ライフサイエンスコーパス: sensor

1 resulted in the production of a KI-sensitive sensor.

2 TIM1), an endo/sarcoplasmic reticulum Ca(2+) sensor.

3 the pH response of an extended gate ISFET pH sensor.

4 ion of enzymatic activity in solution by the sensor.

5 onductivity and hence the sensitivity of the sensor.

6 echanisms that affect the performance of the sensor.

7 s compared to the recently reported p-cresol sensor.

8 bundles can serve as ultra-flexible textile sensors.

9 ations that could be imaged with fluorescent sensors.

10 mponents of the ROS sensing machinery or ROS sensors.

11 , high-sensitivity and low-cost biomolecular sensors.

12 y the prohibitive costs of existing chloride sensors.

13 ability relative to first-generation voltage sensors.

14 sm underlying such impedance based microflow sensors.

15 primates with acutely (few hours) implanted sensors.

16 in-film solar cells, transistors and optical sensors.

17 s not face issues usually common to reusable sensors.

18 In this structure, the voltage sensors adopt a depolarized conformation, and the pore i

19 (CardioMEMS Heart Sensor Allows Monitoring of Pressure to Improve Outcomes

20 The intrinsic amphipathic lipid packaging sensor (ALPS) motif within HOPS Vps41, a target of the v

21 The sensor also exhibited excellent selectivity for SY over

22 The real-time monitoring of embedded SWCNT sensors also allows residence times in the roots, stems

23 mbrane driven by activation of the metabolic sensor AMP kinase.

24 In this study, we identify the metabolic sensor AMP-activated protein kinase (AMPK) as a beta1-in

25 history and emergence of ZBP1 as a pathogen sensor and a central regulator of cell death and inflamm

26 of dStim, the endoplasmic reticular calcium sensor and a principal component of SOCE in the nervous

27 Said devices are: a non-enzymatic sensor and an enzymatic biosensor, the latter showing pr

28 ique composite allowed us to miniaturize the sensor and couple it with a Pt electrode (25 mum diamete

29 ability of the proposed Azu-A based chemical sensor and GOx based biosensor towards the determination

30 ic device with integrated optical pH, oxygen sensors and algal fluorescence.

31 ntial uses of this energy to power different sensors and analysis devices in a wide variety of in-vit

32 ment of new membrane protein electrochemical sensors and enzyme electrodes.

33 bundance in plants, the properties of Ca(2+) sensors and identification of novel target proteins of C

34 PHD1 to PHD3 are molecular oxygen sensors and increasingly considered as putative therapeu

35 distinct interplay between host non-self RNA sensors and pathogenic arenaviruses, which also provides

36 ases of matter, the development of precision sensors and state-of-the-art atomic clocks.

37 ighlight the rich potential of nanoplasmonic sensors and the future growth prospects of the community

38 eceptor), TXNIP (encoding a glucose-feedback sensor) and CNR2 (encoding a cannabinoid receptor) as ce

39 -1 (STIM1), which functions as the SR Ca(2+) sensor, and Orai1, the Ca(2+)-permeable channel in the T

40 todetectors for wearables, conformable image sensor, and other optoelectronic applications.

41 on limit and the quantification limit of the sensor are found to be 1.62x10(-3)microM and 6.14x10(-3)

42 Electrochemical sensors are an attractive platform for analytical measur

43 I and DIV S3-S4 loops of NaV channel voltage sensors are important for the interaction of Pre1a with

44 However, current liquid-metal-based strain sensors are incapable of resolving small pressure change

45 tures by which signals from distinct mechano-sensors are integrated to modulate hypertrophy and gene

46 alow power consumption, and high-sensitivity sensors are significant for miniaturized wearable physio

47 Fluorescence sensors are useful tools for the non-destructive assessm

48 sensor fouling may enable long-term in situ sensor array operation in low resource settings.

