ライフサイエンスコーパス: FET

1 FET devices constructed with the red phosphorus nanowire

2 FET proteins are of medical interest because chromosomal

3 FET proteins can also bind DNA, which may be important i

4 FETs were fabricated based on the well ordered films; we

5 ffected live births were achieved in 9 of 20 FET cycles (45%), with only one false negative (among 54

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

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

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

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

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

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

12 hat graphene or its assisted composite based FET devices are comparatively more efficient and sensiti

13 A graphene monolayer-based FET-like structure is incorporated on a PDMS substrate w

14 ore, the contemplation of nanomaterial-based FET biosensors to various applications encompasses the d

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

16 uiring I-V curves of the bare nanowire-based FETs.

17 ation for reduced Graphene-Oxide (rGO) based FETs used for biosensing applications.

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

19 gling bonds are likely to produce WSe2-based FETs displaying higher room temperature mobilities, i.e.

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

21 In comparison to previous cell-FET-biosensors, the CnuMOS features control (CG), sensin

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

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

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

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

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

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

28 an extended-gate field-effect transistor (EG-FET) signal transducing unit.

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

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

31 ed extended-gate field-effect transistor (EG-FET) was used for signal transduction.

32 notyping needs to be timely enough to enable FET.

33 ) than for (18)F-FDG (1.3 +/- 0.1) and (18)F-FET (2.0 +/- 0.3).

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

35 imaging baseline VOIs was greater for (18)F-FET (79%-93%) than (123)I-CLINDE (15%-30%).

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

37 cant differences in uptake pattern for (18)F-FET and (18)F-DOPA in patients with primary or recurrent

38 (18)F-FET and (18)F-DOPA PET/CT images were compared visually

39 of this study was to determine whether (18)F-FET and (18)F-DOPA PET/CT provide comparable information

40 Thirty (18)F-FET and (18)F-DOPA PET/CT scans were obtained before sur

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

42 e whether (123)I-CLINDE is superior to (18)F-FET in predicting progression of glioblastoma multiforme

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

44 (18)F-FET is predominantly used in Europe, whereas amino acid

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

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

47 s, TBR was higher in rCBV maps than in (18)F-FET PET (TBR, 5.33 +/- 2.63 vs. 2.37 +/- 0.32; P < 0.001

48 (18)F-FET PET analysis comprised a qualitative visual classifi

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

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

51 d was evaluated for the combination of (18)F-FET PET and MR imaging compared with MR imaging alone.

52 All patients had undergone (18)F-FET PET and MR imaging for preoperative evaluation or fo

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

54 In this study, we directly compared (18)F-FET PET and PWI in patients with brain tumors.

55 gliomas were investigated using static (18)F-FET PET and PWI.

56 rmalized histograms were generated for (18)F-FET PET and rCBV maps.

57 th cerebral glioma, tumor imaging with (18)F-FET PET and rCBV yields different information.

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

59 diagnosed low-grade glioma and dynamic (18)F-FET PET before histopathologic assessment were retrospec

60 III; 70 WHO IV) and underwent dynamic (18)F-FET PET before histopathologic assessment.

61 Our findings suggest that (18)F-FET PET can add valuable information for clinical decisi

62 easing time-activity curves in dynamic (18)F-FET PET constitute an unfavorable prognostic factor in a

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

64 Integration of (18)F-FET PET has the potential to avoid overtreatment and cor

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

66 el suggests that the additional use of (18)F-FET PET in the management of patients with recurrent hig

67 Thus, repeated (18)F-FET PET may be helpful for further treatment decisions.

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

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

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

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

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

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

74 ferred these VOIs to the corresponding (18)F-FET PET scans and PWI maps.

75 Sixty-nine (18)F-FET PET scans of 48 children and adolescents (median age

76 Furthermore, in rCBV maps and in (18)F-FET PET scans, tumor volumes, their spatial congruence,

77 (18)F-FET PET shows considerably higher TBRs and larger tumor

78 lioma, TBR was significantly higher in (18)F-FET PET than in rCBV maps (TBR, 2.28 +/- 0.99 vs. 1.62 +

79 r volumes were significantly larger in (18)F-FET PET than in rCBV maps (tumor volume, 24.3 +/- 26.5 c

80 The diagnostic accuracy of (18)F-FET PET was assessed by receiver-operating-characteristi

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

82 Effectiveness of (18)F-FET PET was defined as correct identification of both tu

83 were scanned with (123)I-CLINDE SPECT, (18)F-FET PET, and gadolinium-enhanced MR imaging.

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

85 ncremental cost-effectiveness ratio of (18)F-FET PET/MR imaging compared with MR imaging alone was eu

86 ram analysis of the VOIs revealed that (18)F-FET scans could clearly separate tumor from background.

87 SUV(max) were significantly higher for (18)F-FET than (18)F-DOPA (TBR SUV(mean): 3.8 +/- 1.7 vs. 3.4

88 e compared with those of (18)F-FDG and (18)F-FET through small-animal PET analyses.

