ライフサイエンスコーパス: payload

1 stops advancing the needle and delivers the payload.

2 ukin-3 fused to a truncated diphtheria toxin payload.

3 e Orbitrap to characterize metabolism of the payload.

4 the same calicheamicin gamma(1) (I) -derived payload.

5 linker, and potent topoisomerase I inhibitor payload.

6 y and monomethyl auristatin E as a cytotoxic payload.

7 able linker, and a topoisomerase I inhibitor payload.

8 ulting in subsequent endocytic uptake of the payload.

9 increasing the number of cells that received payload.

10 tion and brain accumulation of the darunavir payload.

11 armed with a monomethyl auristatin E (MMAE) payload.

12 must experience before it releases it's drug payload.

13 other ADCs with maytansinoid derivatives as payload.

14 sma, exactly matching the mass of the linker-payload.

15 d by the physicochemical properties of LTSLs payload.

16 retention and prolonged release of the gene payload.

17 mes more than the control untargeted peptide payload.

18 be modified directly with a desired genetic payload.

19 -based linker, and topoisomerase I inhibitor payload.

20 ieces of linker structures and as functional payloads.

21 are endowed with the properties of specific payloads.

22 apy has been the delivery of oligonucleotide payloads.

23 ADCs for the targeted delivery of cytotoxic payloads.

24 an the level of drug required with other ADC payloads.

25 ing the controlled release of pharmaceutical payloads.

26 s prominently includes their protein and RNA payloads.

27 ow site-specific conjugation with various Ag payloads.

28 antibodies armed with potent small-molecule payloads.

29 drugs and the NIR light triggered release of payloads.

30 niumdiolate NO donors and greater NO-release payloads.

31 mance under different weather conditions and payloads.

32 the delivery of a wide range of hydrophilic payloads.

33 nctional handle to append diverse biological payloads.

34 or of inhaled nanoparticle systems and their payloads.

35 and can accommodate variable length genetic payloads.

36 igh specificity of antibodies with cytotoxic payloads.

37 rdable candidate vehicles for these precious payloads.

38 ate containing non-cleavable auristatin drug payload (033-F).

39 A were 90-140 nm in size, had high darunavir payload (~11-13% w/w), good stability and minimal cellul

40 Payload 17 was conjugated to anti-mesothelin and anti-fu

41 ived nanotracer with a perfluoro-crown ether payload ((19)F-HDL) to allow myeloid cell tracking by (1

42 a significant proportion of the therapeutic payload (86%) was reproducibly delivered into the local

43 This likely allows greater payload accessibility for protein expression with micell

44 ne liver fibrosis model enhanced carrier and payload accumulation in the fibrotic tissue facilitated

45 ch allows controlled diffusion of the active payloads across the bilayer membranes.

46 le of in vivo formation of an albumin-linker-payload adduct.

47 albumin, forming a long-lived albumin-linker-payload adduct.

48 hallmark of cultured cells and tumors, their payload and biologic activity appears to be tightly regu

49 e subcutaneous inflammation to determine the payload and biologic activity of EVs released into the m

50 secretory repertoire of a cell regulates EV payload and biologic activity that affects outcomes in t

51 TBC1D3 regulates the payload and biological activity of extracellular vesicle

52 (~25 kDa), the identification of conjugated payload and its metabolites can be achieved with excelle

53 imultaneous imaging of TNP vehicle, its drug payload and single-cell DNA damage response reveals that

54 ies are obtained, reaching up to 40 % higher payloads and 27-times faster initial drug release.

55 methane leakage rate, to achieving the same payloads and cargo volumes as conventional diesel trucks

56 l species (in some cases also releasing drug payloads) and molecules that exacerbate LIP-induced oxid

57 eic acid cargo, exhibit sustained release of payload, and can stably transfect cells.

58 dy, linker, conjugation site, small-molecule payload, and drug-to-antibody ratio (DAR).