49 he various types of biomimetic crossreactive sensor arrays (also referred to as electronic noses or t

50 Here, large-area all-textile-based pressure-sensor arrays are successfully realized on common fabric

51 dual electrochemical pH and cell-attachment sensor arrays were developed for the real-time spatial a

52 of single-photon avalanche detectors, image sensor arrays, and silicon photomultipliers over a broad

53 lizing such specially-designed nanoplasmonic sensor as working electrode, both electrical and spectra

54 ork has introduced a new fluorescent voltage sensor, ASAP1, which can monitor rapid trains of action

55 Using a quantum sensor associated with the nitrogen vacancy center in di

56 responses of two genetically encoded Zn(2+) sensors at a range of time points spanning several secon

57 xplores a compact nanoelectronic temperature sensor based on a Magnetic Tunnel Junction (MTJ) structu

58 A new type of nitrogen dioxide (NO2 ) gas sensor based on copper phthalocyanine (CuPc) thin film t

59 A new enzyme-free sensor based on iron oxide (Fe3O4) nanodots fabricated o

60 ritically analyses advances of multivariable sensors based on ligand-functionalized metal nanoparticl

61 Our results suggest that microflow sensors based on the concept of elastic deformation coul

62 is study, we describe and characterize novel sensors based on the Systematic Protein Affinity Strengt

63 ale MD simulation-based predictions and FRET sensor-based experiments, we investigated the conformati

64 re-evaluate the binding parameters of these sensors both in the test tube and in living cells.

65 rest is biotinylated and detected by the GMR sensor by linking streptavidin magnetic nanoparticles (M

66 e capacity of DA neurons to act as metabolic sensors by responding not only to hormones but also to F

67 rce resolution 1microN, 0-10mN for the given sensor; [Ca(2+)] range 100nM-25microM).

68 High pressure sensor calibrations were performed in standard solutions

69 tration of glucose detected by the patterned sensor can be converted to fluorescence spectra with hig

70 on Sensitive Field Effect transistor (ISFET) sensor can be significantly enhanced.

71 rical and kinetic responses the flexible ZnO sensor can be used for detection and discrimination betw

72 molecules near the sensor surface, the LSPR sensor can discriminate fine differences in the extent o

73 The sensors can determine relative levels of miRNAs in total

74 an embedded microfluidic diaphragm pressure sensor capable of real-time pulse monitoring and a PDMS

75 nown if, and how, calcineurin B-like calcium sensors (CBLs) and CBL-interacting protein kinases (CIPK

76 f affected cells, where it activates the DNA sensor cGAS.

77 ty graphene-coated IDE-arrays with identical sensor characteristics and assays covering clinically re

78 r comb structured gold electrode array based sensor chip.

79 architecture and coupling them with both the sensor chips, functionalized with Hep-B and Hep-C antibo

80 Low modulus, compliant systems of sensors, circuits and radios designed to intimately inte

81 Sensors consist of a GPCR and G protein tethered by an E

82 and spectral responses on the surface of the sensor could be simultaneously detected during the elect

83 rameters and long term stability of both the sensors could be envisioned as a result of facile immobi

84 e relevant parameter for all other plasmonic sensor counterparts.

85 ependently controlled; the cytoplasmic Cu(+) sensor CueR controls cytoplasmic chaperones and plasma m

86 ped software that automatically analyzes the sensor data to measure mobility and assign the highest l

87 ay kinetics of the fluorescence of the miRNA sensors, demonstrated that miRNAs induce translational r

88 onsiderable interest in applications such as sensors, detectors, energy harvesting cells, and batteri

89 he versatile fabrication methods utilized in sensor development, superior sensitivity, prolonged stab

90 ate electrode, which imposes restrictions on sensor device architectures and results in added expense

91 Our universal NV-based sensor device records single-spin NMR spectra with 13 Hz

92 To form the sensor device, the CNT deposits were functionalized via

93 improvement comes the ability to deploy E-AB sensors directly in situ in the veins of live animals, a

94 ted in pure methanol, a solvent in which the sensor does not aggregate, no fluorescence response to f

95 ressed by designing a new class of nanoscale sensors dubbed nanopore extended field-effect transistor

96 ations between the pore gate and the voltage sensor during deactivation.

