ライフサイエンスコーパス: microbubble

1 e maintaining echoes from very slowly moving microbubbles.

2 treaming flow generated by ultrasound-driven microbubbles.

3 se fashion by ultrasound and ultrasound with microbubbles.

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

5 psies after injection of sulfur hexafluoride microbubbles.

6 ystemically administered OV co-injected with microbubbles.

7 attached to maleimide groups on lipid-coated microbubbles.

8 detection limits of 20 nM thrombin and 2 aM microbubbles.

9 uction-replenishment DCE US with nontargeted microbubbles.

10 rea following bolus injection of the DNA/PEI-microbubbles.

11 in targeted cells by selective excitation of microbubbles.

12 the carotid bifurcation with use of 2 mL of microbubbles.

13 l intensity of continuously infused contrast microbubbles.

14 y sonicated after administration of Definity microbubbles.

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

16 mpared to commercially available Definity(R) microbubbles.

17 using focused ultrasound in combination with microbubbles.

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

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

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

21 me to sustain inertial cavitation, a type of microbubble activity, throughout the exposure.

22 ast echocardiography with late appearance of microbubbles after venous injection of agitated saline (

23 d combined with an intravenously circulating microbubble agent can temporarily permeabilize the BBB.

24 ultrasound (FUS) combined with a circulating microbubble agent is a promising strategy to non-invasiv

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

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

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

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

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

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

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

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

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

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

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

39 ed gene delivery was performed with cationic microbubbles and plasmid deoxyribonucleic acid.

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

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

42 In this study, we evaluated whether microbubbles and ultrasound-targeted microbubble destruc

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

44 preclinical proof-of-concept for customized microbubbles and UTMD to deliver gene-targeted siRNA for

45 s but not ultrasound or control siRNA-loaded microbubbles and UTMD.

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

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

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

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

50 ion molecule-1-targeted and rhodamine-loaded microbubbles are able to bind specifically to the inflam

51 Initially silent microbubbles are activated in the presence of both throm

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

53 Currently, microbubbles are the only agents that have been used to

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 Microbubbles as vascular contrast agents improve the det

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

59 llow the presence of stable and controllable microbubbles at the boundary of microchannels.

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

61 Microbubble attachment to P-selectin-immunoglobulin G fu

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

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

64 Lipid microbubbles bearing recombinant human PSGL-1 (MB(YSPSL)

65 Our results reveal characteristic microbubble behaviors responsible for sonoporation and d

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

67 n-exposed sonicated dextrose albumin (PESDA) microbubbles bind to injured vascular tissue and can be

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

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

70 cally translatable PEGylated VEGFR2-targeted microbubbles (BR55).

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

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

73 tive to controls receiving EGFR siRNA-loaded microbubbles but not ultrasound or control siRNA-loaded

74 f the viscoelastic surface properties of the microbubbles, but methods for independent, nondestructiv

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

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

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

78 However, microbubbles can be used for more than diagnosis: disint

79 Although microbubbles can boost the diagnostic value of ultrasono

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

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

82 BBB/BTB permeabilization induced by FUS and microbubbles can improve outcomes in breast cancer brain

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

84 surrounding brain tissue induced by FUS and microbubbles can slow tumor growth and improve survival

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

86 sound (FUS) bursts combined with circulating microbubbles can temporarily permeabilize both the BBB a

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

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

89 Ultrasound induced microbubble cavitation can cause enhanced permeability a

90 Therapeutic ultrasound using microbubble cavitation to increase muscle perfusion reli

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

92 .81MPa; 10ms bursts; 1Hz PRF; 60s duration), microbubble concentration (Definity, 10mul/kg), and the

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

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

95 Microbubble concentrations of 0.02%, 0.1%, 0.5%, 1%, and

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

97 A microbubble contrast agent is presented that produces ul

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

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

100 Additionally, microbubble contrast agents are improving the sensitivit

101 Microbubble contrast agents can specifically deliver nuc

102 Microbubble contrast agents that undergo ultrasound-medi

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

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

105 stics and percentage maximal distribution of microbubble contrast injection into the SCS were assesse

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

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

108 ologic response in PDAC, we used noninvasive microbubble contrast-enhanced ultrasound imaging, which

109 e; eyes in group 2 (n = 6) were imaged by 3D microbubble contrast-enhanced ultrasound, and the tumor

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

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

112 ur blood vessel, through which the virus and microbubbles could be made to flow.

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

114 PEI-microbubbles coupled to a luciferase bioluminescence rep

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

116 The PEI-microbubbles demonstrated increasingly positive surface

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

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

119 whether microbubbles and ultrasound-targeted microbubble destruction (UTMD) could be used to enhance

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

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

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

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

124 Ultrasound targeted microbubble destruction has become a promising tool for

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

126 ultrasound treatment parameters that mediate microbubble destruction.

127 ensitivity and specificity of ultrasound for microbubble detection, molecular imaging can be realized

128 Molecular microbubbles directed against various targets such as va

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

130 solates the acoustic emissions caused by the microbubbles during sonication.