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

90 Dynamic (18)F-FET uptake analysis was available for 30 of these 34 pat

91 olumes of interest (VOIs) of increased (18)F-FET uptake and (123)I-CLINDE binding was variable (12%-4

92 rest analysis was performed to compare (18)F-FET uptake and ADC values in areas with focal intratumor

93 There is no congruency between (18)F-FET uptake and diffusivity in nonenhancing LGG.

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

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

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

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

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

99 (18)F-FET uptake did not correlate with corresponding (colocal

100 (18)F-FET uptake greater than the background level was found i

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

102 Absence of (18)F-FET uptake in newly diagnosed astrocytic low-grade gliom

103 mean +/- SD, 1.69 +/- 0.85) and global (18)F-FET uptake in tumors (1.14 +/- 0.41) exceeded that of no

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

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

106 litative factor presence or absence of (18)F-FET uptake nor any of the semiquantitative uptake parame

107 ADC values were also compared with the (18)F-FET uptake on a voxel-by-voxel basis across the whole tu

108 ; and dynamic analysis of intratumoral (18)F-FET uptake over time (increasing vs. decreasing time-act

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

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

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

112 (18)F-FET uptake was normalized to the mean cerebellar uptake

113 injection, and time-activity curves of (18)F-FET uptake were assigned to 3 different patterns: consta

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

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

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

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

118 1.0 cm diameter all showed pathologic (18)F-FET uptake, which did not correlate with lesion size.

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

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

121 with baseline (123)I-CLINDE VOIs than (18)F-FET VOIs (21% vs. 8% and 72% vs. 55%).

122 The SUV(mean) and SUV(max) for (18)F-FET were higher than those of (18)F-DOPA (4.0 +/- 2.0 an

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

124 -(2-(18)F-fluoroethyl)-l-tyrosine PET ((18)F-FET) and investigate whether (123)I-CLINDE is superior t

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

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

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

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

129 ng O-(2-(18)F-fluoroethyl)-L-tyrosine ((18)F-FET) PET in children and adolescents with brain tumors i

130 e of dynamic (18)F-fluorethyltyrosine ((18)F-FET) PET in the early diagnosis of astrocytic low-grade

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

132 of O-(2-(18)F-fluoroethyl)-L-tyrosine ((18)F-FET) PET to noninvasively detect malignant progression i

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

134 ic O-(2-(18)F-fluoroethyl)-L-tyrosine ((18)F-FET) PET.

135 ng O-(2-(18)F-fluoroethyl)-L-tyrosine ((18)F-FET) provides important diagnostic information in additi

136 cid O-(2-(18)F-fluorethyl)-L-tyrosine ((18)F-FET) to search for focal changes of diffusion (ADC) and

137 as O-(2-(18)F-fluoroethyl)-l-tyrosine ((18)F-FET), 3,4-dihydroxy-6-(18)F-fluoro-l-phenylalanine ((18)

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

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

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

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

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

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

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

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

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

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

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

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

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

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

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

153 Among the (18)F-FET-positive gliomas, decreasing time-activity curves in

154 blood-brain barrier permeability than (18)F-FET.

155 UV(mean) were significantly higher for (18)F-FET.

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

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

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

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

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

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

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

163 tumor to brain ratios compared to (S)-[(18)F]FET, a well-established system L substrate.

164 As a proof of concept, the fabricated FET responds to nM concentration levels (with a LOD of a

165 The in-house fabricated FETs used in the present study are providing a novel and

166 Finally, FET measurements of doped NC films and the demonstration

167 We find FET is strongly biased toward over-estimating overlap si

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

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

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

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

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

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

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

175 to specific protein detection using graphene FET sensors.

176 In contrast to large area graphene FETs, we find that a suspended graphene QD has an almost

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

178 numerous false-positive enrichment scores in FET, and we therefore suggest it be used to more accurat

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

180 tigate the applicability of the microfluidic FET (muFET) in toxicity testing, copper sulfate, phenol,

181 Unlike previous MoS2-FET-based biosensors, the device configuration of our bi

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

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

184 es the current flowing through each nanowire FET upon applying a constant source-drain voltage.

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

186 nT) through antibody-functionalized nanowire FETs.

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

188 Here we demonstrate fabrication of novel FET biosensor devices using SWNTs as semiconducting chan

189 NW FETs functionalized by GNPs revealed extremely high pH s

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

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

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

193 pite the importance and common acceptance of FET, it is still performed in multiwell plates and requi

194 to the translational clinical application of FET in the detection of cancer protein markers.

195 terature here to illustrate the diversity of FET-based biosensors, based on various kinds of nanomate

196 both the normal and pathological effects of FET proteins are modulated by low-complexity or prion-li

197 mphasis on how the biochemical properties of FET proteins may relate to their biological functions an

198 s of our study indicate the applicability of FETs for cancer research and analyzing pharmacological e

199 e much lower than previously studied organic FETs.