97 tudies revealed that the novel GC/rGO-Nf@Ag6 sensor electrode could be a potential candidate for the

98 d found improved sensitivity relative to the sensor electrode prepared from wild-type M13, Y3E peptid

99 R stress." Sustained activation of ER stress sensors endows malignant cells with greater tumorigenic,

100 n) of at least 5 times higher than a similar sensor equipped with the original dense silver IDEs, whi

101 A proof-of-concept gas sensor equipped with the resulting porous gold IDEs feat

102 As-designed Fabry-Perot (F-P) sensors exhibit nearly synchronous pressure-deflection r

103 The electrochemical sensor exhibited excellent sensitivity (G = 178.8 nA/mug

104 Further, the sensor exhibited long-term stability, which could be due

105 mutant with constitutively activated voltage sensors, F56Bpa and F57Bpa KCNE1 were cross-linked in op

106 The sensor features greater power economy and analytical per

107 were applied in a multimolecular FRET based sensor for detecting activation of a heterotrimeric G-pr

108 method that can be implemented on a wearable sensor for detecting field football head impacts.

109 DA-DA enables the construction of strategic sensor for detecting temperature changes in different ap

110 me that the primary cilium acts as a crucial sensor for electrical field stimulation (EFS)-enhanced o

111 ntial and practical approaches of using this sensor for non-destructive diagnosis of rice nitrogen (N

112 c imprinted polymer modified electrochemical sensor for the targeted detection, removal and destructi

113 configured as ultra-high sensitivity thermal sensors for a broad range of applications.

114 s the growing trend to utilize nanoplasmonic sensors for advanced measurement capabilities, including

115 mproved the sensitivity of FRET-based kinase sensors for monitoring kinase activity under two-photon

116 way for the realization of light-switchable sensors for the analyte or biosensors by combination wit

117 ported and the best MOF-based chemiresistive sensors for these analytes.

118 cence resonance energy transfer (FRET)-based sensors for these kinases had previously been developed,

119 rolonged stability, and lack of non-specific sensor fouling may enable long-term in situ sensor array

120 We re-engineered the Cdt1-based sensor from the original Fucci system to respond to S ph

121 e measured and compared against a commercial sensor giving no significant differences.

122 sensitivity of the film, whereby the GN/BCN sensor has 12400% sensitivity for vapor-phase ethanol co

123 The most sensitive sensor has a limit of detection (LOD) of 0.11 mug/L and

124 The sensor has a linear response in the range of 20-160micro

125 Moreover, the proposed sensor has a wide dynamic range, high linearity, fast op

126 The sensor has also been used to track dynamic changes that

127 A paper strip sensor has been fabricated for successful detection of S

128 The sensor has been successfully applied for the detection o

129 The proposed paper-based colorimetric DNA sensor has potential to be an alternative approach for s

130 chanism for fluorescence modulation in these sensors has been attributed to some form of photoinduced

131 A great number of sensors have been developed, but their activity is gener

132 Although sensitive and accurate tactile sensors have been produced on optical and electronic dev

133 Most importantly, PEDOT-C14-based SC pH sensors have no CO2 interference, an essential pH sensor

134 Strategies for the chronic use of such sensors have recently been established successfully in r

135 lization of a SPR based fiber optic nicotine sensor having coatings of silver and graphene doped ZnO

136 Notably, utilizing skin as part of the EII sensor, high pressure sensitivity and high signal-to-noi

137 Newman and some other S. aureus strains, the sensor histidine kinase SaeS has an L18P (T53C in saeS)

138 nal transduction in sensor histidine kinases.Sensor histidine kinases (SHK) consist of sensor, linker

139 esents a template for signal transduction in sensor histidine kinases.Sensor histidine kinases (SHK)

140 Our results reveal that the new microneedle sensor holds considerable promise for continuous non-inv

141 nt stability and repeatability, the proposed sensor holds practical implementation possibilities in t

142 mouse line with an optimized hybrid voltage sensor (hVOS) probe within a locus designed for efficien

143 pics that we discuss here are supramolecular sensors, imaging for medical applications, metal extract

144 atients undergoing pulmonary artery pressure sensor implantation between June 1, 2014, and December 3

145 trasensitive surface plasmon resonance (SPR) sensor in a checkerboard nanostructure on plastic substr

146 ces that utilizes a smartphone camera as the sensor in conjunction with a hand-held "cradle" that int

147 ding evidence for an essential role of a DNA sensor in human immunity.

148 er 8 (TRPM8) is the primary cold and menthol sensor in humans.

149 sure continuously with a fast intra-vascular sensor in the carotid artery of anaesthetized, mechanica

150 channel behaviour suggests that the voltage sensor in the first domain is a rate limiting step for r

151 By genetically encoding this sensor in the human malarial parasite, Plasmodium falcip

152 r samples to demonstrate their usefulness as sensors in a deep-sea environment.

