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

62 ummary, the reversible pH-responsive and non-drug release antibacterial resin adhesives ingeniously o

63 stigated for spatiotemporal chemotherapeutic drug release applications for cancer chemotherapy.

64 heir ability to fix solid microparticles for drug-release applications, using tetracycline hydrochlor

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

66 ompetent, biocompatible, and capable of dual drug release are designed for regenerative engineering a

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

68 r biomedical applications such as controlled drug release are usually synthesized with the chemical o

69 Using an in vitro drug release assay, we demonstrated that the bi-layered

70 Our in vitro drug-release assay revealed that NL-encapsulated 6-shoga

71 the dialysis methodology applied to in vitro drug release assays.

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 Results obtained from in vitro kinetics drug release at human body temperature (37 degrees C) an

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

76 To ensure drug release at zero-order rates, empirical and theoreti

77 appear to be good candidates for controlled drug release based wound dressing applications.

78 for VCV and 6.45 for MK-2048), with greater drug released based on residual drug levels.

79 ics and critical characteristics influencing drug release behavior are discussed.

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

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

82 ycolide) (PLGA) matrix, thereby altering the drug release behavior.

83 The observed drug release behavour is related to the porosity of the

84 pics, electrophysiology, tissue engineering, drug release, biosensing, and molecular bioelectronics,

85 triggerable polymer self-immolation promotes drug release by switching the hydrophobic core into comp

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

87 Furthermore, we showed that drug release can be influenced by adding dimethyl sulfox

88 the cascade of ROS generation and antitumor-drug release can effectively inhibit tumor growth.

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

90 The multimodal imaging and NIR-triggered drug release capabilities of the proposed nanoplatform v

91 rmed in vivo evaluation to demonstrate rapid drug releasing capability in the subcutaneous space of m

92 importance of the biomolecular corona to the drug release capacity of various types of nanocarriers,

93 nd image-guided drug delivery with a tunable drug release capacity.

94 ture, pressure and biopotentials), sustained drug release, cardiovascular and pulmonary stents and ot

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

96 are more complex in terms of manufacturing, drug release characteristics as well as release mechanis

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

98 arenteral PLGA microspheres with multiphasic drug release characteristics.

99 tate understanding of the differences in the drug release characteristics.

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

101 r drug targeting, high drug loading, control drug release, compatibility with a wide range of drug su

102 Drug release converts those monomers to more hydrophilic

103 Thus, the apparent drug release data outside the dialysis bag typically doe

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

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

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

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

108 ms should provide a basis for adjustments of drug release dosage and duration, thereby contributing t

109 A higher DL, however, shortened the drug release duration from 56 to 42 days.

110 lated and free drug, surfactant, and also NP drug release dynamics, quantitatively interconnected to

111 how prolonged retention, remotely controlled drug release, enhanced targeted accumulation, and effect

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

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

114 Sunb-malate MS sustained the drug release for 30 days under the in vitro infinite sin

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

116 cles have potential to be used for on-demand drug release for an enhanced chemotherapy to effectively

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

118 were utilized as release media to accelerate drug release for LNG-IUSs.

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

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

121 ent years, the development of new methods of drug release from ADCs has continued in parallel to the

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

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

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

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

126 The mechanism of drug release from complex dosage forms, such as multives

127 Clearly, the in vitro and in vivo drug release from conjugated drug-loaded microspheres (P

128 However, studies of controllable long-term drug release from electrospun membrane systems and the u

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

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

131 We report a new approach to monitor drug release from nanocarriers via a paclitaxel-methylen

132 nal finite element (FE) models for diffusive drug release from nanofibers to the three-dimensional (3

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

134 The targeted and sustained drug release from stimuli-responsive nanodelivery system

135 SHC suppressed drug release from TBH but statistical significance was n

136 SHC severely inhibited drug release from TBH, but almost no effects on DKS.

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

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

139 eak inhaled pressure (PIP) and amount of the drug release from these DPIs before and after closure of

140 Experimental data of drug release from various nanoparticle formulations obta

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

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

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

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

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

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

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

148 aocular lens, vitreous substitutes, vitreous drug release hydrogels, and cell-based therapies for reg

149 Drug-releasing implants exhibited no significant differe

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

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

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

153 presence of platinum salts for extracellular drug release in cancer cells.

154 ability and low solubility enabled sustained drug release in mice following a single subcutaneous dos

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

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

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

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

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

160 for examining the spatial patterns of local drug release in the brain and the extent of the resultan

161 rocess of drug distribution and mechanism of drug release in the context of formulation-associated va

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

163 The current results demonstrate that slowing drug release in the mammary duct after intraductal admin

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

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

166 In these emulsions, drug release is a complex process due to drug distributi

167 Using 3D cell culture, it is shown that drug release is commensurate with cell density, revealin

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

169 and determinations of release duration, the drug release kinetics and critical characteristics influ

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

171 be a simple approach to determine the actual drug release kinetics from nano drug carriers inside the

172 cal model is applied to determine the actual drug release kinetics from the experimental data.

173 implication of the surface morphology on the drug release kinetics is examined.

174 property of each formulation, i.e., in vivo drug release kinetics leading to their respective pharma

175 re frequently used to determine the in vitro drug release kinetics of nanoparticle drug delivery syst

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

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

178 l gelation temperature, gelling behavior and drug release kinetics of the hydrogels.

179 The drug release kinetics of the P(NIPA)-based hydrogels are

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

181 nd internal morphologies, drug loadings, and drug release kinetics, and thus, to control them.

182 ly PLGA depot formulations with controllable drug release kinetics, but also generic formulations of

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

184 has been limited because many factors affect drug release kinetics.

185 pot formulations as their properties control drug release kinetics.

