ライフサイエンスコーパス: microbubble

1 uction-replenishment DCE US with nontargeted microbubbles.

2 after intravenous injection of 2x10(8) lipid microbubbles.

3 ound treatment performed without circulating microbubbles.

4 mpared to commercially available Definity(R) microbubbles.

5 using focused ultrasound in combination with microbubbles.

6 treaming flow generated by ultrasound-driven microbubbles.

7 se fashion by ultrasound and ultrasound with microbubbles.

8 near pressure-to-destruction response of the microbubbles.

9 following intravenous (IV) administration of microbubbles.

10 psies after injection of sulfur hexafluoride microbubbles.

11 ystemically administered OV co-injected with microbubbles.

12 mes (with and without gas) and lipid-shelled microbubbles.

13 rovascular structure and blood flow by using microbubbles.

14 d by liposomes that were not associated with microbubbles.

15 mpanies explosive growth and collapse of the microbubbles.

16 e maintaining echoes from very slowly moving microbubbles.

17 index, 0.6 or 1.3) or ultrasound with lipid microbubbles (2x10(8) IV).

18 diated augmentation in flow was greater with microbubbles (3- and 10-fold higher than control for mec

19 cal, cell-membrane-based mechanisms by which microbubble acoustic behaviors cause acute and sustained

20 on (PCD) is a method proposed to monitor the microbubble activity during ultrasound exposure.

21 ncement in addressable focus resolution in a microbubble aggregate target by exploiting the nonlinear

22 US with clinical-grade VEGFR2-targeted microbubbles allows detection of small foci of PDAC in t

23 imensional super-resolution US imaging using microbubbles allows noninvasive nonionizing visualizatio

24 ile tumours treated with separate devices or microbubbles alone were respectively 45% and 112% larger

25 Here we apply these microbubbles along with low intensity pulsed ultrasound

26 offer possibilities of novel applications of microbubbles, already clinically approved for contrast e

27 The acoustic energy emitted from the microbubbles also predicted the delivered dose (r = 0.97

28 e of single-beam acoustical tweezers to trap microbubbles, an important class of biomedically relevan

29 d PVAC catheters in swine is associated with microbubble and microembolus production.

30 tly cationic microbubbles were evaluated for microbubble and ultrasound-mediated enhancement of non-v

31 l growth factor receptor 2 (VEGFR2)-targeted microbubbles and (b) 3D dynamic contrast material-enhanc

32 sed ultrasound treatment after injections of microbubbles and a labeled model drug, while three contr

33 simultaneous trapping of nanoparticle-loaded microbubbles and activation with an independent acoustic

34 ies vary widely across the population of the microbubbles and are influenced by the shell composition

35 y amplified by the intravascular presence of microbubbles and can reverse tissue ischemia.

36 achievable with both commercially available microbubbles and custom-made nanobubbles under acoustic

37 n vivo, followed by intravenous injection of microbubbles and FUS sonication at the brainstem.

38 samples result in the generation of hydrogen microbubbles and hydroxyl ions for DPP degradation.

39 P < 0.001) using MB(VEGFR2) than nontargeted microbubbles and imaging signal significantly decreased

40 Recently, researchers have begun using microbubbles and liposomes to encapsulate such gasses fo

41 t advances in therapeutic gas delivery using microbubbles and liposomes.

42 ays of culture in the presence of 0.5% (v/v) microbubbles and LIPUS in contrast to 18% with LIPUS alo

43 fuse quickly into the water/air interface of microbubbles and react with dissolved O(2) to produce si

44 ultrasound-induced activities of cell-bound microbubbles and the actin cytoskeleton contractile forc

45 nnovative formulation composed of gas-filled microbubbles and the pathogen-derived protective protein

46 MR image-guided focused ultrasound (FUS) and microbubbles and using highly compact "brain penetrating

47 robubbles, (b) bolus DCE US with nontargeted microbubbles, and (c) destruction-replenishment DCE US w

48 This method ultrasonically destroys microbubbles, and measures the wavefront change to compu

49 rescence, contrast-enhanced ultrasound using microbubbles, and superparamagnetic iron oxide nanoparti

50 Therefore, integrating LIPUS and microbubbles appears to be a promising strategy for enha

51 heir large 1-10 microm size, applications of microbubbles are confined to the blood vessels.

52 e treatment, uniform serum concentrations of microbubbles are important for consistent BBB opening.