200 At others FET is lower, but a high R0 makes eradication impossible

201 In former studies we used our FET devices to conduct Electrical Cell-substrate Impedan

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

203 nhancement of the photoresponsivity in PCBDR FETs up to 10(3) .

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

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

206 Herein, we review FET proteins with an emphasis on how the biochemical pro

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

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

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

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

211 imits of applicability for the presented rGO-FETs.

212 At some levels of episodic risk, FET can be high, but eradication is easy because R0 is l

213 tion of ultrasensitive, low-cost, and robust FET-based biosensors; these are categorically very succe

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

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

216 icon nanowire field-effect transistors (SiNW FETs) is described and has been preclinically validated

217 This MPC aptamer/SiNW-FET was also applied to monitor DA release under hypoxic

218 The modification of poly-SiNW-FET by magnetic graphene with long-chain acid groups (MG

219 The Ab-MGLA/poly-SiNW-FET exhibited a linear dependence of relative response t

220 nanowire field-effect transistor (poly-SiNW-FET).

221 While applications of SiNW-FETs for detection of biological species have been descr

222 icon nanowire field effect transistors (SiNW-FETs) have shown great promise as biosensors in highly s

223 rbon nanotube field-effect transistor (SWCNT-FET) to investigate accommodation of dNTP analogs with s

224 ation of performance and instability of SWNT-FET biosensor devices.

225 rlap statistics, such as Fishers Exact test (FET), are often employed to assess these associations, b

226 This work provides evidence that FET analysis performed under microperfusion opens a bran

227 The FET sensing platform has been fabricated using a complem

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

229 The FET shows a switchable ambipolar behavior with independe

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

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

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

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 Moreover, the FET-type DRNCN biosensor had a rapid response time (<1 s

236 Members of the FET protein family, consisting of FUS, EWSR1, and TAF15,

237 ifferent metals has limited influence on the FET performance, suggesting that the 1T/2H interface con

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

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

240 lues of the electrolytes in contact with the FET.

241 The FETs used in the experiments were fabricated using wet-c

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

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

244 a trans-impedance amplifier circuit for the FETs with a higher bandwidth compared to a previously de

245 Furthermore, the FETs were tested for the sensing of biomolecules (bovine

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

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

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

249 The fish embryo toxicity (FET) biotest has gained popularity as one of the alterna

250 brafish embryos during fish embryo toxicity (FET) biotests.

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

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

253 notyping, followed by fresh embryo transfer (FET).

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

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

256 cells on pre-coated field-effect transistor (FET) devices (i.e. fibronectin, anti-CD3 antibody, and a

257 Field-effect transistor (FET) electron mobilities musat up to 3 cm(2)/(V.s) are m

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

261 Here, a field-effect transistor (FET) sensor device is fabricated based on 2D phosphorene

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

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

264 a liquid-ion gated field-effect transistor (FET) system via immobilization and attachment processes,

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 assay in a graphene field effect transistor (FET), and demonstrate the utility of the nanosensor with

268 raphene oxide (rGO) field-effect transistor (FET), functionalized by the odorant-binding protein 14 (

269 acroscopic graphene field-effect transistor (FET), increasing linearly with temperature.

270 devices, including field effect transistor (FET)-based devices.

271 current response of field-effect-transistor (FET)-based biosensors.

272 response in n-type field-effect transistors (FET) and lateral photoconductors using a solution-proces

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

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

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

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

281 Field effect transistors (FETs) based on 2D TMDs are basic building blocks for nov

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

283 Field effect transistors (FETs) have been fabricated based on this novel herterost

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

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

286 use ion-sensitive field-effect transistors (FETs) to analyze the apoptosis inducing effects of hydro

287 on nanotube (SWNT) field-effect transistors (FETs) to use as a fast and accurate sensor for a Lyme di

288 rs on pH-sensitive field-effect transistors (FETs) using an analytical kinetic PenFET model.

289 Field-effect transistors (FETs) with 1T phase electrodes fabricated and tested in

290 rrays of pentacene field effect transistors (FETs) with various channel lengths from 50 mum down to 5

291 changes the fraction of early transmissions (FET) and the basic reproduction number (R0) and conseque

292 TFET) is the only planar architecture tunnel-FET to achieve subthermionic subthreshold swing over fou

293 in and layered semiconducting-channel tunnel-FET (ATLAS-TFET) is the only planar architecture tunnel-

294 17, and is also the only tunnel-FET (in any architecture) to achieve this at a low power

295 band tunnel field-effect transistors (tunnel-FETs), based on a two-dimensional semiconductor, that ex

296 strate that our novel approach of ECIS using FET devices can be expanded to primary neuronal tissue w

297 measured using off-center spin-coating, with FET devices made from DAP PNDIT2 exhibiting better repro

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

299 ntegration of electrodeposited MIP film with FET transducer.

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