Abstract-Contrast microbubbles in combination with ultrasound (US) are promising vehicles for local drug and gene delivery. However, the exact mechanisms behind intracellular delivery of therapeutic compounds remain to be resolved. We hypothesized that endocytosis and pore formation are involved during US and microbubble targeted delivery (UMTD) of therapeutic compounds. Therefore, primary endothelial cells were subjected to UMTD of fluorescent dextrans (4.4 to 500 kDa) using 1 MHz pulsed US with 0.22-MPa peak-negative pressure, during 30 seconds. Fluorescence microscopy showed homogeneous distribution of 4.4-and 70-kDa dextrans through the cytosol, and localization of 155-and 500-kDa dextrans in distinct vesicles after UMTD. After ATP depletion, reduced uptake of 4.4-kDa dextran and no uptake of 500-kDa dextran was observed after UMTD. Independently inhibiting clathrin-and caveolae-mediated endocytosis, as well as macropinocytosis significantly decreased intracellular delivery of 4.4-to 500-kDa dextrans. Furthermore, 3D fluorescence microscopy demonstrated dextran vesicles (500 kDa) to colocalize with caveolin-1 and especially clathrin. Finally, after UMTD of dextran (500 kDa) into rat femoral artery endothelium in vivo, dextran molecules were again localized in vesicles that partially colocalized with caveolin-1 and clathrin. Together, these data indicated uptake of molecules via endocytosis after UMTD. In addition to triggering endocytosis, UMTD also evoked transient pore formation, as demonstrated by the influx of calcium ions and cellular release of preloaded dextrans after US and microbubble exposure. In conclusion, these data demonstrate that endocytosis is a key mechanism in UMTD besides transient pore formation, with the contribution of endocytosis being dependent on molecular size. Key Words: ultrasound microbubble targeted delivery Ⅲ cell membrane pore Ⅲ endocytosis Ⅲ dextran Ⅲ endothelial cells C onventional delivery methods for drugs or genes, such as systemic administration via intravenous injection or oral administration, often do not suffice for therapeutic compounds such as peptides, silencing RNAs and genes. 1 A recent development in delivery systems for therapeutic compounds is the microbubble-ultrasound (US) interaction. 2,3 Before its use as a clinical modality, it is of utmost importance to obtain new physiological insights into the mechanisms of uptake by US and microbubble-exposed cells.Microbubbles were originally developed as US contrast agents and are administered intravenously to the systemic circulation to enhance scattering of blood in echocardiography. They consist of a gas core stabilized with an encapsulation, ranging from 1 to 10 m in diameter. 4 Nowadays, research focuses on the use of US and microbubbles for therapeutic applications. It has been demonstrated that USexposed microbubbles can achieve safe and efficient local delivery of a variety of drugs 5,6 and genes.

The development of ultrasound contrast agents, containing encapsulated microbubbles, has increased the possibilities for diagnostic imaging. Ultrasound contrast agents are currently used to enhance left ventricular opacification, increase Doppler signal intensity, and in myocardial perfusion imaging. Diagnostic imaging with contrast agents is performed with low acoustic pressure using non-linear reflection of ultrasound waves by microbubbles. Ultrasound causes bubble destruction, which lowers the threshold for cavitation, resulting in microstreaming and increased permeability of cell membranes. Interestingly, this mechanism can be used for delivery of drugs or genes into tissue. Microbubbles have been shown to be capable of carrying drugs and genes, and destruction of the bubbles will result in local release of their contents. Recent studies demonstrated the potential of microbubbles and ultrasound in thrombolysis. In this article, we will review the recent advances of microbubbles as a vehicle for delivery of drugs and genes, and discuss possible therapeutic applications in thrombolysis.

In the present study, we addressed the interactions among ultrasound, microbubbles, and living cells as well as consequent arising bioeffects. We specifically investigated whether hydrogen peroxide (H(2)O(2)) is involved in transient permeabilization of cell membranes in vitro after ultrasound exposure at low diagnostic power, in the presence of stable oscillating microbubbles, by measuring the generation of H(2)O(2) and Ca(2+) influx. Ultrasound, in the absence or presence of SonoVue microbubbles, was applied to H9c2 cells at 1.8 MHz with a mechanical index (MI) of 0.1 or 0.5 during 10 s. This was repeated every minute, for a total of five times. The production of H(2)O(2) was measured intracellularly with CM-H(2)DCFDA. Cell membrane permeability was assessed by measuring real-time changes in intracellular Ca(2+) concentration with fluo-4 using live-cell fluorescence microscopy. Ultrasound, in the presence of microbubbles, caused a significant increase in intracellular H(2)O(2) at MI 0.1 of 50% and MI 0.5 of 110% compared with control (P < 0.001). Furthermore, we found increases in intracellular Ca(2+) levels at both MI 0.1 and MI 0.5 in the presence of microbubbles, which was not detected in the absence of extracellular Ca(2+). In addition, in the presence of catalase, Ca(2+) influx immediately following ultrasound exposure was completely blocked at MI 0.1 (P < 0.01) and reduced by 50% at MI 0.5 (P < 0.001). Finally, cell viability was not significantly affected, not even 24 h later. These results implicate a role for H(2)O(2) in transient permeabilization of cell membranes induced by ultrasound-exposed microbubbles.