ライフサイエンスコーパス: analyte

1 dy to ERBB2 quantitatively detects the bound analyte.

2 , specifically biological sex, from a single analyte.

3 pecificity, and selectivity against a target analyte.

4 NE was the most elevated analyte.

5 selectively capture the procalcitonin target analyte.

6 ards online monitoring and remote sensing of analyte.

7 2 protein (HER2) cancer biomarker as a model analyte.

8 lements which emit photons in response to an analyte.

9 r attribute can be correlated to a different analyte.

10 ed biosensors after addition of an exogenous analyte.

11 its in solution by proximity placement to an analyte.

12 ing can remove a significant fraction of the analyte.

13 ricated TLR sensor surfaces against the same analyte.

14 in the range of 90-121were obtained for the analytes.

15 the presence of competing and non-competing analytes.

16 eir application for determination of protein analytes.

17 andards to aid the identification of unknown analytes.

18 c acid prevents significant oxidation of the analytes.

19 ilms to strong electron-donor chemical vapor analytes.

20 80, and poly(methyl methacrylate) (PMMA) as analytes.

21 el, which uses physicochemical parameters of analytes.

22 ces that can be applied to a wide variety of analytes.

23 lation coefficients, r(2)>0.9990 for all the analytes.

24 nd the identification of complex mixtures of analytes.

25 er (2)H or (13)C) within a specified list of analytes.

26 sitive and quantitative detection of protein analytes.

27 w-intensity m/z signals corresponding to the analytes.

28 t was found to be greater than 0.99 for both analytes.

29 reparation was optimized for the recovery of analytes.

30 vices are capable of capturing and filtering analytes.

31 Omega relative to the average Omega for the analytes.

32 nt pathways contributing to the same pool of analytes.

33 t nanoparticles to visualize the presence of analytes.

34 ping approach to achieve separation of these analytes.

35 desserts that may endogenously contain these analytes.

36 unt the effects of the density and charge of analytes.

37 been developed for the analysis of multiple analytes.

38 be further extended to other macromolecular analytes.

39 e electrode sensing current toward different analytes.

40 olling elution order/time of polyprotic acid analytes.

41 e probes for detection of different chemical analytes.

42 t MOF-based chemiresistive sensors for these analytes.

43 ious surfaces toward the analysis of diverse analytes.

44 is based on standard additions for chemical analytes.

45 cific detection of a wide range of different analytes.

46 o statistically discriminate between the two analytes.

47 antitative discrimination of closely eluting analytes.

48 ation of phenols from smoked food sample and analytes absorption into a NaOH solution in a specially

49 ultaneous quantification of glucose and urea analytes along with malaria parasitemia quantification u

50 t extraction procedures regarding the target analyte and food matrix components.

51 omeric conformers able to recognize a chiral analyte and greatly amplify its chiroptical readout.

52 ning micromolar concentrations of the target analytes and 150 mM of NaCl.

53 60muL of CCl4 as extraction solvent for both analytes and 500muL of 1.5% DDTC solution.

54 VHHs are not particularly apt to bind small analytes and failures are not uncommon.

55 ver, the extension of DGT to a wide range of analytes and its use under varied conditions has shown t

56 In studies of urinary analytes and obesity or obesity-related outcomes, contro

57 nd relative migration times of the extracted analytes and related standards allowed identification of

58 ration range of 10-200micromolL(-1) for both analytes and the detection limits were determined as low

59 ow choice of materials must be suited to the analyte, and how innovations in fabrication and sensing

60 the recovery, which was quantitative for the analyte, and the reproducibility (RSD%), checked on diff

61 munosensor and the subsequent binding of the analyte antibody anti-cholera toxin were investigated wi

62 Although these analytes are amenable to LC and LC-MS detection an addit

63 Charged analytes are concentrated near the IDZ when their electr

64 effect transistor sensors for some important analytes are elaborated.

65 Permeating analytes are entrained to an atmospheric pressure ioniza

66 oupling these two functionalities, separated analyte bands eluting from the HPLC column are fractiona

67 es that ranged between 0.3 and 1.8 for these analytes because of the limitations of using TWA concent

68 the method is effective for determination of analytes beta-sitosterol and stigmasterol.

69 pillar surfaces, as well as assessing ligand-analyte binding interactions between anti-human immunogl

70 unequivocal identification of the unmodified analyte by Liquid Chromatography-Mass Spectrometry.

