Microbubbles are bubbles smaller than one hundredth of a millimetre in diameter, but larger than one micrometre. They have widespread application in industry, medicine, life science, and food technology. The composition of the bubble shell and filling material determine important design features such as buoyancy, crush strength, thermal conductivity, and acoustic properties.

They are used in medical diagnostics as a contrast agent for ultrasound imaging. The gas-filled microbubbles, typically air or perfluorocarbon, oscillate, and vibrate if a sonic energy field is applied and may reflect ultrasound waves. This distinguishes the microbubbles from surrounding tissues. Because gas bubbles in liquid lack stability and would therefore quickly dissolve, microbubbles are typically encapsulated by shells. The shell is made from elastic, viscoelastic, or viscous material. Common shell materials are lipid, albumin, and protein. Materials having a hydrophilic outer layer to interact with the bloodstream and a hydrophobic inner layer to house the gas molecules are thermodynamically stable. Air, sulfur hexafluoride, and perfluorocarbon gases all can serve as the composition of the microbubble interior. Microbubbles with one or more incompressible liquid or solid cores surrounded by gas are referred to as microscopic or endoskeletal antibubbles. For increased stability and persistence in the bloodstream, gases with high molecular weight as well as low solubility in the blood are attractive candidates for microbubble gas cores.

Microbubbles may be used for drug delivery, biofilm removal, membrane cleaning /biofilm control and water/waste water treatment purposes. They are also produced by the movement of a ship's hull through water, creating a bubble layer; this may interfere with the use of sonar because of the tendency of the layer to absorb or reflect sound waves.

Contrast in ultrasound imaging relies on the difference in acoustic impedance, a function of both the speed of the ultrasound wave and the density of the tissues, between tissues or regions of interest. As the sound waves induced by ultrasound interact with a tissue interface, some of the waves are reflected back to the transducer. The larger the difference, the more waves are reflected, and the higher the signal to noise ratio. Hence, microbubbles that have a core with a density orders of magnitude lower than and compress more readily than the surrounding tissues and blood, afford high contrast in imaging.

When exposed to ultrasound, microbubbles oscillate in response to the incoming pressure waves in one of two ways. With lower pressures, higher frequencies, and larger microbubble diameter, microbubbles oscillate, or cavitate, stably.  This causes microstreaming near the surrounding vasculature and tissues, inducing shear stresses that can create pores on the endothelial layer. This pore formation enhances endocytosis and permeability. At lower frequencies, higher pressures, and lower microbubble diameter, microbubbles oscillate inertially; they expand and contract violently, ultimately leading to microbubble collapse. This phenomenon can create mechanical stresses and microjets along the vascular wall, which has been shown to disrupt tight cellular junctions as well as induce cellular permeability. Extremely high pressures cause small vessel destruction, but the pressure can be tuned to only create transient pores in vivo. microbubble destruction serves as a desirable method for drug delivery vehicles. The resulting force from destruction can dislodge the therapeutic payload present on the microbubble and simultaneously sensitize the surrounding cells for drug uptake.

Microbubbles can serve as drug delivery vehicles in a variety of methods. The most notable of these include: (1) incorporating a lipophilic drug to the lipid monolayer, (2) attaching nanoparticles and liposomes to the microbubble surface, (3) enveloping the microbubble within a larger liposome, and (4) electrostatically bonding nucleic acids to the microbubble surface.

Microbubbles can facilitate the local targeting of hydrophobic drugs through the incorporation of these agents into the microbubble lipid shell. This encapsulation technique reduces systemic toxicity,  increases drug localization, and improves the solubility of hydrophobic drugs. For increased localization, a targeting ligand can be appended to the exterior of the microbubble. This improves treatment efficacy. One drawback of the lipid-encapsulated microbubble as a drug delivery vehicle is its low payload efficacy. To combat this, an oil shell can be incorporated to the interior of the lipid monolayer to enhance payload efficacy.

Attachment of liposomes or nanoparticles to the exterior of the lipid microbubble has also been explored to increase microbubble payload. Upon microbubble destruction with ultrasound, these smaller particles can extravasate into the tumor tissue. Furthermore, through attachment of these particles to microbubbles as opposed to co-injection, the drug is confined to the blood stream instead of accumulating in healthy tissues, and the treatment is relegated to the location of ultrasound therapy. This microbubble modification is particularly attractive for Doxil, a lipid formulation of Doxorubicin already in clinical use. An analysis of nanoparticle infiltration due to microbubble destruction indicates that higher pressures are necessary for vascular permeability and likely improves treatment by promoting local fluid movement and enhancing endocytosis.