59 ective delivery and release of water-soluble payloads, and can be coupled to enzyme activity within t

60 ing better targets, more effective cytotoxic payloads, and further improvements in antibody-drug link

61 multaneously tests host species, therapeutic payloads, and synthetic gene circuits of engineered bact

62 e controllably loaded into the MOP with high payloads, and the nanocages are then superassembled to f

63 When coupled to antigenic payloads, anti-MHCII VHH primed Ab responses against GFP

64 dose-limiting toxicity of the small molecule payload, antibody-drug conjugates (ADCs) are administere

65 s of the linker between the antibody and the payload are proven to be critical to the success of an A

66 ow that intact mitochondria with their mtDNA payload are transferred in the developing tumour, and pr

67 iophysical properties and amount of released payloads are chief factors determining the overall ADC p

68 Charged peptide payloads are loaded into the pores of the pSiNP at appro

69 The toxic payloads are selectively linked to the interchain cystei

70 bears a non-cleavable linker, auristatin as payload at DAR = 4 and a low affinity antibody with effe

71 herapy by concentrating the immunomodulatory payload at the site of disease.

72 tible Poloxamer hydrogels, yet they released payloads at a ~5-fold slower rate in the subcutaneous ar

73 mparting a bulking effect to the therapeutic payloads attached to them.

74 he range of 2.5 to 2.7 and approximately 85% payload bound to the Fc region, presumably to histidine

75 pes; and 3) cytoplasmic release of the siRNA payload by escaping or bypassing endocytic uptake.

76 l nanoparticle-drug conjugate containing the payload camptothecin (CPT), to improve therapeutic respo

77 dence of either the nanoparticle or its drug payload (camptothecin, CPT) contained within the nanopar

78 th Ce6 and SPION is ~100%, and the total Ce6 payload can be as high as 56% of the total weight (Ce6 +

79 eedle-generated pores, from which the active payload can be released and diffuse laterally into the n

80 livery vehicles, from which the release of a payload can be triggered by NIR light and the release ra

81 Therapeutic payloads can also be loaded into the pH-responsive cap,

82 stidines under mild conditions where various payloads can be introduced via copper-assisted alkyne-az

83 The payloads can be released through the hole when the fatty

84 Therapeutic payloads can be targeted selectively to eosinophils and

85 y platforms due to the ability to tune their payload capacities and release rates by adjusting the lo

86 r) weighs 259 milligrams, with an additional payload capacity allowing for additional onboard devices

87 lability (frequency and ruggedness), sizing, payload capacity, amenability to mechanical programming,

88 ation efficiency (~ 100%) of exendin-4, high payload capacity, and high degrees of uniformity and sta

89 grating onboard electronics within a limited payload capacity.

90 of its potential immunogenicity and limited payload capacity.

91 NP(BTZ-DOX) prolonged payload circulation and targeted tumors in vivo efficien

92 The precision additives reach high payloads close to 1:1, rendering a photosensitizer water

93 However, selection of an optimum target and payload combination, to achieve maximal therapeutic effi

94 ach can facilitate the study of antibody and payload combinations for selection of promising candidat

95 observed between the measured released free payload concentration and the measured loss of drug-to-a

96 which consist of hydrophilic and hydrophobic payloads conjugated to two different antibodies, retain

97 complementarity-determining regions and the payload conjugation sites.

98 s using these chemistries yielding efficient payload conjugation.

99 ve DAR was lowered, decreasing the amount of payload delivered to each targeted cell but increasing t

100 ther areas of medicine requiring life-saving payload delivery as well.

101 Our electroporation protocols result in payload delivery to between 75 and 97% of living cells o

102 nables targeting specificity and therapeutic payload delivery to treat a variety of surgical diseases

103 potential applications for sensing and smart payload delivery.

104 ools for neuroanatomical mapping and genetic payload delivery.

105 rget radiation dose to healthy tissue during payload delivery.

106 preferentially bind to pancreatic tumors for payload delivery.

107 y to guarantee the protection and controlled payload delivery.

108 ally-actuated peptides for tumor-penetrative payload delivery.

109 utics with an emphasis on site-specific drug payload delivery.

110 -in engine for deeper and faster intradermal payload delivery.

111 force to breach dermal barriers and enhance payload delivery.