71 ix effects (MEs) on the quantification of an analyte can be significant and should not be neglected d

72 nstrate that single droplets with <100 pg of analyte can easily be studied using single droplet mass

73 optimal conditions for the separation of new analytes can be accelerated by the use of appropriate th

74 main oven temperature, the retention of all analytes can be reduced so that they elute within their

75 In the case that the analyte cannot be detected within its clinical range wit

76 ility and quality, identification of unknown analytes, capture of nonpersistent chemicals, integratio

77 Separations for key analyte classes and their dependences on electric field

78 ls employing an integrated workflow for dual-analyte co-detection.

79 Connectivity within analyte communities enabled the identification of known

80 is of whole blood gene expression and plasma analytes, comparing South Indian TB patients with and wi

81 stics of a paper-based analytical device for analyte concentration enrichment.

82 The anodic current increases with rising analyte concentration in a range from 5microM to 10mM, a

83 nder optimal conditions was observed for the analyte concentration in the range 1.47-247.20ngmL(-1),

84 If the estimated total analyte concentration is correct, a portion of the sigmo

85 volume, complex nature of the sample and low analyte concentration necessitates signal enhancement us

86 f colour change that was proportional to the analyte concentration with a detection limit of 0.2ppb.

87 regime generate the current proportional to analyte concentration.

88 position and readily correlated to the total analyte concentration.

89 f a biological test sample spiked with known analyte concentrations and the log transformed estimated

90 ted reagent amount truncates peaks from high analyte concentrations but does not hamper WBQ at a low

91 , compared with GP controls, by quartiles of analyte concentrations in primary analyses.

92 Analyte concentrations were compared with baseline (day

93 Unknown endogenous analyte concentrations within even 2-fold diluted human

94 more drugs, particularly in samples with low analyte concentrations, with values of 88% after UglucP

95 interactions directly in liquid at very low analyte concentrations.

96 ssfully applied to food samples to determine analyte concentrations.

97 relies on precise knowledge of the probe and analyte concentrations.

98 figured out between the peak current and the analytes' concentrations on a range of 0.01-30.0muM and

99 reased with increasing concentration of both analytes, confirming the aggregation of Tyr-Au NPs induc

100 We propose the application of a global analyte constraint to prevent the accumulation of false

101 address this limitation, we applied Weighted Analyte Correlation Network Analysis (WACNA) to RNA-seq

102 ements of cellular metabolites and increased analyte coverage, but has lower throughput because the e

103 plex allergy diagnostics using the alpha-Gal analytes CTX and Bos d TG confirms the history of MA pat

104 ection, and offer high selectivity for trace analyte detection in biological fluids.

105 ely 10(10) and sub-zeptomole (<10(-21) mole) analyte detection were accomplished by coating the DFH-4

106 rs of concentration magnitude improvement in analyte detection, which is expected in stacking with hy

107 es direct read-out of the current related to analyte detection.

108 ectively, which are strong enough for single analyte detection.

109 the %RSD values were lower than 10% for all analytes determined.

110 ue that resolves resonances according to the analytes' diffusion coefficients.

111 Second, increased analyte diffusivity due to autothermal runaway Joule hea

112 the solid-state sensor elements and gaseous analytes, distinct color difference patterns were produc

113 A good correlation between the analytes' distribution and mu-EME electric currents was

114 s of pollutants and other treating compounds/analytes (drugs) protecting citizens' life.

115 demonstrated in this work that dispersion of analytes during electrokinetic migration is also the res

116 f the PDMS outer layer on the uptake rate of analytes during the mass transfer process.

117 electrophoresis based on the reversal of the analytes' effective electrophoretic velocities at a dyna

118 tion is undesirable for the analysis of some analytes either due to extraction or chemical modificati

119 t flow chromatography for sample cleanup and analyte enrichment (online-SPE-LC-MS/MS).

120 collected and analyzed for NE using a single-analyte enzyme-linked immunosorbent assay (ELISA).

121 he broad coverage of the coating in terms of analytes extracted and its suitability for both thermal-

122 tion of the address-directed flux of a redox analyte, ferrocenedimethanol (FDM).

123 y and are water-soluble, and their (19)F-NMR analyte fingerprint is pH-robust, thereby making them pa

124 n disparate and predictable surface-directed analyte flux to an array of sensing addresses and a meas

125 ered saline (PBS) may provide an alternative analyte for lower-cost quantitative HIV virus load (VL)

126 ine was densely interconnected with clinical analytes for cardiometabolic disease).

127 (oxygen-, nitrogen-, and sulfur-containing) analytes found in low-concentrations were analyzed by Fo

128 in-line phase-transfer assay, extracting the analyte from aqueous sample droplets into the organic ph

129 The D4 assay can interrogate multiple analytes from a drop of blood, is compatible with a smar

130 tive segregation of ionic and/or hydrophilic analytes from background biofluid electrolytes for quant

131 nsing steps are not required to separate the analytes from the bioelectrolytes.