53 Bolus intravenous injections of microbubbles are standard practice, but dynamic influx a

54 Lipid-coated microbubbles are used to enhance ultrasound imaging and

55 Encapsulated microbubbles are well established as highly effective co

56 ing cytometry technique using functionalized microbubbles as an actuatable, biocompatible, and multif

57 , we introduce an ultra-sensitive and facile microbubbling assay for the quantification of protein bi

58 work provides the proof-of-principle of the microbubbling assay with a digital readout as an ultra-s

59 Bolus injections of microbubbles at 4 muL/kg were tested for each sonication

60 PFH-NDs containing 5% w/v IONP converted to microbubbles at 42 degrees C at 2.18 MI, which is just a

61 oil, and those responsible for stability of microbubbles at the air-water interface, facilitating it

62 simultaneously concentrate and activate the microbubbles at the target site.

63 hly concentrated levels of nucleic acids and microbubbles at the tissue of interest which upon ultras

64 molecularly targeted US with VEGFR2-targeted microbubbles, (b) bolus DCE US with nontargeted microbub

65 tumor functional and molecular imaging using microbubble-based ultrasound and ultrasound-mediated opt

66 dentified distinct regimes of characteristic microbubble behaviors: stable cavitation, coalescence an

67 ion molecule-1-targeted and rhodamine-loaded microbubbles bound 8x more efficient (P=0.016) to stimul

68 means of first-pass kinetics of nontargeted microbubbles (BR1, BR38; Bracco, Geneva, Switzerland) an

69 co, Geneva, Switzerland) and VEGFR2-targeted microbubbles (BR55, Bracco) before and 4, 7, and 14 days

70 trasound without any contrast agents such as microbubbles, bringing a single-cell level targeting and

71 e of a propagating vortex beam can confine a microbubble by forcing low-amplitude, nonspherical, shap

72 flow augmentation produced by ultrasound and microbubbles by 70% (P<0.01), whereas inhibition of aden

73 The ability to stabilize gas microbubbles can be finely tuned through variation of th

74 At the end of reaction, the microbubbles can be removed from the reaction systems th

75 Although microbubbles can boost the diagnostic value of ultrasono

76 pon applying ultrasound, nanoparticle-loaded microbubbles can deposit nanoparticles onto cells grown

77 nhanced ultrasound with molecularly targeted microbubbles can detect early-stage cancer through the v

78 rated that ultrasound alone or combined with microbubbles can efficiently increase cell membrane perm

79 Focused ultrasound (FUS) combined with microbubbles can enhance the permeability of the BTB in

80 Focused ultrasound (FUS) in combination with microbubbles can non-invasively open the BBB in a target

81 Overall, these data suggest that FUS and microbubbles can not only increase DOX delivery across t

82 her, our data show that ultrasound-activated microbubbles can safely deliver high concentrations of d

83 ultrasound (FUS) exposure in the presence of microbubbles can temporally open the blood-brain barrier

84 We prepared microbubbles carrying hydrogen sulfide (hs-MB) with diff

85 s study demonstrates that ultrasound induced microbubble cavitation can be a useful tool for delivery

86 Ultrasound induced microbubble cavitation can cause enhanced permeability a

87 ted the platform on phantoms to optimize the microbubble cavitation dose based on acoustic parameters

88 Therapeutic ultrasound using microbubble cavitation to increase muscle perfusion reli

89 icrobubble oscillations, which can influence microbubble-cell interactions.

90 t cancer cells by using doxorubicin-liposome-microbubble complexes (DLMC) assisted by ultrasound (US)

91 .81MPa; 10ms bursts; 1Hz PRF; 60s duration), microbubble concentration (Definity, 10mul/kg), and the

92 length, and pulse repetition frequency) and microbubble concentration in a tissue mimicking phantom.

93 e imaging to optimize the acoustic pressure, microbubble concentration, treatment duration, DNA dosag

94 sures were conducted with different Definity microbubble concentrations at various acoustic pressures

95 mage-guided delivery of DNA-BPN with FUS and microbubbles constitutes a safe and non-invasive strateg

96 mL of Optison (GE Healthcare, Oslo, Norway) microbubble contrast agent solution (perflutren protein-

97 k rarefaction pressure) in the presence of a microbubble contrast agent.

98 Additionally, microbubble contrast agents are improving the sensitivit

99 d increases in perfusion can be augmented by microbubble contrast agents that undergo ultrasound-medi

100 Microbubble contrast agents that undergo ultrasound-medi

101 acterization of focal liver lesions and uses microbubble contrast agents to increase signal backscatt

102 essure to induce cavitation of lipid-shelled microbubble contrast agents.

