Gas types affect stability of microbubbles and ultrasound mediated brain-targeted drug delivery
Ultrasound (US) is used for clinical diagnosis and therapy. Microbubbles (MBs) as US-contrast agents are applied to detect micro blood flow or specific lesions. Recently, the combination of MBs and US has received much attention for drug delivery. US induces MB oscillation or collapse in some conditions, and the behavior of MBs can enhance vascular permeability. Therefore, the combination of MBs and US has the potential to selectively deliver drugs to the tissue exposed to US.
In the brain, the blood–brain barrier (BBB) restricts the transportation of molecules between blood and parenchyma. As most drugs cannot cross the BBB, it is a major obstacle to achieve efficient drug delivery for effective disease therapy. It has been reported that the combination of MBs and US could also enhance the permeability of BBB, so called “BBB opening,” and the combination has become a possibility for brain-targeted drug delivery. US devices are important and have been developed to establish a noninvasive and efficient brain-targeted drug delivery system. Meanwhile, MBs also play an important role in BBB opening. The structure of MBs is composed of inner gas and an outer shell (Fig. 1A). Previous reports have demonstrated that the particle size and shell components of MBs affected the efficacy of brain-targeted drug delivery. However, the effect of encapsulated gas in MBs on brain-targeted drug delivery is not well evaluated.
In this study, we prepared lipid-based MBs containing perfluoropropane (C3F8), perfluorobutane (C4F10), or sulfur hexafluoride (SF6) with the same phospholipid shell (MB-C3F8, MB-C4F10, or MB-SF6) and examined the effects of each MB on brain-targeted drug delivery.
The average diameter of each gas-loaded MB was approximately 2.5 µm. Therefore, the effect of the size of MBs on brain-targeted drug delivery would be excluded. We first evaluated the stability of MBs in blood flow because MBs need to reach to the brain. MBs were injected into mice, and the echogenicity in their kidneys was measured using a US-imaging device. As a result, the half-life of echogenicity of MB-C3F8 and MB-C4F10 was longer than that of MB-SF6 (Fig. 1B). The solubilities of C3F8 and C4F10 in water are lower than that of SF6. SF6 can be easily dissolved in a solution outside MBs, resulting in the reduced stability of MB-SF6. This result suggests that MB-C3F8 and MB-C4F10 could circulate in the blood for a long time and are expected to increase the likelihood of creating a BBB opening. Next, we examined the delivery efficacy of Evans blue (EB), which is a model drug with a blue color, to the brain. The mixture of MBs and EB was injected into mice, and transcranial US was immediately applied to the right side of the mice’s brains. After 1 hour, the brain was collected and observed. When MB-C3F8 and MB-C4F10 were administrated, EB was distributed in wide areas of the brain compared with MB-SF6 (Fig. 1C). In addition, we confirmed no hemorrhage or neuron degradation in the brain after the MBs and US treatment. These results suggest that MBs containing C3F8 or C4F10 can efficiently deliver drugs into the brain.
In conclusion, we prepared MB-C3F8, MB-C4F10, and MB-SF6 with identical outer shells and similar sizes and demonstrated that MB-C3F8 and MB-C4F10 could efficiently deliver EB into the brain with US. Our results suggested that C3F8 and C4F10 are useful for developing MBs to achieve efficient brain-targeted drug delivery.
Daiki Omata 1, Ryo Suzuki 1,2
1Laboratory of Drug and Gene Delivery Research, Faculty of Pharma-Science, Teikyo University, Tokyo, Japan
2Advanced Comprehensive Research Organization (ACRO), Teikyo University, Tokyo, Japan
Effects of encapsulated gas on stability of lipid-based microbubbles and ultrasound-triggered drug delivery
Omata D, Maruyama T, Unga J, Hagiwara F, Munakata L, Kageyama S, Shima T, Suzuki Y, Maruyama K, Suzuki R
J Control Release. 2019 Oct
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