ライフサイエンスコーパス: deep tissue

1 g) as a result of strong light scattering in deep tissue.

2 ed by difficulties in detecting pathogens in deep tissue.

3 ualizing and quantifying oxidative stress in deep tissue.

4 e organism in or culturing the organism from deep tissue.

5 h bioluminescent nanocapsules, especially in deep tissue.

6 llowing for quantitative targeted imaging in deep tissue.

7 of biological and pathological processes in deep tissue.

8 visualization of biological processes within deep tissue.

9 esolution fluorescence imaging in centimeter-deep tissue.

10 acquisition of high-resolution 3D images in deep tissue.

11 ress of bacteria from a superficial wound to deep tissue.

12 t, hindering efforts to visualize targets in deep tissues.

13 teria (SFB) and increased microbial loads in deep tissues.

14 cterized by painful vaso-occlusive crises in deep tissues.

15 cell lining of the vasculature to invade the deep tissues.

16 ical high resolution fluorescence imaging in deep tissues.

17 these distortions and to focus light inside deep tissues.

18 are subject to scattering and absorption in deep tissues.

19 tained bacteremia, leading to the seeding of deep tissues.

20 cilitating the study of cellular function in deep tissues.

21 two-color imaging of transgene expression in deep tissues.

22 ee-dimensional (3D) mapping of hemoglobin in deep tissues.

23 ecovery, especially for devices implanted in deep tissues.

24 ellular functions such as gene expression in deep tissues.

25 g mice we detect ~10(5) fluorescent cells in deep tissues.

26 Antares2, which offers improved signal from deep tissues.

27 ion limits their sensitivity as reporters in deep tissues.

28 d high-resolution images of blood vessels in deep tissues.

29 irection in photomedicine for using light in deep tissues.

30 the brightness needed to visualize events in deep tissues.

31 ere the respiratory tract (40%), followed by deep tissue (30%) and superficial tissues (26%), while a

32 absorbing photocages is their potential for deep tissue activation of biomolecules and phototherapeu

33 Bright gold clusters can penetrate deep tissue and can be applied in in vivo brain vessel i

34 nduce effects at nanomolar concentrations in deep tissue and can be engineered into switchable analyt

35 ection of intracellular calcium signaling in deep tissue and intact organisms remains a challenge.

36 to map a broad range of optical phenomena in deep tissue and other opaque environments.

37 therefore is particularly useful for imaging deep tissues and animals.

38 mentally overcome this resolution barrier in deep tissues and at the same time increase the focus to

39 (54.5%), followed by superficial (28.4%) and deep tissues and fluids (14.7%).

40 asive manipulation of cellular activities in deep tissues and living animals.

41 detected by mechanoreceptors of the skin and deep tissues and processed by the somatosensory system,

42 We compared overall, wound and skin, and deep-tissue and bone complications between brachytherapy

43 9; P < .001), but there was no difference in deep-tissue and bone complications.

44 tum yield of the polymer allows for in vivo, deep-tissue and ultrafast imaging of mouse arterial bloo

45 cial (stage 1 and 2) and severe (stage 3, 4, deep tissue, and unstageable) pressure injuries.

46 scent light in cells and in animals, even in deep tissues, and are suitable for multiplexed in vivo i

47 te.CONCLUSIONHIV reservoirs persisted in all deep tissues, and blood was the main source of dispersal

48 s and similar boundary structures in sterile deep tissues, and it remains unclear whether they underg

49 intestinal epithelium, disseminates into the deep tissues, and traverses biological barriers such as

50 h spatial resolution in the NIR-II region in deep tissue angiography.

51 rk presents an important step toward in vivo deep tissue applications of wavefront shaping.

52 robust optogenetic and imaging reagents for deep tissue applications.

53 ous monitoring of physiological signals from deep tissues are constrained by the depth of signal pene

54 llicles, the finding of multiple subtypes in deep tissues around a single patient's infected joint is

55 allenging to apply photomedical treatment in deep tissue as they may damage normal tissues.

56 mitations, capturing optical absorption from deep tissue at high resolution.