132 vides sufficient sensitivity to measure many analytes from volume-limited samples, each type of mass

133 dentification of biomarkers was possible for analytes >15 ng/mL.

134 or commonly encountered biological media and analytes hampers optimisation of biosensor performance f

135 f cadmium, copper, lead, and silver as model analytes has been demonstrated by microextraction as die

136 re-forming proteins to interact with various analytes has found vast applicability in single molecule

137 cular nanoparticle hybrids for biosensing of analytes have been a major focus due to their tunable op

138 While a number of assays for soluble analytes have been developed using paper-based microflui

139 ly in ensuring target disease specific small analytes (i.e. metabolites, proteins, etc.) stability in

140 ion strategy for untargeted and low abundant analyte identification directly from tissue sections.

141 vent incidence, changes in safety laboratory analytes (ie, serum chemistry and haematology), and part

142 and flicker), (ii) emission spectrum of the analyte, (iii) emission spectrum of the optical backgrou

143 anoporous gold coating enables capturing the analyte in pico- to nano-molar ranges.

144 emented to improve the detection of specific analyte in systems where more than one analyte is presen

145 asurements of up to 168 distinct hydrocarbon analytes in 2,980 sediment samples collected within 4 y

146 ific method to quantify trace amounts of DNA analytes in a wash-free suspension assay.

147 efore the determination of BCA and gammaGBCA analytes in accurate and reliable manner has high import

148 owered pre-concentrators and autosamplers of analytes in ambient groundwater and as infrared communic

149 ticles (FONs) for determination of important analytes in aqueous medium.

150 ystem that allows for the assay of different analytes in complex samples.

151 have the potential to define distribution of analytes in different parts of the cell.

152 ptical and mass biosensors to detect various analytes in food.

153 to the concentration and separation of trace analytes in liquid-liquid microextraction.

154 werful tools for quantifying and visualizing analytes in living cells, and when targeted to organelle

155 The method for the determination of 85 analytes in lyophilized egg albumen was developed and su

156 vent moves through the probe, drawing in the analytes in preparation for ionization using an electros

157 The real-time monitoring of specific analytes in situ in the living body would greatly advanc

158 d to the surrounding medium (e.g., to detect analytes in solution).

159 traints for modeling the structures of those analytes in solution.

160 ficulty to specifically and precisely detect analytes in the biological sample.

161 For 28 of 30 analytes in the study method limit of quantification val

162 itability of using CFI-MS in the analysis of analytes in vapor, liquid, and solid phases using a sing

163 tivity, along with a broad suite of chemical analytes, in streamwater from 35 well-characterized site

164 vantages were realized for some low polarity analytes including both estradiol and estrone.

165 The evaluation was carried out using 86 analytes, including 22 phenolic compounds (phenolic acid

166 rting of 1.0, 10.2, 19.5, and 48.5 kbp dsDNA analytes, including both plasmid and genomic DNA.

167 , we identified untargeted and low-abundance analytes, including neuropeptides deriving from the pro-

168 The hyPAD is able to concentrate a range of analytes, including small molecules, DNA, proteins, and

169 Specific binding events of target analyte induced collision frequency changes enabling ult

170 erformance by providing more active area for analyte interaction, thereby allowing more rapid interfa

171 tive sensing methods, characterized by light-analyte interactions, are explained explicitly.

172 opy to demonstrate stability in detection of analytes, Interleukin-6 (IL-6) and Cortisol, from human

173 he tool also allows for testing of different analytes/internal standard combinations, which helps wit

174 ice to separate a wide range of nucleic acid analytes into distinct microchannel outlets.

175 t a given amount of RNA molecules (i.e., the analyte) into an amplified amount of signaling molecules

176 We recorded analyte ion and total ion counts as a function of wavele

177 of >300 that is sufficient to differentiate analyte ions with CCS differences as small as 0.5%.

178 Four additional analytes (IP-10, IL-12/23p40, IFNy, IL-15) were found to

179 cific analyte in systems where more than one analyte is present.

180 Once the sample is added in the strip, the analyte is selectively captured by antibody-decorated si

181 A solution containing the analyte is sprayed uniformly through picoliter droplets

182 nonpolar as well as medium and high polarity analytes is also demonstrated.