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

187 lectrostatic charge, may directly impact the drug release kinetics.

188 Understanding drug-release kinetics is critical for the development of

189 excipient widely exploited in oral sustained drug release matrix systems.

190 nanocarriers, but also its interference with drug release measurements.

191 is requires an understanding of the LNG-IUSs drug release mechanism and the development of a sensitiv

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

193 Based on these results a potential MVL drug release mechanism was proposed, which may assist wi

194 release conditions allowing for study of the drug release mechanism.

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

196 elease exponents, n, which correspond to the drug release mechanisms, were found to be between 0.41 a

197 iffusible signal molecules delivered through drug-releasing microparticles.

198 Providing fast drug release, nanocrystals significantly accelerated the

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

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

201 In vitro drug release of minoxidil sulphate from nanofiber exhibi

202 which further boosts tumor-selective active drug release of MMP9-DOX-NPs by 3.7-fold in an orthotopi

203 rocess of drug distribution and mechanism of drug release of ophthalmic emulsions in the context of f

204 tro drug release profiles showed a sustained drug release of sildenafil citrate for over 24 h.

205 Non-irradiated PolyRad demonstrated maximum drug release of ~70% after 72 h, while UV-irradiated and

206 nd H(2)O(2)-treated PolyRad showed a maximum drug release of ~85%.

207 he paper also presents the effects of cancer drug release on cell survival (%), as well as the cell m

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

209 o achieve superior distribution and extended drug release over time.

210 CLM displayed a drug release pattern in response to pH/enzyme dual stimu

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

212 onal additives that ultimately influence the drug release performance and absorption.

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

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

215 Drug release, polymer erosion, polymer degradation, and

216 eting, mitochondria targeting, bioresponsive drug release, pro-apoptosis, and anti-mobility, can be d

217 dant groups via linker cleavage, and as this drug release proceeds, the polymer chains losing hydroph

218 introduced three-layered scaffold delays the drug release process and can be used for the time-contro

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

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

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

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

223 y of an in silico approach to optimising the drug release profile and ultimately the effectiveness of

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

225 The in vitro drug release profile of FGF from PXDDA film and cell gro

226 The apparent drug release profile of the nanocarrier is then determin

227 enabling efficient encapsulation, a tunable drug release profile, improved nanoparticle size uniform

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

229 chanism of the LNG-IUSs considering the full drug release profile.

230 ulated 6-shogaol (6-S-NL) exhibits a delayed drug-release profile compared to free 6-shogaol (free-6-

231 The in vitro drug release profiles at 37 degrees C showed that over 9

232 It is found that the drug release profiles can be divided into three stages a

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

234 The in-vitro drug release profiles showed a sustained drug release of

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

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

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

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

239 ized premature drug leakage and synchronized drug release profiles.

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

241 eptor saturation, but also on the consequent drug release rate being tuned to ensure prolonged satura

242 probably a consequence of the extremely slow drug release rate of LNG-IUSs under real-time in-use con

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

244 Experimental results of drug release rates from the scaffold are compared with t

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

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

247 Activatable liposomes, with drug release resulting from local heating, enhance serum

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

249 An in vivo murine drug release showed a photoacoustic signal enhancement o

250 The drug release showed sustained release pattern noted up t

251 erapy with high tumor-targeting accuracy and drug release specificity is the key to improve the effic

252 Bulk chemotherapy and drug release strategies for cancer treatment have been a

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

254 was investigated both experimentally, using drug release studies, and theoretically using classical

255 of framework topology, aluminium content and drug release study media.

256 A model drug release study with these plasma gels indicated slow

257 An in vitro drug-release study showed an initial burst release (25 %

258 k demonstrates a proof-of-concept responsive drug-release system that may be used in implantable devi

259 (DAPI), was achieved with this self-powered drug-release system.

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

261 spinning is an attractive method to generate drug releasing systems.

262 as his following work in polymer-controlled drug releasing systems.

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

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

265 nts) predicts that this radiation-controlled drug release technology enables significant improvements

266 (8.6mm) were more efficient at accelerating drug release than longer channels (18.2mm) despite havin

267 44 degrees C) reveal a non-Fickian sustained drug release that is well-characterized by Korsmeyer-Pep

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

269 revious research has demonstrated incomplete drug release to always be a feature of OMS formulations.

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

271 ical models can serve as efficient tools for drug release to the surrounding porous medium or biologi

272 ion, this approach, involving ROS-responsive drug release, together with the identification of the ta

273 and PLGA concentration had major effects on drug release, too.

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

275 surface silanol moieties leads to incomplete drug release under a wide range of dissolution condition

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

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

278 le drugs, such as DSP, and achieve sustained drug release using conventional encapsulation methods.

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

280 Drug-releasing vaginal rings are torus-shaped devices, g

281 the scientific literature, and despite seven drug-releasing vaginal rings having been approved for ma

282 c literature for testing in vitro release of drug-releasing vaginal rings.

283 Complete drug release was achieved in 32 and 672 days in THF and

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

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

286 Drug release was not suppressed by SHC in DKS, while it

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

288 Drug release was sustained over 48h from SLNs, compared

289 Drug release was triggered by proteases with >50% releas

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

291 Degradation behavior and MMP-8-responsive drug release were performed by high-performance liquid c

292 but rapid micellar breakdown and concomitant drug release, when in breast cancer cells with increased

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

294 their potential for precise and controllable drug release with different applications in personalized

295 rst oral dosage form that achieves multi-day drug release with near zero-order kinetics and efficient

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

297 All drugs released with concentrations above their protein-a

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

299 dride (PA) in 2:1:1 M ratio that enabled 50% drug release within 38.5 h followed by sustained release

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