57 system optimized for tracking metastasis in deep tissues at high resolutions and able to detect spon

58 y tract (58.8%), followed by superficial and deep tissues at similar frequencies (21.6 and 19.6%, res

59 has limited spatial resolution in centimeter-deep tissue because of the tissue's high scattering prop

60 r where they are located in the body-even in deep tissue beds.

61 ore effectively probed using multiparametric deep-tissue bioluminescence imaging.

62 changes of CR can be detected with skin and deep tissue biopsies.

63 agnosis of infection of a chronic wound is a deep tissue biopsy culture, which is an invasive procedu

64 To invade the deep tissues, blood-borne organisms must cross the endot

65 is there limited evidence for activation of deep tissues by transcranial electric stimulation, its e

66 or mitochondria targeted PDT applications in deep tissue cancer therapy.

67 great implication in photodynamic therapy of deep-tissue cancers.

68 he life cycle of STm from growth in cells to deep-tissue colonization in a murine model of typhoid fe

69 omarkers owing to their high sensitivity and deep tissue compatibility.

70 itor the activity of this key biomarker in a deep tissue context is critical because it is associated

71 efore, we discuss the role of CGRP and SP in deep-tissue craniofacial pain and suggest that neuropept

72 e types of craniofacial pain, treatments for deep-tissue craniofacial pain such as temporomandibular

73 ) as a potential therapeutic target to treat deep-tissue craniofacial pain.

74 peutic potential, including the treatment of deep-tissue craniofacial pain.

75 iagnosis was confirmed by histopathology and deep tissue culture in all cases.

76 Understanding longterm deep tissue damage caused by UV radiation is imperative

77 lymer tattoos to detect UV radiation-induced deep tissue damage in living organisms using bioimpedanc

78 nd ionizing radiation, and cause longlasting deep tissue damage that cannot be immediately and readil

79 r-associated gold nanorods designed to allow deep tissue detection, therapy, and monitoring in living

80 r excitation power can be greatly reduced in deep tissues, deviating from the power requirement of ba

81 near-infrared window hold great promise for deep-tissue diagnosis and treatment.

82 cell lining of the vasculature to invade the deep tissues during a hematogenously disseminated infect

83 d by margin assessment of the peripheral and deep tissue edges; conjunctival mapping biopsies can fac

84 etition under growth conditions that mimic a deep-tissue environment, LacD.1 conferred a significant

85 ad different subtypes of C. acnes within the deep tissues even though the colony morphology was simil

86 ifted fluorescent Ca2+ indicator Cal-590 for deep tissue experiments in the mouse cortex in vivo.

87 Heptamethine cyanine dyes enable deep tissue fluorescence imaging in the near infrared (N

88 Due to the confocal pinhole, deep tissue fluorescence imaging is not practical.

89 orm with exceptional potential to facilitate deep-tissue fluorescence-based imaging for in vivo diagn

90 Modern technologies enable deep tissue focusing of nanosecond pulsed electric field

91 The reported technique provides a deep tissue-focusing solution with high efficiency, reso

92 nt for effective spirochete dissemination to deep tissues for as long as 3 weeks postinoculation and

93 P receptor protein) and cdt (colonization of deep tissues) genes have been constructed and characteri

94 watt levels of power can be transferred to a deep-tissue (>5 cm) microimplant for both complex electr

95 robes that can monitor disease biomarkers in deep tissue has the potential to replace invasive medica

96 resonance imaging (MRI), which penetrates to deep tissues, has been limited by single reporter visual

97 -II, 1000-1700 nm) is a promising method for deep-tissue high-resolution optical imaging in vivo main

98 e an approach employing X-ray activation for deep-tissue hydrogel formation, surpassing all previous

99 tinociceptive effect on mechanical, cold and deep tissue hyperalagesia in both genders.

100 xicity profile that can be readily imaged in deep tissues, ICG may have significant utility for clini

101 l networks to augment live-imaging data with deep-tissue images taken on fixed samples.

102 sought to establish: (a) multimodal 2-photon deep tissue imaging and 3-dimensional analysis of the di

103 ch as blood, mucus, and vitreous) as well as deep tissue imaging and control in vivo.