103 intensity curves obtained after injection of microbubble contrast material 6 weeks after beginning ph

104 of 5 x 10(7) clinical-grade VEGFR2-targeted microbubble contrast material.

105 nd localization microscopy, where individual microbubbles (contrast agents) are detected and tracked

106 pathways in aquatic systems, the presence of microbubbles could alter the resulting CH4 and perhaps C

107 Ultrasonic excitation of microbubbles could elicit a rapid and sustained reactive

108 They suggest that heated microbubbles could have hosted the first cycles of molec

109 sound pulses to actuate functionalized lipid microbubbles covalently attached to single live cells to

110 We demonstrate that ULM microbubble data processing methods, applied to images a

111 the small vessels was estimated by tracking microbubbles, demonstrating the potential of this techni

112 tic pressure at levels where no such sign of microbubble destabilization occurred resulted in safe BB

113 rred most significantly at pressures causing microbubble destruction (450kPa and 600kPa); by increasi

114 oparticles (aFGF-NP) and ultrasound-targeted microbubble destruction (UTMD) technique for DCM prevent

115 We used ultrasound-targeted microbubble destruction (UTMD) to locally deliver microR

116 article (NP) carrier and ultrasound-targeted microbubble destruction (UTMD) was reported the first ti

117 stage strategy combining ultrasound-targeted microbubble destruction (UTMD) with CGT nanotherapy.

118 Conclusion The combination of US-triggered microbubble destruction and transarterial radioembolizat

119 that delivery of H2S by ultrasound targeted microbubble destruction attenuates myocardial ischemia-r

120 Ultrasound targeted microbubble destruction has become a promising tool for

121 nal GRK4 expression, via ultrasound-targeted microbubble destruction, decreased ETBR phosphorylation

122 ventional approach using ultrasound-targeted microbubble destruction-mediated delivery of phosphoroth

123 tic transthoracic ultrasound and intravenous microbubbles dissolve thrombi (sonothrombolysis) and inc

124 The protocol includes the preparation of a microbubble-DNA mix and in vivo sonoporation under ultra

125 clic, paired displacements of integrin-bound microbubbles driven by the attractive secondary acoustic

126 rinsic physical timescales (microseconds for microbubble dynamics and seconds to minutes for local ma

127 at expansion is constrained, suggesting that microbubble echoes would be difficult to detect in such

128 orces to individual cells via integrin-bound microbubbles, enabling a creep test for measuring cellul

129 nt a new technique, time-reversed ultrasound microbubble encoded (TRUME) optical focusing, which can

130 sults demonstrated that combining LIPUS with microbubbles enhanced glycosaminoglycan (GAG) production

131 P), administered by an ultrasound-guided and microbubble-enhanced delivery approach in doxorubicin-re

132 that ultrasound could be used to guide local microbubble-enhanced sonoporation of plasmid DNA.

133 ts bear great promise for the development of microbubble-enhanced sonoporation-induced gene therapies

134 In this work, we demonstrate that microbubble-enhanced ultrasound can similarly improve ge

135 ent disruption of the blood-brain barrier by microbubble-enhanced ultrasound has been used to success

136 emporary disruption of the choroid plexus by microbubble-enhanced ultrasound is therefore a viable wa

137 ramped pulse exposure scheme for optimizing microbubble excitation to improve sonoporation gene tran

138 metry (Gibbs films), Langmuir monolayers and microbubble experiments.

139 We hypothesized that the destabilization of microbubbles exposed to a critical level of ultrasound w

140 We quantified the dynamic activities of microbubbles exposed to pulsed ultrasound and the result

141 ith 50mug luciferase plasmid DNA and 5x10(5) microbubbles followed by ultrasound treatment at 1.4MHz,

142 Focused ultrasound combined with microbubble for blood-brain barrier disruption (FUS-BBBD

143 erial-enhanced (DCE) US by using nontargeted microbubbles for assessment of antiangiogenic treatment

144 roplets capable of vaporization into gaseous microbubbles for imaging or therapy.

145 ound coupled with intravenously administered microbubbles (FUS) has been proven an effective, non-inv

146 latform such as an ultrasound contrast agent microbubble has the potential to be a minimally-invasive

147 in the presence of systemically administered microbubbles has been shown to locally, transiently and

148 Focused ultrasound with microbubbles has been used to noninvasively and selectiv

149 Ultrasound application in the presence of microbubbles has shown great potential for non-viral gen

150 More recently, drug-loaded microbubbles have been developed and the load release by

151 Oxygen-loaded magnetic microbubbles have been explored as a targeted delivery v

152 Lipid-shelled microbubbles have been used in ultrasound-mediated drug

153 Ultrasound-triggered drug-loaded microbubbles have great potential for drug delivery due

154 The collapse of microbubbles (i.e., microcavitation) may induce a mechan

155 lux is possibly explained by the presence of microbubbles in the lake's surface layer.

