ライフサイエンスコーパス: FET

1 FET devices constructed with the red phosphorus nanowire

2 In the highlight demonstration, the MoS(2) FET crossbar array optically images 1000 handwritten dig

3 ectrical characteristics of suspended MoS(2) FET, gating potential was applied through an electrolyte

4 challenges and future perspectives of 1D/2D-FET biosensors are covered.

5 In addition, the progress in the 1D/2D-FET biosensors in North America, in the last decade, is

6 her (two orders of magnitude) than that of a FET based on an unsuspended CNT and about 50% sensing su

7 In this report, a FET transducer is compared with the recently proposed bi

8 be a superior transducer in comparison to a FET in an electrochemical sensor.

9 Unlike a FET sensor, the calibration curve of the BJT sensor is i

10 o replace and/or coexist with Si-based aging FET technologies.

11 chieve hysteresis-free subthermionic SS, and FETs that can operate in the quantum-capacitance limit a

12 s introduced, and different state-of-the-art FET sensor structures are reviewed.

13 ON current compared to any state of the art FETs.

14 aracteristics of back-gated Schottky barrier FETs (SB-FETs) from 2D channel materials.

15 tability, and sensitivity, the aptamer-based FET biosensor has potential as a point-of-care diagnosis

16 The signal of the aptamer-based FET biosensor increased linearly with the increase in th

17 evolving field of 1D and 2D materials-based FET biosensors, with an emphasis on structure and electr

18 toward the application of nanomaterial-based FET sensors for biochemical sensing in physiological env

19 y applicable to nanotube- and nanowire-based FETs, oxide semiconductors, and organic-material-based t

20 we review the state-of-the-art of TMD-based FETs and summarize the current understanding of interfac

21 temperature in the MoS2 negative-capacitance FETs as the result of negative capacitance due to the ne

22 terointerface of the WSe2 /MoS2 dual-channel FET.

23 se a biased conducting AFM tip to gate a CNT-FET at the nanoscale and demonstrate that the strongest

24 t the critical role of metallic tubes in CNT-FET biosensor devices and demonstrate that network compo

25 stem, with sensors based on spray-coated CNT-FETs.

26 arbon nanotube field-effect transistors (CNT-FETs) are a simple and cost-effective alternative for co

27 arbon nanotube field-effect transistors (CNT-FETs) have benefitted from improved separation technique

28 We show that concomitant FET sensitivity and single-mismatch selectivity can be a

29 Here, perovskite single-crystal FETs based on methylammonium lead bromide are studied an

30 les fabrication of perovskite single-crystal FETs with high mobility of up to ~15 cm(2) V(-1) s(-1) a

31 lications of electric double layer FETs (EDL-FETs), a triboiontronic transistor is proposed to bridge

32 namic concentration ranges of the QCR and EG-FET chemosensors were 0.15 mM and 0.15 to 1.25 mM as wel

33 With the QCR and EG-FET chemosensors, the d-arabitol concentration was deter

34 neously serves as a gate electrode of the EG-FET and as the SPR active interface.

35 The EG-FET gate surface was coated with the PQQPFPQQ-templated

36 he extended-gate field-effect transistor (EG-FET) chemosensor.

37 lectrolyte gated field-effect transistor (EG-FET) methods in a single analytical device we introduce

38 ve extended-gate field-effect transistor (EG-FET) transducer leads to highly selective HSA determinat

39 or extended-gate field-effect transistor (EG-FET) transducers integrated with molecularly imprinted p

40 An extended-gate field-effect transistor (EG-FET) was used as the transduction unit.

41 Here we propose an electrostrictive FET device, involving the epitaxial oxide heterostructur

42 ver, existing proposals for electrostrictive FET applications typically adopt approaches that are ent

43 bsolute uptake in tumor was higher for (18)F-FET (3.5 +/- 0.8 percentage injected dose [%ID]/g) than

44 Ds [%]), with regards to AC-CTref: for (18)F-FET (A)-SUVs as well as volumes of interest (VOIs) defin

45 ce for other tracers is limited; thus, (18)F-FET and (11)C-MET are preferred when available.