183 One-fourth of the 40 target analytes is investigated for the first time in this biol

184 ents that can bind simultaneously to a given analyte, is the gold standard in diagnostics and many bi

185 lizes on a stable composition of the infused analyte leading to consistent time-independent detection

186 mical signals produced by the interaction of analyte-ligands could be applicable for a wide range of

187 d GR-active compounds on the target-chemical analyte list were detected.

188 he combination of rotating parts and gaseous analytes makes the design of RDE cells that allow for he

189 ng primary ion beam-induced fragmentation of analytes, ME-SIMS has proven useful for detection of num

190 t participants and 11 hormone and nonhormone analytes measured by 37 immunoassays, ingesting 10 mg/d

191 nt concentrations of chloramphenicol through analyte-mediated inner filtering of sub-330 nm excitatio

192 ffects of the matrix for single and multiple analytes methods.

193 ctroscopy and mass spectrometry, suggest the analyte molecules to be formed in the cold plasma vicini

194 om frustules is capable of concentrating the analyte molecules, which offers a simple yet effective m

195 rces of resonances in a mixture of different analytes, nor can they separate inhomogeneous and homoge

196 l features showed that the excitation of the analyte occurred in the region near the collection elect

197 es and thus a high sorption capacity for the analyte of interest.

198 S) approach can be implemented to detect the analyte of interest.

199 say in the quantitative determination of the analyte of interest.

200 PENK is a stable surrogate analyte of labile enkephalins that is correlated inverse

201 to non-invasively detect a large variety of analytes of clinical interest.

202 strate the success of this approach with two analytes of diagnostic importance, i.e., influenza viral

203 he availability of capture molecules to bind analytes of interest to the sensor surface.

204 were developed and validated to quantify the analytes of interest.

205 re biomimetics which can selectively bind to analytes of interest.

206 the effect of interfering compounds from the analytes of interest.

207 e the sensitivity (ion counts per ppt of the analytes) of the HRToF-CIMS to the acids.

208 lization of light-switchable sensors for the analyte or biosensors by combination with NADH producing

209 nsors necessitates stability in detection of analytes over prolonged and continuous exposure to sweat

210 ection of M. genitalium Expansion of the STI analyte panel (including M. genitalium) and additional s

211 tructures for the defined conversion of this analyte paving the way for the realization of light-swit

212 meter-scale spatial distribution of specific analytes (potassium, calcium, manganese, iron, and zinc)

213 The achieved online analyte preconcentration led to a 480-fold enhancement o

214 d efficient thermal desorption/ionization of analytes previously concentrated on the coating, and dra

215 pg, negligible with regard to the amounts of analytes processed.

216 m/z, retention time and CCS values for each analyte; processing and analyzing data using dedicated s

217 atures of individual chemical components for analyte-profile determination.

218 patterns with different alpha-Gal-containing analytes provides the basis for an individual allergy di

219 re and software, called bioluminescent-based analyte quantitation by smartphone (BAQS), provides an o

220 n this paper, we describe a novel method for analyte quantitation that does not rely on calibrants, i

221 provide rejection of interferences and multi-analyte quantitation.

222 Detection levels for all the five analytes ranged from 0.0007 to 0.002mugg(-1) and quantif

223 used for nucleic acid sensing extending the analyte recognition beyond a 5-mer.

224 e and reduced graphene oxide, and a reliable analyte recognition.

225 ry leaving the binding sites free for target analyte recognition.

226 d limits of detection (0.549-0.673ppb), good analyte recoveries (100.8-105.99%) and good reproducibil

227 ion with a C18 sorbent was proposed (average analyte recoveries were between 94 and 104%).

228 quantitative detection without the need for analyte reference standards would offer substantial bene

229 After MALDI MS analysis, a majority of the analyte remains for follow-up measurements to extend the

230 When the analyte response across the measurement range is not str

231 een LC and MS were considered to enhance the analyte response and reduce band broadening and/or solut

232 onsistency and minimized calibration burden; analyte response curves were shown to be highly repeatab

233 a systematic investigation of heat transfer, analyte retention, and migration velocity at a range of

234 thick, depending on the tissue type and the analyte(s) of interest.

235 logy is desirable to increase the breadth of analyte(s), maintain the topographies of the brain, and

236 d the maximum observed charge state for each analyte scales with mass in agreement with an analytical

237 tionship between NIMS surface morphology and analyte selectivity.

238 quiring overall 45min to be completed before analyte sensing.

239 for the development of ultrasensitive toxic analyte sensor platforms.

240 spatially characterizing very low abundance analytes separated only by 20 mDa.

241 tory extraction efficiencies for the studied analytes, several parameters affecting the SALLE procedu

242 Laboratory studies on target analytes showed that the ionization conditions in the PT

243 hat were used to build highly accurate multi-analyte signatures for patient classification.