156 Ablation with the PVAC showed fewest microbubbles in the unipolar mode (P=0.012 versus bipola

157 Previous optical studies of microbubbles in vessels of approximately 20 microns have

158 wideband echoes are detected from individual microbubbles in vessels with flow rates below 2 mm/s.

159 of 120 mg PFH/kg, converted into detectable microbubbles in vivo 5 h, but not shortly after injectio

160 ow), ultrasound (mechanical index, 1.3) with microbubbles increased perfusion by 2-fold to a degree t

161 s the use of ultrasound to burst circulating microbubbles inducing transient permeabilization of surr

162 ultrasound transducer during an intravenous microbubble infusion (sonothrombolysis) can restore epic

163 ostic transducer, combined with a commercial microbubble infusion, can prevent microvascular obstruct

164 s have demonstrated that, during intravenous microbubble infusion, high mechanical index (HMI) impuls

165 ing ultrasound transducer with an integrated microbubble injection tube is more advantageous for effi

166 ls treated with DNA injection alone, DNA and microbubble injection, or DNA injection and ultrasound t

167 de range of protrusion angles, theta, of the microbubbles into the flow, using a microparticle image

168 Focused ultrasound (FUS) combined with microbubbles is a non-invasive method for targeted, reve

169 uced blood-brain barrier (BBB) opening using microbubbles is a promising technique for local delivery

170 Insonation of microbubbles is thought to facilitate two mechanisms for

171 asound (FUS), when combined with circulating microbubbles, is an emerging noninvasive method to tempo

172 ane inducing endocytotic uptake, and second, microbubble jetting inducing the formation of pores in t

173 infusions were performed at rates of 7.2 ul microbubbles/kg/min or below, we were able to obtain con

174 Microbubble kinetics was investigated over the course of

175 und the sample and, along with the generated microbubbles, lead to greatly enhanced fluid transport a

176 This technology is extended to microbubble-liposome conjugates, which exhibit a stronge

177 Magnetically responsive microbubbles (MagMBs), consisting of an oxygen gas core

178 ol based on harmonic emissions of stimulated microbubbles may be important for facilitating the clini

179 und (FUS) in conjunction with contrast agent microbubbles may be used to non-invasively and temporari

180 These microbubbles may originate from atmospheric bubble entra

181 Microbubble (MB) mediated sonoporation offers a potentia

182 Microbubbles (MB) bearing antibodies targeting lymphocyt

183 stemic infusion of ultrasound contrast agent microbubbles (MB) causes localized blood-brain barrier (

184 We here investigated microbubbles (MB) functionalized with the selectin ligan

185 ert domain receptor [KDR] -targeted contrast microbubble [MBKDR]) that is targeted at the KDR, one of

186 yl N-azidoacetylmannosamine (Ac4 ManAz) from microbubbles (MBs) and its metabolic expression in the c

187 high intensity focused ultrasound (HIFU) and microbubbles (MBs) can improve tumor drug delivery from

188 rasound (FUS) in conjunction with gas-filled microbubbles (MBs) has emerged as a noninvasive modality

189 Microbubbles (MBs) have been shown to create transient o

190 US-activated cavitation agents such as microbubbles (MBs) have been used to release therapeutic

191 Dual P- and E-selectin-targeted microbubbles (MBs) have previously been used for ultraso

192 focused ultrasound (FUS) with intravascular microbubbles (MBs) is able to locally and reversibly dis

193 based on ultrasound-activated lipid-shelled microbubbles (MBs) targeted to inflamed mesenteric endot

194 Background US contrast agents are gas-filled microbubbles (MBs) that can be locally destroyed by usin

195 By acoustically actuating integrin-bound microbubbles (MBs) to live cells, ATC increased the surv

196 ubicin (DOX)-liposome (DL) to the surface of microbubbles (MBs) via the biotin-avidin linkage.