104 licated wavefront distortions encountered in deep tissue imaging and provide compensations for not on

105 However, deep tissue imaging at the single molecule sensitivity h

106 forebrain organoids confirms the successful deep tissue imaging capabilities of both Lyso-2arm and M

107 Its deep tissue imaging capability leads to less sectioning,

108 ton excitation can be potentially useful for deep tissue imaging for future in vivo studies.

109 hniques and use of two-photon microscopy for deep tissue imaging have enabled observation of neuronal

110 lled drug delivery of large biomolecules and deep tissue imaging make this system an excellent theran

111 3D deep tissue imaging of the failing RV in PAB mice, pulmo

112 inear optical microscopy has enabled in vivo deep tissue imaging on the millimeter scale.

113 ight from 900 to 1400 nm, which is ideal for deep tissue imaging owing to minimized light scattering

114 multi-photon excitation system in enhancing deep tissue imaging resolution.

115 molecule tracking, early disease diagnosis, deep tissue imaging, and drug delivery and therapies.

116 r neurons, targeted photodynamic therapy and deep tissue imaging.

117 pecificity, and some lack the capability for deep tissue imaging.

118 ous fluorophores and potentially facilitates deep tissue imaging.

119 are lacking imaging contrast properties for deep tissue imaging.

120 because they offer high resolution and allow deep tissue imaging.

121 tile nanoparticulate system for simultaneous deep-tissue imaging and drug molecule release in vivo is

122 rotein tags and components of biosensors for deep-tissue imaging and multicolour microscopy.

123 g efficacy of biliverdin-dependent tools for deep-tissue imaging and optogenetic manipulation.

124 high-energy light excitation, can facilitate deep-tissue imaging and sensing applications.

125 n of smart MRI nanoprobes ideally suited for deep-tissue imaging and target-specific cancer diagnosis

126 Our results set the stage for a range of deep-tissue imaging applications in biomedical research

127 current fluorescent calcium indicators limit deep-tissue imaging as well as simultaneous use with oth

128 e-photon microscopy is highly beneficial for deep-tissue imaging because of the long excitation wavel

129 optoacoustic tomography (MSOT) developed for deep-tissue imaging in humans could enable the clinical

130 Separately, orange-red FPs are useful for deep-tissue imaging in mammals owing to the relative tis

131 ity of oncolytic virotherapy, a noninvasive, deep-tissue imaging modality is needed.

132 NIR-II fluorescence enables deep-tissue imaging with micrometric resolution in anima

133 romising applications in cellular labelling, deep-tissue imaging, assay labelling and as efficient fl

134 l imaging holds promise for high-resolution, deep-tissue imaging, but is limited by autofluorescence

135 Red GECIs facilitate deep-tissue imaging, dual-color imaging together with GF

136 Despite advances in deep-tissue imaging, many optical methods struggle to ac

137 nfrared fluorescent proteins (iRFP) to allow deep-tissue imaging.

138 is the current method of choice for in vivo deep-tissue imaging.

139 n their high specificity and sensitivity and deep-tissue-imaging capability.

140 mic particles, demonstration of operation in deep tissue in large animal models and readout with a sm

141 focused ultrasound can be used to stimulate deep tissue in the brain.

142 ontrolling a variety of protein functions in deep tissue in the future.

143 loaded with anticancer microRNAs (miRNAs) to deep tissues in a pig model.

144 s the migration of injected DCs to small and deep tissues in mice and humans.

145 n subcutaneous mouse tissue, and 5.7-fold in deep tissues in mice.

146 tial information on subcellular processes of deep tissues in vivo has been a long-standing challenge

147 dout of cellular and organismal processes in deep tissues in vivo.

148 PEGylated Ag(2)S superdots enable deep-tissue in vivo imaging at low excitation intensitie

149 d genetically encoded fluorescent probes for deep-tissue in vivo imaging.

150 We conclude that the deep tissue included in our transplants is important for

151 Penetration of light through deep tissues, including the liver and spleen, was also o

152 a organisms recovered from the intestine and deep tissues indicate local and systemic infections.

153 tients experience recurrent episodes, due to deep tissue infection and treatment-resistant bacterial

154 Innate immune defense against deep tissue infection by Staphylococcus aureus is orches

155 Efficacy was also demonstrated in the deep-tissue infection model, where Hu-1.4/1.1 bound to S

156 intoxication model, as well as in sepsis and deep-tissue infection models.