112 compositions containing from zero to several payloads, demands the use of advanced analytical charact

113 ies were found to be antibody-, linker-, and payload-dependent.

114 sents developments in vector engineering and payload design aimed at tailoring AAV vectors for transd

115 As a consequence, the proteinosome payload (dextran, single-stranded DNA, platinum nanopart

116 signed to selectively deliver the ultratoxic payload directly to the target cancer cells.

117 cacy of polymersomes to deliver encapsulated payloads directly into cell nuclei.

118 The mechanism and kinetics of the payload discharge appeared to be phospholipase A2 activi

119 diverse, clinically relevant anticancer drug payloads (docetaxel, cabazitaxel, and gemcitabine) were

120 ise dose whilst ensuring that the dry-coated payload does not significantly impact on MN skin penetra

121 ng the maximum number of cells with a lethal payload dose correlates more strongly with in vivo effic

122 atumoral distribution of ADC, independent of payload dose or plasma clearance, plays a major role in

123 and enhance the anticancer potency of a drug payload (doxorubicin hydrochloride).

124 DC configurations, by varying type of linker-payload, drug-to-antibody ratio (DAR), affinity and Fc f

125 to achieve the controlled release of a model payload (e.g., silica nanoparticles) encapsulated within

126 al properties of nanoparticles (NPs) and the payload efficacy of nanocarriers have been thoroughly in

127 materials for controlled release, where the payloads encapsulated in a solid matrix are released onl

128 nstable, too hydrophilic for cell uptake and payload encapsulation, and may cause unintended biologic

129 vectors of autonomous insertional sequences (payloads) encoding diverse functional modifications that

130 However, compared to (111)In-labeled payload EPI, (125)I-labeled EPI showed lower radioactivi

131 To determine the payload for ADCs against liver cancer, we screened three

132 ic acid component acts as both a therapeutic payload for intracellular gene regulation and the delive

133 ed into a nanostructure carrying a high drug payload for specific drug delivery.

134 prolonging the release of nucleic acid drug payload for sustained, long-term gene expression or sile

135 nes both biological barriers and nanocarrier payloads for a variety of drug delivery applications.

136 of PBDs, and the strategies for their use as payloads for ADCs.

137 ted picomolar potencies that qualify them as payloads for antibody drug conjugates (ADCs), while a nu

138 ogues of these natural products as potential payloads for antibody-drug conjugates and other delivery

139 overed in this study are highly desirable as payloads for antibody-drug conjugates and other drug del

140 for image-guided delivery of the therapeutic payloads for precise cancer treatment.

141 r, they can be loaded with diverse molecular payloads for targeted delivery.

142 s and others like them may serve as powerful payloads for the development of antibody drug conjugates

143 ined release of an active therapeutic agent (payload) for targeted delivery to specific sites of acti

144 Accumulation of released payload from 033-F was reduced in higher volume spheroid

145 activation to release a fluorogenic coumarin payload from a polymer incorporating a chain-centered me

146 We found that an enzymatic release of payload from ADC-depleted human plasma at 144 h was able

147 icles owing to their ability to shield their payload from chemical and enzymatic degradations as well

148 to either form stable conjugates or release payloads from 3-isocyanopropyl groups.

149 -triggered drug release while preventing the payloads from lysosomal degradation.

150 the site of injection, protection of antigen payloads from proteolytic degradation and reduction of a

151 confocal microscopy showed a dissociation of payloads from the early endosome indicating translocatio

152 gnificant vehicle from which DNA-damaging Pt payload gradually releases to neighbouring tumour cells.

153 y-drug conjugates (ADCs) containing multiple payloads has been developed.

154 itation and allows the plates to carry small payloads heavier than the plates themselves.

155 When loaded with a chemotherapeutic payload (i.e., doxorubicin), these cellular vectors (CEL

156 asma stability coupled with rapid release of payload in a lysosomal environment.

157 stribution and safety of a given therapeutic payload in circulation.

158 Nucleic acids are generally regarded as the payload in gene therapy, often requiring a carrier for i

159 oth hemiasterlin and taltobulin as cytotoxic payloads in antibody-drug conjugates (ADCs).