46 Conclusion: (18)F-FET and (11)C-MET, both amino-acid tracers, showed a com

47 y induce significant treatment-related (18)F-FET and (3)H-MET uptake near the resection cavity in the

48 vivo dual-tracer autoradiography using (18)F-FET and (3)H-MET.

49 ake with a mean L/B of 2.0 +/- 0.3 for (18)F-FET and a mean L/B of 1.7 +/- 0.2 for (3)H-MET was noted

50 y the perfusion and internalization of (18)F-FET by cells in various tissues of the rat, whereas grap

51 termine which are more appropriate for (18)F-FET in rats.

52 We obtained (18)F-FET metabolic tumor volumes (MTVs) as well as mean and m

53 e model allowed adequate decoupling of (18)F-FET perfusion and internalization by cells in the differ

54 E105 (10.6 +/- 2.3, P < 0.01) than for (18)F-FET PET (1.8 +/- 0.3).

55 32 BMs) treated with ICI or TT who had (18)F-FET PET (n = 60 scans) for treatment monitoring from 201

56 23 d; range, 6-44 d) and postoperative (18)F-FET PET (time after surgery: median, 14 d; range, 5-28 d

57 (18)F-FET PET analysis comprised maximal tumor-to-background r

58 sion represents a potential pitfall of (18)F-FET PET and may mimic brain tumor.

59 The predictive value of changes of (18)F-FET PET and MRI parameters on survival was evaluated sub

60 n the corresponding centers of mass in (18)F-FET PET and MRS imaging of Cho/NAA, determined by simult

61 etabolism during epileptic seizures by (18)F-FET PET and to elucidate the pathophysiologic background

62 e study and had 27 early postoperative (18)F-FET PET exams performed preferentially in a hybrid PET/M

63 (18)F-FET PET findings were verified by neuropathology (40 pat

64 18)F-FET-negative glioma and available (18)F-FET PET follow-up.

65 Metabolic responders to ICI or TT on (18)F-FET PET had a significantly longer stable follow-up (thr

66 Whether seizures also affect (18)F-FET PET imaging is currently unknown.

67 ation grade II-IV glioma who underwent (18)F-FET PET imaging to distinguish between TP and TRCs.

68 MR and (18)F-FET PET imaging were performed at baseline and after the

69 dual tumor suggests that supplementary (18)F-FET PET is relevant in cases where reoperation for resid

70 Conclusion: (18)F-FET PET may add valuable information for treatment monit

71 (18)F-FET PET might provide additional information beyond the

72 e glioma, we investigated the value of (18)F-FET PET monitoring of primarily (18)F-FET-negative gliom

73 (18)F-FET PET monitoring with static and dynamic evaluation is

74 Conclusion: Changes of (18)F-FET PET parameters appear to be helpful for identifying

75 Threshold values of (18)F-FET PET parameters to predict outcome were established b

76 The diagnostic accuracy of (18)F-FET PET parameters was evaluated by receiver-operating-c

77 In all lesions, static and dynamic (18)F-FET PET parameters were obtained (i.e., mean tumor-to-br

78 Conclusion: Our study confirmed that (18)F-FET PET provides valuable information for assessing the

79 (18)F-FET PET results correlated with overall survival (P < 0.

80 stases without prior local therapy and (18)F-FET PET scanning were retrospectively identified in 2 ce

81 stases without prior local therapy and (18)F-FET PET scanning were retrospectively identified in 2 ce

82 11 of 27 cases (41%), results from the (18)F-FET PET scans added relevant clinical information, inclu

83 (18)F-FET PET scans and ex vivo autoradiography were performed

84 y, we evaluated pre- and postoperative (18)F-FET PET scans of glioma patients with particular emphasi

85 Results: Visual analysis of (18)F-FET PET scans revealed complete resection in 16 of 43 pa

86 progression in MRI when no concomitant (18)F-FET PET was available, but subsequent follow-up PET was

87 artment, the diagnostic performance of (18)F-FET PET was convincing but slightly inferior to that of

88 The prognostic value of (18)F-FET PET was estimated using the Kaplan-Meier method.

89 In 13 patients, (18)F-FET PET was performed for response assessment to ICI or

90 In 27 patients, (18)F-FET PET was used to differentiate treatment-related chan

91 tus epilepticus, who underwent MRI and (18)F-FET PET, were studied.