157 ted in mice in sepsis, superficial skin, and deep-tissue infection models.

158 Of the 133 wound infections, 89 (67.1%) were deep-tissue infection, occurring at a median of 8 (range

159 hylococcus aureus bacteremia associated with deep tissue infections, such as pyomyositis, osteomyelit

160 that high molecular mass HA facilitates GAS deep tissue infections, whereas the generation of short-

161 ecological tracts and less frequently causes deep tissue infections.

162 ld be standard practice in the assessment of deep-tissue infections in patients with drainage cathete

163 Most PTSAgs cause TSS in deep-tissue infections, whereas only TSS toxin 1 (TSST-1

164 icans hyphal invasion coupled with S. aureus deep tissue infiltration.

165 y organized nociceptive responses, orofacial deep tissue injury also is coupled to somatovisceral and

166 /Vc-RVM pathway is activated after orofacial deep tissue injury and plays a critical role in facilita

167 d descending pain modulation after orofacial deep tissue injury.

168 /Vc transition zone in response to orofacial deep tissue injury.

169 ulcer categorized as stages II, III, and IV; deep tissue injury; or unstageable.

170 Deep tissue intravital and organ culture microscopy stud

171 ry of previous debulking surgery, absence of deep tissue invasion, minimal residual disease after sur

172 ecific plasmids, pMT1, is thought to promote deep tissue invasion, resulting in more acute onset of s

173 ultivariable logistic regression showed that deep tissue involvement had the strongest association wi

174 ith musculoskeletal features, with a lack of deep tissue involvement having a negative predictive val

175 Of these, 7 (44%) had deep tissue involvement.

176 nts and separately transplanted we find that deep tissue is able to induce the formation of ectopic a

177 xternal magnetic fields (less than 10 mT) in deep tissue is demonstrated for the first time.

178 ific imaging with high spatial resolution in deep tissue is often considered the grand challenge of o

179 rythema, purulent exudate, separation of the deep tissues, isolation of bacteria, and duration of inp

180 adroxil, an antibiotic, by >16-fold into the deep tissue layers of the skin without inducing skin irr

181 d recent applications of such nanosystems in deep tissue light-mediated therapeutics.

182 Combining deep tissue light-sheet microscopy for in toto live visu

183 Deep-tissue live imaging presents a particular challenge

184 linical disease more accurately, however the deep tissue location of these tumors makes longitudinal

185 iplexed SERS signals in both superficial and deep tissue locations at least an order of magnitude fas

186 Current deep tissue microscopy techniques are mostly restricted

187 den was observed in the superficial skin and deep-tissue models.

188 g the autofluorescence/scattering issues for deep tissue molecular imaging.

189 This article presents noninvasive deep-tissue molecular images in a living subject with th

190 MRI sensor offers the exciting potential for deep-tissue monitoring of beta-cell function in vivo dur

191 ented light-scattering ambiguity inherent to deep-tissue multifocal two-photon microscopy.

192 We present a deep tissue multiplexed functional imaging method that p

193 In deep tissues, NIR BLI enabled detection of as low as 10(

194 These insights may help pave the way to deep-tissue non-invasive mapping of microvascular blood

195 es to revolutionize biophotonics by enabling deep tissue noninvasive optical imaging, manipulation, a

196 is work is an important step towards in vivo deep tissue noninvasive optical imaging, optogenetics an

197 esent a minimally invasive system to monitor deep-tissue O(2) that reports continuous real-time data

198 cence microscopy is a powerful technique for deep-tissue observation of living cells.

199 hile maintaining high spatial resolution for deep tissue observations.

200 lent optical contrast and high resolution in deep-tissue observations, far beyond the penetration lim

201 nt subtypes of C. acnes were observed in the deep tissues of a single patient.

202 enables monitoring of gene expression in the deep tissues of living subjects.

203 old in cells and faster 6-fold activation in deep tissues of mice.

204 w for assaying PPIs both in cell culture and deep tissues of small animals.

205 icularly challenging for oligonucleotides in deep tissues of the CNS.