160 s the way toward controlled delivery of drug payloads in confined, hard-to-reach locations, with pote

161 hemiasterlin and its analogues as potential payloads in targeted therapeutics.

162 y systems to selectively release therapeutic payloads in vivo(7-11).

163 nt-feature-targeted delivery of 13 molecular payloads (including opsins, indicators, and fluorophores

164 obust intracellular delivery of a variety of payloads, including hydrophilic small molecule drugs (e.

165 rrolobenzodiazepine dimer (PBD) or tubulysin payloads induce ICD, modulate the immune microenvironmen

166 ker and conjugation chemistry, and cytotoxic payload) influence its activity.

167 to therapeutic targets in vivo is limited by payload integrity, cell targeting, efficient cell uptake

168 cluster delivery, release of the nanocluster payload into brain tissue can be triggered by a second f

169 l buffers and only release their therapeutic payload into cancer cells after a time-dependent cellula

170 eloped high-efficiency delivery of molecular payloads into chytrid zoospores using electroporation.

171 rgeting and infiltration of immunomodulatory payloads into tissues and cells, ii) microscale material

172 of processing PCMs, and their mixtures with payloads, into stable suspensions of colloidal particles

173 y an integrin-mediated process, releases its payload intracellularly, and is a highly potent inhibito

174 s that a modular and coherent photonic-aided payload is feasible, making way to an extensive introduc

175 g conjugate (ADC) biotherapeutics, where the payload is linked to the antibody by a thioether bond.

176 F) while maintaining the activity of protein payloads is reported.

177 safe and local delivery of immunotherapeutic payloads leading to systemic antitumor immunity.

178 R2-targeting ligands, conjugation sites, and payloads led to the discovery of 22 (PEN-221), a conjuga

179 The location/site of conjugation of payload-linker can have an effect on ADC stability and h

180 , HC-Fab, and HC-Fc) with various classes of payload-linkers.

181 An analysis of Antibody-Drug Conjugate Payload manufacturing has revealed that the majority of

182 h sperm during epididymal transit) carry RNA payloads matching those of mature sperm and can deliver

183 can undergo in vivo biotransformation (e.g., payload metabolism, deconjugation) leading to reduced or

184 In contrast, a less membrane permeable payload, MMAF, failed to mediate bystander killing in vi

185 nes allowing for facile functionalization of payload molecules.

186 line L-82, but delivered the same cytotoxic payload (monomethyl auristatin E, MMAE), and we found th

187 Animals immunized with a high-payload monovalent FMD vaccine developed high titers of

188 t delivery kinetics as measured by different payloads: nanoparticle encapsulated DiR was observed to

189 noparticle (SLN), capable of delivering high payload of 5-FU to treat CRC.

190 eport on characterization of modification to payload of ADC following desulfuration.

191 ful in characterization of metabolism on the payload of ADC to provide guidance for improvement of it

192 s concomitant with controlled release of the payload of anti-inflammatory drug.

193 for the conjugation of any alkyne-containing payload of choice.

194 In mission #2, a payload of ice, saline, and blood tubes (3.8 kg, 8.4 lbs

195 breviated as P-SMART), with 14.3+/-2.8% drug payload of SMART-OH.

196 This polarity switch is used to release payload of the polymersomes on demand, and to activate b

197 ression of TBC1D3 in macrophages altered the payload of their released EVs, including RNA-binding pro

198 These NCP particles contain high payloads of chemotherapeutics cisplatin or cisplatin plu

199 cteristics for this application such as high payloads of contrast generating material, strong X-ray a

200 it is demonstrated that the DNF can deliver payloads of cytotoxic protein (i.e., RNase A) to the cel

201 NMR spectrometer for efficient production of payloads of hyperpolarized contrast agent and in situ qu

202 atography mass spectrometry has been used as payload on such space exploration missions.

203 We show that these payloads on their own induced an immune response that pr

204 livery platform that releases its antibiotic payload only at the site of infection and only in the pr

205 xygen gas and that they release their oxygen payload only when exposed to desaturated blood.