92 acteristic analysis yielded an optimal (18)F-FET TBR(max) cutoff of 1.95 (sensitivity, 70%; specifici

93 er uptake was significantly higher for (18)F-FET than for (3)H-MET (P < 0.001).

94 s, slope, and tumor-to-brain ratios of (18)F-FET uptake (18-61 min after injection) were evaluated us

95 Conclusion:(18)F-FET uptake and increased Cho/NAA ratio are not always co

96 The average tumor volumes for (18)F-FET uptake and increased Cho/NAA were 19 +/- 20 cm(3) (m

97 um tumor-to-brain ratios (TBR(max)) of (18)F-FET uptake and the slope of the time-activity curves (20

98 periments detected reactive changes in (18)F-FET uptake at the rim of the resection cavity within the

99 of 17 (94%) evaluable patients showed (18)F-FET uptake at the time of malignant transformation.

100 erved, with a considerable increase in (18)F-FET uptake compared with preoperative values in either t

101 Fourteen of 23 patients showed tumoral (18)F-FET uptake concurrent to and 4 of 23 before MRI-derived

102 (18)F-FET uptake corresponded to structural MRI changes, compa

103 of bevacizumab on BBB permeability and (18)F-FET uptake in a human xenograft model.

104 (18)F-FET uptake in reactive changes was frequent (52%), but c

105 low-up in 5 patients showed decreasing (18)F-FET uptake in the flare areas in 4 patients and progress

106 Time-activity curves of (18)F-FET uptake in those areas revealed constantly increasing

107 ery to examine time-activity curves of (18)F-FET uptake in treatment-related changes.

108 Hence, (18)F-FET uptake indicating malignant transformation might inf

109 In metastases > 1.0 cm, (18)F-FET uptake intensity was highly variable and independent

110 The maximum lesion-to-brain ratio for (18)F-FET uptake near the resection cavity was significantly h

111 BRmax) and dynamic analysis of tumoral (18)F-FET uptake over time (increasing vs. decreasing) includi

112 ino acid transport with a strict gyral (18)F-FET uptake pattern.

113 In 3 of 23 patients, no (18)F-FET uptake was detected at tumor progression.

114 Changes in (18)F-FET uptake were evaluated by tumor-to-brain ratios in re

115 s in tumor-to-brain ratios or slope of (18)F-FET uptake were observed in PET and autoradiography (P >

116 etastases predominantly show increased (18)F-FET uptake, and only a third of metastases < 1.0 cm were

117 etastases predominantly show increased (18)F-FET uptake, and only a third of metastases < 1.0 cm were

118 At first occurrence of tumoral (18)F-FET uptake, TBRmax was significantly higher in patients

119 1.0 cm diameter all showed pathologic (18)F-FET uptake, which did not correlate with lesion size.

120 reased seizure-associated strict gyral (18)F-FET uptake, which was reversible in follow-up studies or

121 e and widespread (>/= 1 lobe) cortical (18)F-FET uptake.