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

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

133 Custom-designed microbubbles efficiently bound siRNA and mediated RNAse

134 used for more than diagnosis: disintegrating microbubbles emit acoustic forces that are strong enough

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

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

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

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

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

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

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

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

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

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

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

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

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

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

149 This review on the use of microbubbles for ultrasound-based molecular imaging, the

150 The microbubbles form explosively when small aliquots of an

151 Currently, the first microbubble formulations targeted to angiogenic vessels

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

153 ntally and numerically examine the effect of microbubble geometry on the slippage at high resolution.

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

155 Acoustic cavitation of microbubbles has been recognized to play an important ro

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

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

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

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

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

161 challenges to fully realize the potential of microbubbles in advanced applications such as perfusion

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

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

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

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

166 However, DNA loading to form polyplex-microbubbles increased circulation in the bloodstream an

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

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

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

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

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

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

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

174 ound activation of systemically administered microbubbles is a noninvasive and localized drug deliver

175 Insonation of microbubbles is thought to facilitate two mechanisms for

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

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

178 Microbubble kinetics was investigated over the course of

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

180 US contrast microbubbles linked to antibodies or small molecules may

181 UTMD-mediated delivery of microbubbles loaded with EGFR-directed siRNA to murine s

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

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

184 These microbubbles may originate from atmospheric bubble entra

185 t to investigate the therapeutic efficacy of microbubble (MB) enhanced sonothrombolysis for aged CVC

186 plex gene carriers and adjustments to US and microbubble (MB) parameters.

187 wth factor receptor type 2 (VEGFR2)-targeted microbubbles (MB(VEGFR2)) to improve the diagnostic accu

188 Microbubbles (MB) bearing antibodies targeting lymphocyt

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

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

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

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

193 t al (1) have shown that P-selectin-targeted microbubbles (MBs) can be used to monitor the expression

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

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

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

197 ipid conjugates were used to create photonic microbubbles (MBs) having a porphyrin shell ("porshe"),

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

199 sized that contrast-enhanced ultrasound with microbubbles (MBs) selectively targeted to activated pla

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

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

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

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

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

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

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

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

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

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

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

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

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

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

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

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

216 Microbubbles of different surface charges (neutral, slig

217 ; P=0.045), and greatest with type II or III microbubbles on transesophageal echocardiography.

218 Cerebral embolization of air microbubbles or microparticulate debris that approximate

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

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

224 -positive cells (1.76 +/- 0.49 [mean +/- SD] microbubbles per cell) than to control cells (0.07 +/- 0

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

226 These results suggest that the polyplex-microbubble platform offers improved control of DNA load

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

228 The resultant microbubble reaction systems exhibit significant catalys

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

230 By quantifying microbubble retention within the carotid plaque, LP cont

231 8 and 1 mL/min) showed significantly reduced microbubbles retention, by 38% (P=0.03) and 55% (P=0.03)

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

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

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

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

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

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

238 d, commercially available, second-generation microbubbles (SonoVue) and clinically translatable PEGyl

239 Gas microbubbles stabilized with lipids, surfactants, protei

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

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

242 s, peptides, and other targeting moieties to microbubble surfaces.

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

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

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

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

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

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

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

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

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

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

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

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

255 udy, we conducted experiments using targeted microbubbles that were attached to cell membrane to faci

256 Ultrasound excitation of microbubbles that were targeted to the plasma membrane o

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

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

259 onically-induced oscillations of circulating microbubbles to permeabilize vascular barriers such as t

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

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

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

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

264 for 60s and combined with IV injection of a microbubble ultrasound contrast agent (Definity; 10 mul/

265 Microbubble ultrasound contrast agents are being develop

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

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

268 We have discovered that ultrasound-mediated microbubble vascular disruption can enhance tumor respon

269 d single treatments of ultrasound-stimulated microbubble vascular perturbation and radiation inducing

270 High microbubble volume in the extracorporeal circulation loo

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

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

273 Microbubble volumes with PVAC (29.1 nL) were greater tha

274 quency ultrasound (7.44MHz) pulses, a single microbubble was generated and positioned at a desired di

275 122 delivery into tumors with ultrasound and microbubbles was 7.9-fold higher compared to treatment w

276 sonication) in conjunction with circulating microbubbles was applied in 86 locations in 27 rats to d

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

278 netic model accounting for free and adherent microbubbles was developed to describe the anomalous tim

279 vivo ultrasound contrast persistence of PEI-microbubbles was measured in the healthy mouse kidney, a

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

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

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

283 (200 mug) encoding luciferase and SonoVue(R) microbubbles were co-injected intravenously in mice.

284 Microemboli and microbubbles were compared between ablation with an irri

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

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

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

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

289 In this study, novel polyplex-microbubbles were synthesized, characterized and evaluat

290 d the mechanical action caused by collapsing microbubbles when sonic waves propagate through a liquid

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