206 roduction of oligoglycine-modified cytotoxic payloads or NIR fluorophores.

207 , which incorporate new types of linkers and payloads other than maytansines and auristatins, are mor

208 r the preprogrammed burst release of vaccine payloads over a period of a few days to more than a mont

209 , we saw a small amount of leakage (1.75% of payload) over the course of 1000 h of simulated implanta

210 They have been conjugated to toxic payloads, PEGs, or radioisotopes to increase and optimiz

211 that 173 +/- 38 polymersomes released their payload per cell, with significant heterogeneity in upta

212 ortunity to image the dispersion of the drug payload post release.

213 requires a new generation of communications payloads powered by large-scale processors, enabling a d

214 utilizes lung ECs as a source of therapeutic payload production and a highly desirable toxicity profi

215 able targeting and incorporate a therapeutic payload, provides a new and innovative therapeutic platf

216 wder enhance lung retention of their protein payload, relative to protein alone and non-targeted coun

217 of a bimetallic microcapsule with controlled payload release and precise modulation of translational

218 eneous delivery after 1 day, degradation and payload release by 2 days, and in vitro cell killing and

219 nd cyclization, we found the initial rate of payload release from this newly derived scaffold to be d

220 ex functions such as signaling or controlled payload release in response to external stimuli includin

221 emulsion-solid interface offers a triggered payload release mechanism.

222 s study, we investigated the degree to which payload release predicts ADC activity in vitro and in vi

223 eloped cPPA programmable microcapsules whose payload release rates depend on the composition and conc

224 Mass spectrometry studies of payload release suggested that other cysteine cathepsins

225 Controllable payload release through judicious design of the linker h

226 t also controls the endolysosomal escape and payloads release through photothermal conversion under l

227 local diffusion and distribution of released payloads represents a potential mechanism of ADC-mediate

228 LMNs) rupture and release their liquid metal payload, resulting in a rapid 10(8) -fold increase in th

229 The shortened PBD monomers provide a new ADC payload scaffold because of their potent cytotoxicity an

230 For payload selection, we biotinylated toxins and conjugated

231 ous because it allows for the development of payloads separately from the binding/translocation compo

232 ecause of the vital importance of minimising payload (size and mass).

233 argeted antibody conjugated to the cytotoxic payload SN-38.

234 stablished drug delivery system that enables payload stability and enhanced cellular activity upon in

235 zation-degradation pathway to deliver active payloads, strategies aimed at restoring lysosomal functi

236 geted delivery of diagnostic and therapeutic payloads such as radionuclides and drugs into neoplastic

237 and local delivery of non-native therapeutic payloads, such as antibodies, in response to antigen.

238 nal carriers designed for different types of payloads, surveying the biomaterials used to construct t

239 he non-covalent binding of the antibody to a payload that we designed to act as an affinity ligand fo

240 e find that CDI nuclease domains are modular payloads that can be redirected through different import

241 o allow for convenient attachment of various payloads that can be targeted directly to the tumor.

242 main peptides (MDP) can be tailored to carry payloads that modulate the extracellular environment.

243 device strategies load CGM sensors with drug payloads that release locally to tissue sites to mitigat

244 Using a common payload, the assembly of these linker-drugs utilized dif

245 od circulation between polymeric carrier and payload; the carriers ((111)In-2P and (125)I-2P) showed

246 gene target and a drug target using only the payloads themselves, bypassing the need for a cocarrier

247 Conjugation of shishijimicin A enediyne payloads through their phenolic moiety represents a nove

248 The cross-linkages can lock the payloads tightly, endowing the crosslinked Rososome with

249 amino acids were found to localize a peptide payload to a bone fracture 91.9 times more than the cont

250 Based on these observations, we altered the payload to a pyrrolo[2,1-c][1,4]benzodiazepine dimer (PB

251 binding to the receptor and linking a toxic payload to an SSTR2 agonist is a potential method to kil

252 ii) a novel tandem peptide cargo to localize payload to bacterial membranes.