122 O-(2-(18)F-fluoroethyl)-l-tyrosine ((18)F-FET) (7 studies, 172 lesions) demonstrated a sensitivity

123 ies using (18)F-fluoro-ethyl-tyrosine ((18)F-FET) (n = 31) and (68)Ga-DOTANOC (n = 7) and studies of

124 ake of 2-(18)F-fluoroethyl-l-tyrosine ((18)F-FET) and l-[methyl-(3)H]-methionine ((3)H-MET) in residu

125 ng O-(2-(18)F-fluoroethyl)-l-tyrosine ((18)F-FET) and proton MR spectroscopy (MRS) imaging of cell tu

126 ng O-(2-(18)F-fluoroethyl)-l-tyrosine ((18)F-FET) has been shown to be a useful tool for detecting TP

127 th O-(2-(18)F-fluoroethyl)-l-tyrosine ((18)F-FET) has gained increasing importance for glioma managem

128 O-(2-(18)F-fluoroethyl)-l-tyrosine ((18)F-FET) is a radiolabeled artificial amino acid used in PET

129 ng O-(2-(18)F-fluoroethyl)-l-tyrosine ((18)F-FET) is useful to detect residual tumor tissue after gli

130 ng O-(2-(18)F-fluoroethyl)-l-tyrosine ((18)F-FET) may be helpful for solving this diagnostic problem.

131 d O-(2-[(18)F]fluoroethyl)-l-tyrosine ((18)F-FET) PET for response assessment in glioma patients afte

132 of O-(2-(18)F-fluoroethyl)-l-tyrosine ((18)F-FET) PET for treatment monitoring of immune checkpoint i

133 operative (18)F-fluoro-ethyl-tyrosine ((18)F-FET) PET in children and adolescents would improve diagn

134 O-(2-(18)F-fluoroethyl)-l-tyrosine ((18)F-FET) PET is a well-established method increasingly used

135 ic O-(2-(18)F-fluoroethyl)-l-tyrosine ((18)F-FET) PET.

136 n, O-(2-(18)F-fluoroethyl)-l-tyrosine ((18)F-FET).

137 imaging, and dosimetric profile makes (18)F-FET-betaAG-TOCA a promising candidate radioligand for st

138 All patients tolerated (18)F-FET-betaAG-TOCA with no adverse events.

139 oroethyl triazole [Tyr(3)] octreotate ((18)F-FET-betaAG-TOCA) in patients with neuroendocrine tumors

140 MBq (mean +/- SD, 155.7 +/- 8 MBq) of (18)F-FET-betaAG-TOCA.

141 de II, 5 WHO grade III) with primarily (18)F-FET-negative glioma and available (18)F-FET PET follow-u

142 Overall, 20 of 31 primarily (18)F-FET-negative glioma turned (18)F-FET-positive during the

143 evaluation is useful even in primarily (18)F-FET-negative glioma, providing a high detection rate of

144 With regard to the occurrence of (18)F-FET-negative glioma, we investigated the value of (18)F-

145 (18)F-FET PET monitoring of primarily (18)F-FET-negative gliomas concerning the detection of progres

146 All (18)F-FET-negative metastases had a diameter of </= 1.0 cm, wh

147 ly a third of metastases < 1.0 cm were (18)F-FET-negative, most likely because of scanner resolution

148 ly a third of metastases < 1.0 cm were (18)F-FET-negative, most likely because of scanner resolution

149 TBRmax >/= 1.6 and were classified as (18)F-FET-positive (median TBRmax, 2.53 [range, 1.64-9.47]; TB

150 arily (18)F-FET-negative glioma turned (18)F-FET-positive during the follow-up.

151 ssing the postoperative situation than (18)F-FET.

152 d during 50 min after a 1-min bolus of (18)F-FET.

153 Conclusion:(8)F-FET uptake in glioblastomas seems to be largely independ

154 ng properties similar to those of (S)-[(18)F]FET in the DBT tumor model while (S)-[(18)F]14 afforded

155 o be increased 1.4- to 1.7-fold, with [(18)F]FET showing the biggest volume as depicted by a threshol

156 ing biomarker of active tumor volume ([(18)F]FET) in conjunction with MRI.

157 hed O-(2-[(18)F]fluoroethyl)tyrosine ([(18)F]FET) tracer in a head-to-head comparison.

158 O-(2-[(18)F]fluoroethyl)-l-tyrosine ([(18)F]FET), in the delayed brain tumor (DBT) mouse model of hi

159 uctors, and organic-material-based thin-film FETs.