206 g blood vessel structure is reconstructed by deep tissue optical imaging in serial sectioning techniq

207 transparent, presenting major challenges for deep tissue optical microscopy.

208 atter structures that are ideally suited for deep-tissue optical imaging and sensitive diagnostic app

209 IR-IIb) (1,500-1,700 nm) window is ideal for deep-tissue optical imaging in mammals, but lacks bright

210 ng in biomedical applications while enabling deep-tissue optical penetration, and single-molecule res

211 Melanin production also facilitated deep tissue optoacoustic imaging as well as MRI.

212 APNO-1080, a NIR-II NO-responsive probe for deep-tissue PA imaging.

213 Owing to its high spatial resolution in deep tissues, PA imaging holds great potential for biome

214 ss-CyFaP is an accessible contrast agent for deep tissue PAI in the NIR-II window.

215 esponse to an intensity-controlled sustained deep-tissue pain challenge with positron emission tomogr

216 ciency of existing PDT drug molecules in the deep-tissue-penetrable near-infrared (NIR) region has be

217 bility of phototherapy, necessitating use of deep tissue penetrating near-infrared (NIR) to visible l

218 gical targets in vivo, with the advantage of deep tissue penetration and fewer interactions with the

219 gy and pathology at the molecular level with deep tissue penetration and fine spatial resolution.

220 Further, the deep tissue penetration and high spatial and temporal re

221 ear-infrared window (1.0-1.7 mum) can afford deep tissue penetration and high spatial resolution, owi

222 vo visualization of molecular processes with deep tissue penetration and high spatiotemporal resoluti

223 ow here that the use of NIR radiation allows deep tissue penetration and inhibition of tumor growth o

224 The deep tissue penetration and low autofluorescence backgro

225 sing for in vivo fluorescence imaging due to deep tissue penetration and low tissue autofluorescence.

226 ypass the biological barriers, thus allowing deep tissue penetration and the accumulation of the nano

227 ectral region confer the advantage of having deep tissue penetration capacity.

228 Noninvasive optical imaging with deep tissue penetration depth and high spatiotemporal re

229 indicate that there is indeed a pH-dependent deep tissue penetration in ex vivo tumor multicellular s

230 maging owing to the low autofluorescence and deep tissue penetration in the near-infrared region beyo

231 ity of utilizing these assemblies to achieve deep tissue penetration in tumors.

232 significance of reduced autofluorescence and deep tissue penetration of light in the NIR region, the

233 ttractive for complex applications requiring deep tissue penetration or dual-wavelength control in co

234 Multiphoton microscopy allows for deep tissue penetration with relatively minor phototoxic

235 medical applications like photopharmacology (deep tissue penetration).

236 all size of the complex small, desirable for deep tissue penetration, and the aptamer block accessibl

237 (NIR) light, with its low phototoxicity and deep tissue penetration, holds particular promise.

238 red window (NIR-II, 1,000-1,700 nm) features deep tissue penetration, reduced tissue scattering, and

239 osolic uptake into targeted cancer cells and deep tissue penetration.

240 hree-dimensional sub-cellular resolution and deep tissue penetration.

241 Magnetic resonance imaging (MRI) offers deep tissue penetration.

242 ative visualization with high resolution and deep tissue penetration.

243 ric mapping of photoabsorbing molecules with deep tissue penetration.

244 and be excitable by light illuminations with deep tissue penetration.

245 bility, low auto-fluorescent background, and deep tissue penetration; however, UCNPs also suffer from

246 tion offers the opportunity to combine NIR's deep-tissue penetration and biocompatibility with the pr

247 are pivotal for biomedical imaging, offering deep-tissue penetration and high signal-to-noise ratios

248 color three-photon fluorescence imaging with deep-tissue penetration in the living mouse brain using

249 However, the limited deep-tissue penetration of visible light needed for QD a

250 IIb window) affords high spatial resolution, deep-tissue penetration, and diminished auto-fluorescenc

251 o their exceptional selectivity profiles and deep-tissue photoacoustic imaging capabilities, these pr

252 To facilitate deep-tissue photoactivation with near-infrared light, we

253 can be activated by molecules of interest in deep tissue, providing a basis for mapping nanomolar-sca

254 nd use in a range of applications, including deep-tissue quantum enhanced sensing and individual opti

255 Diffuse optical flowmetry (DOF) assesses deep tissue RBC dynamics by measuring coherent fluctuati

256 wo-photon microscopy, a method of choice for deep-tissue recording.

