The clinical need for organ- or tissue-specific drug delivery, also known as targeted drug delivery, arises when systemic delivery of a drug in sufficient doses to achieve a therapeutic effect at the target site results in deleterious systemic effects. Relevant clinical problems include delivery of chemotherapeutic drugs to tumors, delivery of thrombolytic drugs to the cerebral or coronary circulation during ischemic stroke or myocardial infarction, and delivery of vasoactive drugs to the cerebral or coronary circulation for treatment of vasospasm. Current solutions to these problems involve invasive catheterization procedures directed at selective intra-arterial infusion of a drug into the target vascular bed. Such procedures often carry major risks. In many cases, therapeutic efficacy is lost shortly after removal of the indwelling catheter and cessation of drug infusion. Additional treatments require repetition of the invasive catheterization procedures with incremental accumulation of procedure- related risks. In most cases, prolonged maintenance of indwelling catheters for sustained or repetitive treatment is associated with prohibitive risk. Over the last 4 decades, liposomes have been explored as targeted drug delivery vehicles.1,2 A number of clinical and experimental therapeutic agents have been successfully loaded into liposomes.3 Liposomes, which are formed by enclosure of an aqueous core by 1 or more phospholipid bilayers, range in size from about 100 nm to several micrometers. Liposomes offer several advantages as drug delivery vehicles. Water-soluble compounds may be entrapped in the aqueous core, whereas water-insoluble compounds may bind to the lipid membrane. A liposome-associated drug (either bound to the lipid or entrapped in the aqueous core) is hypothesized to remain physiologically inactive until the physical integrity of the lipid membrane is disturbed. Drug-loaded liposomes propagated in the circulation can function as mobile drug reservoirs with the ability to deliver large pay-loads of a drug to specific target organs or tissues when appropriately triggered. Several chemical and physical methods for triggered drug release from liposomes have been explored, including acoustic pressure-, temperature-, and pH-dependent mechanisms.4–6 One promising approach that is being explored for drug delivery is the use of ultrasound-activated echogenic liposomes (ELIPs). These agents are synthesized by incorporating air and a drug of interest into liposomes that are submicrometer in size (mean diameter, 780 nm).7 These encapsulated air pockets are probably on the order of tens or hundreds of nanometers in diameter and thus can be considered nanobubbles. Note that the perfluorocarbon gas pockets in many contrast agents used clinically today are on the order of several micrometers and thus encapsulate microbubbles, not nanobubbles.8,9 Exposure of ELIPs to suitable pulses of ultrasound disturbs the physical structure of the liposome and results in drug release. Because ELIP activation by ultrasound can be controlled both spatially and temporally, ELIPs are potentially powerful tools for selective tissue- or organ-specific drug delivery. Furthermore, the encapsulated nanobubbles can serve as ultrasonic contrast agents, enabling the process of drug release and activation to be imaged in real time. The pulse repetition frequency and duty cycle dependence of the acoustic pressure destruction threshold for ELIPs has been characterized with 6-MHz pulsed Doppler ultrasound.10 Continuous wave ultrasound (2–7 W/cm2) has been investigated as a means of triggering calcein or recombinant tissue plasminogen activator (rt-PA) release from ELIP in nonflowing solutions.4,11,12 Recently, pulsed color Doppler ultrasound was used to trigger release of rt-PA from rt-PA-loaded ELIPs in flowing solutions.13 The use of color Doppler ultrasound (a scanned mode) enables a larger number of ELIPs to be exposed per unit of time than spectral Doppler ultrasound (an unscanned mode). This is important in clinical drug delivery paradigms because ELIPs circulating in the bloodstream will move rapidly through the ultrasound field. Because in vitro evaluation of ultrasound-triggered drug release must consider this aspect of clinical drug delivery, our experimental design used a flow model with a peristaltic pump to circulate ELIP solutions through an ultrasound exposure volume. Calcein, a water-soluble polyanionic fluorescein derivative with photosensitizing properties, is used as a fluorescent indicator in drug release studies as well as a contrast agent in retinal angiography.14,15 Papaverine, a spasmolytic lipophilic opium alkaloid, is administered into cerebral arteries through a microcatheter for clinical treatment of posthemorrhagic cerebral vasospasm.16,17 In this study, calcein-loaded ELIPs (C-ELIPs) and papaverine-loaded ELIPs (P-ELIPs) were circulated in a flow model and exposed to pulsed color Doppler ultrasound to trigger calcein or papaverine release from C-ELIPs or P-ELIPs. The objective of this study was to quantify the release of calcein and papaverine from C-ELIPs and P-ELIPs, respectively. Dynamic changes in echogenicity were also assessed with B-mode ultrasound before, during, and after color Doppler ultrasound exposure.