153 of transcription 1 signaling and dsRNA viral sensors in macrophages.

154 Synaptotagmins (Syts) act as Ca(2+) sensors in neurotransmitter release by virtue of Ca(2+)-

155 nd dynamic range of Prussian Blue based (bio)sensors in power generation mode are, respectively, even

156 Selectivity of the (bio)sensors in power generation mode is similarly high relat

157 iated gene 5 (MDA5), which are crucial viral sensors in the host innate immune system.

158 new routes for the biointegration of various sensors in wearable electronics systems, and toward adva

159 is to carefully select nodes (sentinels, or sensors) in the network to report outbreaks.

160 ith the differential regulation of ER stress sensors, in particular Perk.

161 luminescence intensity of the patterned FRET sensor increases linearly with increasing concentration

162 sing novel applications for high performance sensor, infrared photodetector and cavity quantum electr

163 ution at room temperature.Dissipation of the sensor is a limiting factor in metrology.

164 Noninvasive mobility sensor is a novel and feasible method for automating eva

165 se results indicate that an implanted strain sensor is an effective tool to help assess bone healing

166 addition, the performance of this PAni-based sensor is compared to fluorescence measurements, and it

167 Thanks to these merits, the textile sensor is demonstrated to be able to recognize finger mo

168 y, a facile room-temperature phosphorescence sensor is developed to detect DA based on l-cysteine cap

169 The sensor is found to be more sensitive than most of the li

170 how that signalling through the TrpA1 thermo-sensor is required for PMW, and that TrpA1 specifically

171 We demonstrate that the sensor is selective and is able to quantify diclofenac i

172 These results suggest this electrochemical sensor is suitable for environmental and potentially bio

173 on of MIP nanoparticles with micromechanical sensors is one of the pioneer studies in the mass sensin

174 cteristics of poly(3-APBA) based enzyme-free sensors justify their future use for noninvasive clinica

175 ase (AMPK), a major decorin-activated energy sensor kinase, prevented decorin-evoked TFEB induction a

176 -based parameters, we accurately explain the sensor-level sustained field amplitude, demonstrating th

177 that stabilization of the activated voltage sensor limits the return of hERG channels to rest.

178 es.Sensor histidine kinases (SHK) consist of sensor, linker and kinase modules and different models f

179 However, quantum sensors lose their sensitivity in the presence of noise.

180 A pressure-sensor matrix (PSM) with full dynamic range can accurate

181 eal that the use of this electrochemical bio-sensor may provide a potential platform for the detectio

182 ) allows simultaneous measurement of voltage sensor movement and current through the channel pore.

183 S140G, but not V141M, directly slows voltage sensor movement, which indirectly slows current deactiva

184 idered a potential solution for self-powered sensor networks and large-scale renewable blue energy.

185 a, and indicated a role for the inflammasome sensor NLRP3 and for potassium efflux in T. gondii-induc

186 Thus, we propose that FACT acts as a sensor of ADS formation in cells.

187 RAGE can also act as an innate immune sensor of microbial pathogen-associated molecular patter

188 tivated cation channel Piezo1 is a molecular sensor of physical exercise in the endothelium that trig

189 gradation are well-understood, the molecular sensors of aberrant mRNAs and their mechanism of action

190 Genetic ablation of sensors of apoptotic cells impaired the proliferation of

191 Primary cilia are sensors of electrical field stimulation to induce osteog

192 Electrochemical aptamer-based (E-AB) sensors offer advantageous analytical detection abilitie

193 Most importantly, these sensors offer low-cost and disposable detection platform

194 y higher and wider compared to the same (bio)sensors operated in the conventional three-electrode reg

195 latform to contrive next-generation chemical sensors, optoelectronics, energy harvesters, and convert

196 plications such as wireless and self-powered sensors or low-power electronics.

197 to detection with traditional RGB intensity sensors or the naked eye.

198 demonstrate that the autocorrelation of the sensor output alone is sufficient to find this optimal n

199 DNAzymes have enjoyed success as metal ion sensors outside cells.

200 sting that the RNase L system is the primary sensor pathway for endogenous dsRNA that leads to cell d

201 that proton binding at the intracellular pH sensor perturbs the potassium affinity at the extracellu

202 to glucose determination using a bienzymatic sensor phase (glucose oxidase/horseradish peroxidase) wi

203 The electrochemical, aptamer-based (E-AB) sensor platform provides a modular approach to the conti

204 (EIS) and Mott-Schottky analysis on the same sensor platform to demonstrate multi-configurable modes.