257 noninvasive detection of free metal ions in deep tissue remains a formidable challenge.

258 The inability to sample deep-tissue reservoirs in individuals living with human

259 Thus, injection of capsaicin into deep tissues results in a longer-lasting mechanical allo

260 introduction of GAS into the pharynx or into deep tissues results in rapid induction of has operon ex

261 the masseter muscle, an injury of orofacial deep tissue, results in a widespread change in neuronal

262 uscle pain was shown to be effective for the deep tissue sensibility in healthy subjects.

263 Within deep tissue sites, extracellular bacterial pathogens oft

264 ometric imaging of both cells in culture and deep-tissue small animal tumor models and validate their

265 have an increased number of primary tumors, deep tissue spread, perineural and lymphatic invasion, r

266 are, in principle, considered inadequate for deep tissue stimulation unless accompanied by optic fibe

267 CANCAN-ES is promising for non-invasive deep tissue stimulation, either alone or combined with o

268 ng, long-term in vitro and in vivo labeling, deep tissue structure mapping and single particle invest

269 Ca(2+) at 940 nm, GCaMP3fast is suitable for deep tissue studies.

270 (FFA) tracer suitable for in vivo imaging of deep tissues such as the heart.

271 e exhibited improved performance for imaging deep-tissue targets in live mice.

272 roducing substantially brighter signals from deep tissues than firefly luciferase and other biolumine

273 be detected with high positional accuracy in deep tissues, that molecular specificities of different

274 Non-invasive deep-tissue three-dimensional optical imaging of live ma

275 e changes over time, and we combined it with deep-tissue time-lapse imaging based on fast two-photon

276 lease of compounds, including potentially in deep tissue, to achieve tailored personalized therapy.

277 the hierarchical barriers from injection to deep tissue transduction.

278 iques in the ideal NIR-IIb (1,500-1,700 nm) 'deep-tissue-transparent' sub-window.

279 titude of applications in wireless displays, deep tissue treatment, sensing, and imaging.

280 e photomodification is crucial to facilitate deep-tissue treatments.

281 CRET can effectively detect MPO activity at deep tissue tumor foci due to tumor development-associat

282 assessments of homeostatic dysregulation in deep tissues typically require expensive imaging techniq

283 afterglow or photoacoustic signals, enabling deep-tissue ultrasensitive imaging of biological tissues

284 h to high-resolution optical imaging through deep tissues, useful for a wide range of applications fr

285 method for multi-color, multi-RNA imaging in deep tissues using single-molecule hybridization chain r

286 ess may facilitate parasite sequestration in deep tissue vasculature.

287 roach to deliver light (termed 'deLight') in deep tissue via systemically injected mechanoluminescent

288 ), for high-resolution imaging in centimeter-deep tissues via fluorescence contrast.

289 hypoalgesia that occurs after injection into deep tissue was reversed by spinal blockade of adenylate

290 tered centers of replicating bacteria within deep tissues, where peripheral bacteria express the NO-d

291 devices are unable to sense biomolecules in deep tissues, which have a stronger and faster correlati

292 pplications of C-dots for in vivo imaging in deep tissues, which is currently not possible using conv

293 ageous therapy alternative that may activate deep tissues while avoiding drug side-effects.

294 One patient had four subtypes in the deep tissues, while four patients had two different subt

295 Fluorescence imaging in deep tissue with high spatial resolution is highly desir

296 , enabled us to image fluorescent targets in deep tissue with spatial resolution beyond the acoustic

297 Fluorescence imaging in centimeter-deep tissues with high resolution is highly desirable fo

298 new opportunities for biomedical imaging of deep tissues with improved contrast.

299 howed reduced fibrosis in both cutaneous and deep tissue wounds, which was accompanied by a reduction

300 ellular infiltration in cutaneous but not in deep tissue wounds.