197 arginine-grafted bioreducible polymer (ABP), microbubbles (MBs), and ultrasound technology (US) we we

198 e the use of oxygen-loaded, lipid-stabilised microbubbles (MBs), decorated with a Rose Bengal sensiti

199 d on localization and tracking of individual microbubbles (MBs), offers unprecedented microvascular i

200 When enhanced by the cavitation of microbubbles (MBs), US exposure can induce sonoporation

201 blood cells using gas-filled buoyant immuno-microbubbles (MBs).

202 delivery efficiency since they determine the microbubble mechanical properties, circulation persisten

203 and validated a platform for ultrasound and microbubble-mediated delivery of FDA-approved pegylated

204 Cavitation-facilitated microbubble-mediated focused ultrasound therapy is a pro

205 The goal of microbubble-mediated sonoporation is to enhance the upta

206 e report the development of an intravascular microbubble-mediated sonothrombolysis device for improvi

207 Either a microbubbled mixture of air (1.0-4.0 mL), blood, contras

208 time, offered evidence directly linking the microbubble monolayer shell with their efficacy for drug

209 tMBs) or that are not targeted (non-targeted microbubbles, ntMBs).

210 verall, the use of bolus injections and high microbubble numbers resulted in increased gene expressio

211 The size and number of microbubbles observed during ablation ranged from 30 to

212 Microbubbles of different surface charges (neutral, slig

213 eered a BBE model to determine the effect of microbubbles on the structural and functional changes in

214 n conjunction with systemically administered microbubbles, opens the BBB locally, reversibly and non-

215 onoporation by high-intensity ultrasound and microbubbles or cavitation agents.

216 Cerebral embolization of air microbubbles or microparticulate debris that approximate

217 .3-3 W/cm(2)), sonoporation may be caused by microbubbles oscillating in a stable motion, also known

218 the way for therapeutic ultrasound mediated microbubble oscillation and has shown that this approach

219 s between ultrasound-stimulated encapsulated microbubble oscillation physics and the resulting cellul

220 We show that there exists a microbubble oscillation-induced shear-stress threshold,

221 V in vivo, but its use to induce cavitation, microbubble oscillations, for enhanced OV tumor extravas

222 ource of acoustic reflections and aspherical microbubble oscillations, which can influence microbubbl

223 imulated cells and 14x more than nontargeted microbubbles (P=0.016).

224 ly acoustic powering to position and actuate microbubbles paves the way toward controlled delivery of

225 arly targeted US signal with VEGFR2-targeted microbubbles, peak enhancement, and rBV significantly de

226 allergen, phospholipase A2, associated with microbubbles (PLA2denat -MB) in a mouse model of honeybe

227 A dispersion of negatively charged microbubble/positively charged microdroplet clusters are

228 ective method to improve drug uptake through microbubble potentiated enhancement of microvascular per

229 es to prevent accumulation or circulation of microbubbles produced by the chemical indication reactio

230 Focused ultrasound combined with gas-filled microbubbles provides a noninvasive way to improve the p

231 The resultant microbubble reaction systems exhibit significant catalys

232 ase reactions can be transformed to H2 or O2 microbubble reaction systems.

233 8 and 1 mL/min) showed significantly reduced microbubbles retention, by 38% (P=0.03) and 55% (P=0.03)

234 The physicochemical properties of the microbubble shell could affect the delivery efficiency s

235 owed that a relatively small increase in the microbubble shell rigidity resulted in a significant inc

236 cosity distributions exist within individual microbubble shells even with a single surfactant compone

237 r, a C2F5-labeled nitrosoimidazole (EF5), in microbubble shells.

238 y of US equipment in terms of sensitivity to microbubble signal, interreader variability, large numbe

239 ene delivery vehicles, the slightly cationic microbubbles significantly increased ultrasound-mediated

240 his study was to compare sulfur hexafluoride microbubble (SonoVue)-enhanced myocardial contrast echoc

241 Gas microbubbles stabilized with lipids, surfactants, protei

242 but a lower stable cavitation threshold than microbubbles, suggesting that contrast agent-dependent a

243 ualization of transpulmonary agitated saline microbubbles suggests that anatomical intra-pulmonary ar

244 e termed a "molecular rotor" embedded in the microbubble surface, whose fluorescence lifetime is dire

245 We show that the concentration of a microbubble suspension can be monitored quantitatively w

246 The microbubble suspension was added to buffer at the apical

247 reaction, also indicating that the developed microbubble system may be a valuable platform to design

248 alcohol oxidation activation energy for the microbubble systems is much lower than that for the conv

249 imaging of the thoracic aorta performed with microbubbles targeted to GPIbalpha demonstrated selectiv