205 nd utilize this finding in the design of the sensor platform.

206 s in the design and fabrication of efficient sensor platforms based on nanostructures make the highly

207 ng field effect transistors into biochemical sensor platforms is the requirement of a gate electrode,

208 The CdSe/ZnS/LiTCNE photoelectrochemical sensor presented a linear range from 0.6 to 250mumolL(-1

209 The optimization of the potentiometric sensor presented here yields an outstanding analytical p

210 ytical characteristics comparable to glucose sensors previously reported using conventional electrode

211 rs have no CO2 interference, an essential pH sensors property when aimed for whole-blood analysis.

212 e protein 16 (IFI16) is an immunological DNA sensor proposed to act in the cyclic GMP-AMP synthase-st

213 quantify the interaction of neuronal Ca(2+)-Sensor proteins with their targets operating in phototra

214 In addition, the electrochemical DNA sensors provide direct electronic signal without the use

215 The integrated sensor provided a very low detection limit (25 fM, 0.25

216 on of the detection limit for potentiometric sensors provided by the IUPAC.

217 h, in higher plants, requires the luminal pH sensor PsbS and other yet unidentified components of the

218 we describe a quantitative redox-activatable sensor (qRAS) for the real-time monitoring of cytosolic

219 ylate cyclase --> cAMP --> neuritogenic cAMP sensor-Rapgef2 --> B-Raf --> MEK --> ERK pathway mediati

220 In addition to their role as microbial sensors, recent evidence indicates that nucleotide-bindi

221 The sensor-regulator hybrid SagS plays a central role in bio

222 The sensor relies on differentiating the RBC deformability (

223 M2, suggesting STIM1 is the dominant calcium sensor required for classical short-term neutrophil resp

224 DNA layer is measured through changes of the sensor resonance frequency upon hybridization and at var

225 Under optimal flow conditions, the sensor responded linearly in the concentration range of

226 The faster phase of voltage-sensor return slowing correlated with the kinetics of po

227 Furthermore, a dsFP-based miR-132 sensor revealed the rapid kinetics of miR-132 activation

228 mensional calibration plot demonstrating the sensor's suitability to enable a rapid process decision

229 as well as wireless connections for wireless sensors, security, and control networks.

230 sh the task, a tubular shaped potentiometric sensor selective to perchlorate ion was constructed with

231 In the present study a simple colorimetric sensor should be developed and tested for the real-time

232 The sensor showed high selectivity and sensitivity towards N

233 ns for culturing confluent monolayers on the sensor slides were optimized, and neurotransmitter exocy

234 The ranking and screening of MOS sensors, specific for volatile organic compounds, was pe

235 and presence of gold nanoparticle to enhance sensor stability and sensitivity for label free DNA and

236 ening-induced and relaxation-induced voltage-sensor stabilization are separable.

237 mporal sequence of events leading to voltage sensor stabilization upon membrane depolarization.

238 , G546L, impeded the faster phase of voltage sensor stabilization without attenuating the slower phas

239 an impaired STING pathway.IMPORTANCE The DNA sensor STING plays pivotal role in controlling HSV-1 inf

240 novel interactions between HSV-1 and the DNA sensor STING.

241 the enzyme for blood glucose monitor enzyme sensor strips was evaluated, especially by investigating

242 lenges faced by previously reported reusable sensors, such as enzyme degradation, leaching, and hyste

243 taine methacrylamide)] grafted from the gold sensor surface and post modified with hepatitis B surfac

244 tic nanobeads-peptide moieties away from the sensor surface upon test sample dropping.

245 pCB-(DOPA)4, were applied onto a paper-based sensor surface via a simple "graft-to" immersion process

246 proximity of phospholipid molecules near the sensor surface, the LSPR sensor can discriminate fine di

247 tavidin magnetic nanoparticles (MNPs) to the sensor surface.

248 ening the way to the creation of multiplexed sensor systems.

249 (SNP) detection using highly selective BiDz sensors targeting loci associated with species typing an

250 pnia, but not by hypoxia, and express proton sensors, TASK-2 and Gpr4.