253 r mimic extracellular matrix or to deliver a payload to diseased tissue.

254 ug development are made by coupling a linker-payload to native or engineered cysteine residues on the

255 lities of an antibody to deliver a cytotoxic payload to specific cell types.

256 ther linker was optimized for release of the payload to take advantage of the high resolution and hig

257 fective and specific delivery of therapeutic payload to TAMCs.

258 f the linkage strategy adopted to attach the payload to the antibody.

259 nly delivers a cytotoxic or an immunotherapy payload to the tumor but also reports back on the effica

260 ith direct paracrine delivery of a bioactive payload to transplanted ovarian tissue.

261 urally varied linkers that attached the drug payloads to a beta-cyclodextrin-PEG copolymer to form se

262 gy for the conjugation of alcohol-containing payloads to antibodies has been developed and involves t

263 sed for coupling maleimide-containing linker-payloads to antibodies resulting in the generation of an

264 rrolobenzodiazepine dimer were chosen as the payloads to construct two GPC3-specific ADCs: hYP7-DC an

265 the selective pharmacodelivery of cytotoxic payloads to diseased tissues, providing an innovative pl

266 able of localizing small amounts of peptidic payloads to fracture surfaces 2-fold over healthy bone,

267 s that can recognize and deliver therapeutic payloads to macrophages in a tumor-specific manner.

268 treatments require sustained release of drug payloads to maintain the effective therapeutic level.

269 in was used to deliver fluorescently labeled payloads to Neuro-2a cells.

270 ugation method to enable precise addition of payloads to proteins, synthesis of antibody-drug conjuga

271 ry of nanoscale carriers containing packaged payloads to the central nervous system has potential use

272 cific cell types, delivering their enzymatic payloads to the cytosol.

273 s, and targeting polymers/nanoparticles with payloads to the mitochondria.

274 highly potent killing activity of drugs with payloads too toxic for systemic administration.

275 ery of versatile NCs indicated the effective payloads towards the target site, increased apoptosis in

276 tatively characterizing the extent of linker-payload transfer to serum albumin and the first clear ex

277 can rapidly and effectively release its DOX payload triggered by an acidic pH environment (pH~5) and

278 ds to autonomous release of the encapsulated payload upon gastric-acid neutralization by the motors.

279 via the antibody and release their cytotoxic payload upon internalization.

280 encapsulate and deliver various hydrophilic payloads using a pH-responsive silica-metal-organic fram

281 y tethered to a cytotoxic drug (known as the payload) via a chemical linker.

282 The highest payload was 0.56(+/-0.01) mumol SNAP/mg microspheres.

283 For mission #1, no payload was carried.

284 The payload was conjugated to trastuzumab by a protease-clea

285 The payload was designed to operate in microgravity and to w

286 Sustained release of the pGFP payload was shown over a period of 8 days.

287 jugated via hinge-cysteines to an auristatin payload was used as a model in this study to understand

288 t brain delivery for multiple small molecule payloads, we observed minimal evidence for targeting to

289 ct resonance frequencies and a high fluorine payload were characterized in terms of size, stability,

290 m silicate shell traps and protects an siRNA payload, which can be delivered to neuronal tissues in v

291 eared, the erythrocyte surface-bound antigen payload will be cleared tolerogenically along with the e

292 The hydrogels released 50% of their payload within 30min and enhanced the accumulation of GA

293 subsequent entrapment and degradation of the payload within acidic/digestive lysosomal compartments.

294 nanocarriers released ~75% of the paclitaxel payload within six hours in acidic pH, which was accompa

295 ase in the deposition of a model therapeutic payload within the phantom was achieved using the MAD co

296 cells for several days and release their RA payloads within a few minutes upon exposure to blue/UV l

297 self-immolative unit for alcohol-containing payloads within ADCs, a class that has not been widely e

298 lize gastric acid and simultaneously release payload without causing noticeable acute toxicity or aff

299 eptor-mediated cytosol delivery of the siRNA payload without endosome trapping, as attested by fluore

300 roles in imaging by delivering large imaging payloads, yielding improved sensitivity, multiplexing ca