160 g performance of BP as a sensing channel for FET biosensor applications.

161 ized rapid binding of bacterial cells to a G-FET by electrical field guiding to the device to realize

162 dielectrophoresis for the first time in a G-FET, allowing us to monitor changes in the Dirac point d

163 use of graphene field effect transistors (G-FET) including the first use of peptide probes to electr

164 For high sensitivity applications, G-FETs were functionalized by monoclonal antibodies specif

165 equency graphene field-effect transistors (G-FETs) were demonstrated, with extrinsic cutoff frequency

166 s were subsequently used in an extended gate FET setup for electrochemical detection of PSA.

167 In particular, dual-gated FETs based on multilayer MoS(2) and WSe(2) are used as c

168 The GONR-FET biosensor demonstrated a sensitivity of 12.5muA/mM (

169 mit, and a simple device structure, the GONR-FET sensor is suitable for sensing biomaterials.

170 ) change and Dirac point shift in a graphene FET.

171 to specific protein detection using graphene FET sensors.

172 ue, we fabricated protein-decorated graphene FETs and measured their electrical properties, specifica

173 view we focus on silicon-based immunological FET (ImmunoFET) for specific and label-free sensing of p

174 bility of conducting electrical impedimetric FET measurements with a portable unit for the ultrasensi

175 metric measurements, electrical impedimetric FET measurements yielded significant improvements in bio

176 In FETs, we find this oxidation destroys conductivity in th

177 Finally, a practical role of NC in FETs is to save the subthreshold and overdrive voltage l

178 sified applications of electric double layer FETs (EDL-FETs), a triboiontronic transistor is proposed

179 risk episodes varies from days to lifetimes, FET first increases, then falls.

180 tron donors in both monolayer MoS2 and MoSe2 FET devices ceases after moderate exposure, with final v

181 Unipolar n-type MoTe2 FETs with a high on-off ratio exceeding 10(6) are achiev

182 mer layer on the surface of silicon nanowire FET sensors.

183 pacitance limit are desired platforms for NC-FET construction.

184 is and findings are intended to steer the NC-FET research in the right direction.

185 ative-capacitance field-effect transistor(NC-FET) has attracted tremendous research efforts.

186 um-capacitance is the limiting factor for NC-FETs to achieve hysteresis-free subthermionic SS, and FE

187 Firstly, NiO-FET was tested for NADH detection showing a linear conce

188 different stages of AD by utilizing Si TL NW FET structures fabricated on the basis of cost-efficient

189 a observed in the novel Si two-layer (TL) NW FET structures with advanced characteristic parameters c

190 NW FETs functionalized by GNPs revealed extremely high pH s

191 The PSA concentrations determined by the NW FETs in serum were compared with well-established ELISA

192 The NW FETs were fabricated from SOI material using high-resolu

193 ilicon nanowire field effect transistors (NW FETs) with Schottky contacts (Si-Ti).

194 ials, have helped improve the sensitivity of FET biosensors and enabled detection down to single mole

195 s for improving the field-effect mobility of FETs compared to needle-like 1D structures, because of t

196 ly migrating T cells can be traced using our FET devices.

197 trates the potential advantages of SGTs over FETs as driver transistor for AMOLEDs display circuits w

198 However, the performance of perovskite FETs is hampered predominantly by device instabilities,

199 gh-performance solution-processed perovskite FETs.

200 ound biomolecules to readout of liquid-phase FETs fabricated with graphene or other two-dimensional m

201 ed molybdenum disulfide and black phosphorus FETs.

202 degradation of high-mobility, p-type polymer FETs and demonstrate an effective route to improve devic

203 much higher than that of previously reported FET biosensors.

204 wer value than that of a previously reported FET DNA biosensor whose sensing materials were in direct

205 that is connected to the gate of a reusable FET transducer.

206 by using our V(th) shifting model for the RG FET.