250 involves contrast-enhanced ultrasound using microbubbles targeted to molecular signatures on tumor n

251 Molecular imaging with microbubbles targeted to the A1 domain of von Willebrand

252 n live cells by acoustic actuation of paired microbubbles targeted to the cell adhesion receptor inte

253 st and unique interaction of ultrasound with microbubbles, TB-ATC provides distinct advantages for ex

254 tegies for using ultrasound with and without microbubble technology for enhancing our understanding o

255 ng a short ultrasound pulse to excite single microbubbles tethered to cell membranes, a transient por

256 corporated in their shell can generate vapor microbubbles that can be spatiotemporally controlled by

257 as a functional modality through the use of microbubbles that can be targeted to specific biological

258 cin (BLM) were studied in cell culture using microbubbles that had been derivatized with multiple cop

259 r targeted to a specific biomarker (targeted microbubbles, tMBs) or that are not targeted (non-target

260 blood-brain barrier by exposing circulating microbubbles to a sequence of long ultrasound pulses.

261 ability of novel ultrasound-activated lipid microbubbles to deliver drugs into the cytoplasm of apic

262 een fluorescent protein) and used ultrasound microbubbles to deliver tyrosine kinase receptor-2 promo

263 amplitude in ATC actuated the integrin-bound microbubbles to mobilize the crystal-like drug inclusion

264 as is required to exit the surface layer via microbubbles to produce the observed elevated k600,CH4.

265 w-pressure ultrasound and require gas-filled microbubbles to transduce the ultrasound wave.

266 ot strongly affected by early binding of the microbubbles to VEGFR2.

267 ), in the presence of intravenously injected microbubbles, to safely and transiently increase the per

268 e (MR) imaging-guided focused ultrasound and microbubble ultrasonography (US) contrast agents for the

269 amil (1 mg/ml in drinking water) or by local microbubble-ultrasound TXNIP shRNA transfection.

270 care, 45 patients received an infusion of a microbubble US contrast agent and saline.

271 High microbubble volume in the extracorporeal circulation loo

272 heath flushing produced significantly higher microbubble volume than slow sheath flushing (median, 12

273 ap of proximal and distal electrodes (median microbubble volume, 1744 nL; interquartile range, 737-40

274 122 delivery into tumors with ultrasound and microbubbles was 7.9-fold higher compared to treatment w

275 Binding of Thy1-targeted contrast microbubbles was assessed in cultured cells, in mice wit

276 sound-activated intracellular delivery using microbubbles was over 16 times greater than the control

277 ruption using 690kHz ultrasound and Definity microbubbles was performed in one of the tumors and in a

278 Formation of microbubbles was the greatest during fast saline/contras

279 Using doxorubicin-liposome-loaded microbubbles, we show that sonoprinting allows to deposi

280 DiI-labeled microbubbles were administered during ablation at 2, 4,

281 (200 mug) encoding luciferase and SonoVue(R) microbubbles were co-injected intravenously in mice.

282 Microemboli and microbubbles were compared between ablation with an irri

283 The gas-filled lipid microbubbles were decorated with liposomes containing th

284 In an acoustic field, trapped microbubbles were driven into oscillatory motion generat

285 Based on these results, slightly cationic microbubbles were evaluated for microbubble and ultrasou

286 Individual microbubbles were identified, localized, and tracked to

287 a focused ultrasound transducer, and formed microbubbles were imaged using a clinical ultrasound sca

288 In this work, single microbubbles were localized in vivo in a rat kidney usin

289 e, the acoustic emissions from FUS-activated microbubbles were passively detected by an ultrasound im

290 ion molecule-1-targeted and rhodamine-loaded microbubbles were shown to be specifically bound to tumo

291 ctive, resulting in echogenic and persistent microbubbles which provide real-time high MI visualizati

292 ver gene and proteins into cytoplasm without microbubbles, which enables controlled and local intrace

293 e composition and the presence of SonoVue(R) microbubbles, which provided the nuclei for the initiati

294 These microbubbles will also affect the surface fluxes of othe

295 ier (BBB) opening in vivo using monodisperse microbubbles with different phospholipid shell component

296 cell-derived vesicles, model membranes, and microbubbles with environmentally-sensitive probes Laurd

297 Overall, lipid-shelled microbubbles with long hydrophobic chain length could ac

298 Conventional microbubbles with the same lipid shell composition and p

299 While the interactions of microbubbles with ultrasound have been widely investigat

300 To achieve this, we trapped microbubbles within predefined sidewall microcavities in