251 kinin response using the synthetic cytokinin sensor, TCSn, showed that this response occurs in cortic

252 ipid bilayer platform as well as DNA tension sensor technologies.

253 ts by promoting conformations of the voltage sensor that are associated with the channel's open state

254 results support a role for CML36 as a Ca(2+) sensor that binds to and modulates ACA8, uncovering a po

255 rt on the design and fabrication of a hybrid sensor that integrates transmission-mode localized surfa

256 towards realizing a reusable, point-of-care sensor that snugly fits around a smartphone and which do

257 his is achieved by expression of an array of sensors that detect a wide variety of viral, bacterial,

258 We provide a strategy to design ratiometric sensors that display dramatic spectral shifts by leverag

259 Instead of applying optical sensors that only use "single-mode" detection, i.e., coo

260 Here we describe 'coincidence-detecting' sensors that selectively report the phosphoinositide com

261 g units (microvilli), constituting its light sensor (the rhabdomere), and the speed and recoverabilit

262 ate the quick response of the patterned FRET sensor to 2microL of tear samples.

263 external magnet was fixed on the back of the sensor to accelerate the cleavage of the magnetic nanobe

264 develop and validate a noninvasive mobility sensor to automatically and continuously detect and meas

265 clinical effectiveness of a wearable patient sensor to improve care delivery and patient outcomes by

266 thod of using 2D plasmonic nanoparticle as a sensor to understand the polymer brush formation is appl

267 -associated structures, and the use of these sensors to follow the dynamics of phosphoinositide conve

268 us silicon diodes acting both as temperature sensors to monitor the temperature distribution and phot

269 Specifically, we have used E-AB sensors to perform the multihour, real-time measurement

270 ring and a PDMS glove with multiple embedded sensors to provide comprehensive tactile feedback of a h

271 r knowledge there are no existing MIPs-based sensors toward amphetamine-type stimulants (ATS).

272 Here, multiple sensors tracked O2 and CO2, gas pressure (DeltaP) betwee

273 approach is employed to fabricate 3D tactile sensors under ambient conditions conformally onto freefo

274 re implemented, leading to the creation of a sensor unparalleled in sensitivity and information conte

275 The sensor used the synergistic activity of the catalyticall

276 The strategy for improvement of sensors used here should be applicable for developing hi

277 ports a compact confocal LED epifluorescence sensor using a light stop with an arc-shaped aperture fo

278 st a comparable reliability of the cutaneous sensor using the zero-heat-flux method compared with eso

279 d a linear correlation of R(2)=0.998 between sensor values and reference glucose values in the range

280 The results shown the linear range of the sensor was 40.0-1100.0 femtomolar and the limit of detec

281 attering profiles as distributed temperature sensors, we demonstrated real-time monitoring of solid o

282 These attributes also make electrochemical sensors well suited for wearable applications which requ

283 FASTmiR sensors were also used to estimate the copy number range

284 Potentiometric sodium ion sensors were developed using a polyvinyl chloride (PVC)

285 oped, and the corresponding sodium selective sensors were obtained for the first time.

286 monstrate their practical applicability, the sensors were used to determine the salinity in the seawa

287 on nanostructures make the highly sensitive sensors which could indicate very low detection limit to

288 vapor-phase ethanol compared to the pure GN sensor, which has only 21% sensitivity.

289 ring with the recruitment of ASC to upstream sensors, which prevents caspase-1 activation and cytokin

290 d central aortic pressure were recorded with sensor wires.

291 ates a nitrogen-vacancy (NV) diamond quantum sensor with optical and microwave waveguide delivery ena

292 nanoparticle resonance energy transfer based sensor with polyethylenimine-coating provides high collo

293 eneral approach to compatibly interface E-AB sensors with complex biological samples.

294 form for the development of new fluorescence sensors with high selectivity for chloride.

295 e concentration in parallel to pH and oxygen sensors with integrated fluorescence detectors.

296 point-enhanced sensitivity paves the way for sensors with unprecedented sensitivity.

297 Integration of skin-like flexible sensors with wireless communication technology creates a

298 nsmembrane segment 4 (domain 1), the voltage sensor, with histidine.

299 The sensor would be useful tool for monitoring allergen leve

300 ity and multifunctionality of this impedance sensor would greatly facilitate applications in portable