207 ng a remote-gate field-effect transistor (RG FET) detection system that was able to measure the elect

208 he presence of urea, the urease-modified rGO FETs showed a shift in the Dirac point due to the change

209 The modification of rGO FETs with a weak polyelectrolyte improved the pH respons

210 ne-oxide based field-effect transistors (rGO FETs) for the detection of urea.

211 O, thereby modulating the conductance of rGO-FET.

212 tics of back-gated Schottky barrier FETs (SB-FETs) from 2D channel materials.

213 l integrates the "conventional" model for SB-FETs with the phenomenon of contact gating - an effect t

214 observed; namely, the conductivity of a SCNT-FET was much higher (two orders of magnitude) than that

215 ow as 10 aM] was obtained using such an SCNT-FET, which showed a lower value than that of a previousl

216 SCNT)-based field effective transistor (SCNT-FET), which was fabricated by utilizing the surface tens

217 olymer film coupled to the gate of a silicon FET.

218 ld voltage ( V(th)) on the n-channel silicon FET.

219 icon nanowire field effect transistors (SiNW FETs) typically display exquisite sensitivities, but the

220 n alternative operation principle where SiNW FETs are operated in a frequency-domain electrical imped

221 The aptamer-modified SiNW-FET presented in this work enables the simple and sensit

222 nanowire-based field-effect transistor (SiNW-FET) biosensor, with a detection limit in the picomolar

223 While in the off-state, FETs shows comparatively better stability than SGTs devi

224 Such FET sensor shows high specificity for different matching

225 e apply an optogenetic approach to show that FET-family transcriptional regulators exhibit a strong t

226 The FET sensor is significantly faster than ELISA (<10 min),

227 The FET shows a switchable ambipolar behavior with independe

228 5 has a unique charge distribution among the FET family members that enhances its interactions with t

229 arge transport layer in the FET channel, the FET properties are tailored by controlling doping concen

230 xicity are capable of modeling data from the FET assay.

231 onse to infrared light was observed from the FET device.

232 The calibration curve from the FET sensor arrays showed good agreement in the physiolog

233 n films as the charge transport layer in the FET channel, the FET properties are tailored by controll

234 sed as the sensing/conducting channel in the FET, with an Al2O3 thin film as the dielectric layer for

235 lief is that the contacts can only limit the FET performance and hence the extracted mobility is an u

236 mechanisms (donor and gating effects) of the FET sensor were discussed.

237 al, which generates a signal response of the FET transducer.

238 icient triboelectric potential gating on the FET and explore diversified applications of electric dou

239 stic analysis supports the argument that the FET assay is a suitable alternative testing strategy for

240 nal changes by 10 times per pCl, whereas the FET signal changes by 8 or less times.

241 Accordingly, the FETs with higher GB densities showed much poorer electri

242 rays in wafer-scale is demonstrated, and the FETs show remarkable uniformity.

243 nce metrics are measured and compared as the FETs evolve from back-gated, to top-gated and finally, t

244 n and how this influences the readout of the FETs.

245 t governs the performance of atomically thin FETs and is applicable to the entire class of atomically

246 Meanwhile, this FET analysis tool offered a means of monitoring the phys

247 1 V) and hysteresis (0.9 V) when compared to FETs with the Al layer (V(Dirac) = - 6.1 V and hysteresi

248 ernative method is the fish embryo toxicity (FET) assay.

249 Fish embryo toxicity (FET) showed that the starch was not toxic and that it wa

250 back of charge screening seen in traditional FET based biosensors, allowing detection of target prote

251 of high-performance field-effect transistor (FET) arrays in wafer-scale is demonstrated, and the FETs

252 amer-functionalized field-effect transistor (FET) as a label-free sensor for AIV detection in chicken

253 ork, we developed a field effect transistor (FET) biosensor utilizing solution-processed graphene oxi

254 sphorous (BP)-based field-effect transistor (FET) biosensor was fabricated by using few-layer BP nano

255 Field effect transistor (FET) biosensors based on low-dimensional materials have

256 bricate a backgated Field Effect Transistor (FET) device for the first time using this precursor to d

257 he monolayer MoS(2) field effect transistor (FET) exhibits photo-induced short-term and long-term pot

258 ys an extended-gate field-effect transistor (FET) for direct potentiometric serological diagnosis.