244 OIS) at a concentration close to that of the analyte significantly improved the quantitative analysis

245 of detection down to 1 pM, regardless of the analyte size.

246 Similar to SAI, the analyte solution is directly introduced into a heated in

247 eir operation to rapid timescales and dilute analyte solutions.

248 applicable to IC-based sensors that undergo analyte-specific gating.

249 By ELISA, two analytes (ST2 and Spondin-1) best described longitudinal

250 Among the different analytes studied using the sensor combining TMB, H2O2, a

251 s are approximately 3x faster for the larger analytes studied, and calibration sensitivity is improve

252 or this reason the determination of targeted analytes such as: Cd, Pb, As, Cu, Cr, Ni, Fe, Mn and Sn

253 the key in optical detection of low-abundant analytes, such as circulating RNA or DNA.

254 For analyte systems we investigated DNA oligomers (3-HPA), p

255 /445 and 101/76 for the cationic and anionic analytes tested, respectively.

256 is its applicability toward the detection of analytes that do not show UV absorption or are not ionis

257 y subject baselines and determine the set of analytes that exhibit biologically stable baselines afte

258 ltered by its embedding micro-environment or analyte, thereby leading to substantial changes in reado

259 is attributed to the facile diffusion of the analyte through the well-spread nanofeatured gold skin.

260 The binding of a target analyte to an ion channel (IC), which is readily detecte

261 e DRELFA is very effective in localizing the analyte to the test line (consistently over 90%) and thi

262 of sediment and porewater, and analyzed for analytes to identify unconventional O&G wastewater dispo

263 antum sensing, whereby porosity would enable analytes to infuse into a sensor matrix.

264 enin channels by chitosan addition prevented analyte translocation.

265 that have been employed to control fluid and analyte transport in paper-based assays.

266 Excellent results were obtained for all analytes under study; furthermore, the tests yielded sat

267 hing step to remove matrix interferents, the analyte was eluted in back-flush mode and the eluent fro

268 This analyte was quantified through a competitive detection p

269 ross-linker and the carboxylate group of the analyte was still operative upon real sample analysis.

270 A pool of 59 (bio)analytes was screened, containing monosaccharides, phosp

271 The calibrated range in cheese for all analytes was very broad, from 0 to 1000mgkg(-1), and in

272 nd multiple isotopes per charge state of the analyte were used during quantitation for optimized sens

273 These analytes were also detected and quantified in a house du

274 ngly affected sorption as negatively charged analytes were attracted by the positively charged surfac

275 Deuterium labelled analogues of the target analytes were either purchased commercially or synthesis

276 Analytes were extracted from 5mL wine sample (previously

277 The relative abundances of these analytes were found to be reproducible between mice.

278 Responsive groups for various analytes were introduced as a head-trigger during the po

279 Estrogen analytes were measured in serum or urine by liquid chrom

280 ously parallelize 48 samples in 1 h, and the analytes were measured using ultrahigh-performance super

281 The analytes were mostly detected as the deprotonated ion [M

282 ell pellets, and SOMAscan analysis of sputum analytes were performed.

283 Fifty analytes were spiked into a diesel fuel at two concentra

284 Target analytes were stable in wastewater at 4 and 20 degrees C

285 the present work, 79 structurally unrelated analytes were taken into account and their chromatograph

286 roup multiple features arising from the same analyte, which we call "degenerate features", using a co

287 nit for the detection of oxygen and catechol analytes, which are central to medical and environmental

288 ctively eliminate mu-EME transfers of target analytes, which are retained in the sample, and the resu

289 The ability to target a single analyte will transform forensic science as each originat

290 Only protonated analytes with a carboxylic acid, a sulfone, or a sulfona

291 zation method to analyze mixtures containing analytes with different polarities and volatilities in d

292 d minimal sample preparation and resulted in analytes with excellent chromatographic and mass spectro

293 ich allows the simultaneous determination of analytes with extremely different properties.

294 The limits of detection for analytes with high polarities such as dodecyl trimethyla

295 ng, which enables detection of low-abundance analytes with poor precursor ion signal.

296 ety of small molecule messengers and protein analytes with standard instrumentation, thereby simplify

297 perimental design to aid in the discovery of analytes with statistically different variances between

298 ive the unknown endogenous concentrations of analyte within complex biological matrices (e.g. serum o

299 chemical SERS (EC-SERS) to detect IV therapy analytes within their clinically relevant ranges.

300 Both spectral (x-outlier) and analyte (y-outlier) outliers can be detected separately