259 probe on a graphene field effect transistor (FET) for high-specificity, single-nucleotide mismatch de

260 Field-effect transistor (FET) is a very promising platform for biosensor applicat

261 raphene oxide (rGO) field effect transistor (FET) is reported.

262 tic sensor based on field-effect transistor (FET) is reported.

263 Nanomaterial-based field-effect transistor (FET) sensors are capable of label-free real-time chemica

264 s review, different field-effect transistor (FET) structures and detection principles are discussed,

265 d to a bilayer MoS2 field effect transistor (FET) through deposition of a silicon nitride stress line

266 ipolar dual-channel field-effect transistor (FET) with a WSe2 /MoS2 heterostructure formed by separat

267 S)-based biosensor, field-effect transistor (FET)-based biosensor, surface plasmon resonance (SPR)-ba

268 Field-effect transistor (FET)-based biosensors allow label-free detection of biom

269 tamer probes and 2) field-effect transistor (FET)-based sensor arrays.

270 e vision of silicon field-effect transistor (FET)-based sensors has been an attractive venue for addr

271 sitive and specific field-effect transistor (FET)/chemiresistor (CR) biosensors.

272 otubes (SWNTs) in a field-effect transistor (FET)/chemiresistor architecture with selective antibodie

273 mensional nanowire field-effect transistors (FET) and quantum bit (qubit) devices.

274 ities by utilizing field-effect transistors (FET) based on two phases of titanyl phthalocyanine (TiOP

275 e of extended gate field-effect transistors (FET) for the label-free and sensitive detection of prost

276 Field effect transistors (FET) have been widely used as transducers in electrochem

277 emonstrate through field-effect transistors (FET) measurements that amorphous red phosphorus (a-RP) f

278 nd should apply to field effect transistors (FET) with high-kappa dielectric gates, van der Waals het

279 e oxide materials: field-effect transistors (FETs) and source-gated transistors (SGTs).

280 f silicon nanowire field-effect transistors (FETs) and the signal-conditioning circuitry on the same

281 h-mobility polymer field-effect transistors (FETs) are demonstrated by modest doping and charge compe

282 mically thin MoTe2 field-effect transistors (FETs) are measured during cycles of pulses through the g

283 conjugated polymer field-effect transistors (FETs) are promising candidates for enabling flexible ele

284 the performance of field-effect transistors (FETs) based on novel nanomaterials.

285 (Si) nanowire (NW) field-effect transistors (FETs) covered with a thin SiO(2) dielectric layer have b

286 insofar WSe2-based field-effect transistors (FETs) display the largest Hall mobilities among the tran

287 solution-processed field-effect transistors (FETs) for next-generation, low-cost, flexible electronic

288 g fabricated Si NW field-effect transistors (FETs) in combination with fluorescent marker techniques

289 electrolyte-gated field-effect transistors (FETs) induce an extremely large local electric field tha

290 telluride (MoTe2 ) field-effect transistors (FETs) is described, through rapid thermal annealing (RTA

291 molecule-decorated field-effect transistors (FETs) range from biosensors to in vivo implants.

292 Field-effect transistors (FETs) with Pd edge contact and Au edge contact show high

293 d black phosphorus field effect transistors (FETs), as a class of analog and probabilistic computatio

294 c devices, such as field effect transistors (FETs), from these materials require patterning and fabri

295 g liquid-ion gated field-effect transistors (FETs).

296 hene for top gated field effect transistors (FETs).

297 l alignment allows creation of p- and n-type FETs on the same intrinsic MoS(2) flake using Pd and low

298 Here, we use FETs with a deformed monolayer graphene channel for the

299 pta-MIP sensor developed in conjunction with FET devices demonstrates the potential for clinical appl

300 ective aptamer-lined pockets (apta-MIP) with FETs for sensitive detection of prostate specific antige