Membrane Organization Strategies in Vesicular Antibiotic Delivery.

Small molecule antibiotics are often derived from microorganisms that thrive in competitive environments. Their importance as therapeutics for infectious disease in humans has been established over many years. It has now become clear that antibiotic-producing organisms use packaging and delivery in the form of vesicles in many cases. A similar strategy has evolved in recent decades in the pharmaceutical industry for formulation of antibiotic therapies. The top-down approach that has evolved over millions of years in various micro-organisms has generated complex, efficient delivery systems that we are just now beginning to understand. The bottom-up formulation approach involves simple, safe compositions, which are being continually enhanced by trying to add features of which the natural systems inform us. A comparison is made here of these paradigms. Despite the differences, there are a number of common features in the basic physical and biological requirements that must be satisfied. In this review, illustration and comparison of some of these requirements is given, demonstrating the ongoing challenges in this area of research.

Vesicular Delivery of the Antifungal Antibiotics of Lysobacter enzymogenes C3.

Lysobacter enzymogenes C3 is a predatory strain of Gram-negative gliding bacteria that produces antifungal antibiotics by the polyketide synthetic pathway. Outer membrane vesicles (OMV) are formed as a stress response and can deliver virulence factors to host cells. The production of OMV by C3 and their role in antifungal activity are reported here. Vesicles in the range of 130 to 150 nm in diameter were discovered in the cell-free supernatants of C3 cultures. These OMV contain molecules characteristic of bacterial outer membranes, such as lipopolysaccharide and phospholipids. In addition, they contain chitinase activity and essentially all of the heat-stable antifungal activity in cell supernatants. We show here that C3 OMV can directly inhibit growth of the yeast Saccharomyces cerevisiae as well as that of the filamentous fungus Fusarium subglutinans The activity is dependent on physical contact between OMV and the cells. Furthermore, fluorescent lipid labeling of C3 OMV demonstrated transfer of the membrane-associated probe to yeast cells, suggesting the existence of a mechanism of delivery for membrane-associated molecules. Mass spectrometric analysis of C3 OMV extracts indicates the presence of molecules with molecular weights identical to some of the previously identified antifungal products of C3. These data together suggest that OMV act as an important remote mobile component of predation by LysobacterIMPORTANCE The data presented here suggest a newly discovered function of outer membrane vesicles (OMV) that are produced from the outer membrane of the bacterial species Lysobacter enzymogenes strain C3. We show that these OMV can be released from the surface of the cells to deliver antibiotics to target fungal organisms as a mechanism of killing or growth inhibition. Understanding the role of OMV in antibiotic delivery can generally lead to improved strategies for dealing with antibiotic-resistant organisms. These results also add to the evidence that some bacterially produced antibiotics can be discovered and purified using methods designed for isolation of nanoscale vesicles. Information on these systems can lead to better identification of active molecules or design of delivery vehicles for these molecules.

A gamma scintigraphy study to investigate lung deposition and clearance of inhaled amikacin-loaded liposomes in healthy male volunteers.

BACKGROUND: The purpose of this study was to investigate the inhalation of a liposomal formulation of amikacin in healthy male volunteers in terms of pulmonary deposition, clearance, and safety following nebulization with a commercial jet nebulizer. METHODS: Amikacin was encapsulated in liposomes comprised of dipalmitoyl phosphatidylcholine (DPPC) and cholesterol via a proprietary manufacturing process (20 mg/mL final amikacin concentration). The liposomes were radiolabeled with (99m)Tc using the tin chloride labeling method. A nominal dose of 120 mg of drug product was loaded into a PARI LC STAR nebulizer, aerosolized using a PARI Boy compressor where subjects inhaled for 20 min. Lung deposition was determined by gamma scintigraphy in three healthy male volunteers at the following time points (0, 1, 3, 6, 12, 24, 48, and 72 h post-administration). RESULTS: Total lung deposition, expressed as a percentage of the emitted dose, was 32.3 +/- 3.4%. The time-dependent retention of radiolabeled liposomes was biphasic with an initial rapid reduction in counts, followed by a slower phase to 48 h. The overall mean retention at 24 and 48 h was 60.4 and 38.3% of the initial dose deposited, respectively. The observed clearance of radiolabel is consistent with clearance of amikacin following aerosol delivery to rats. There were no clinically significant changes in laboratory parameters, vital signs, or ECG. No adverse events including cough or bronchospasm were reported. CONCLUSIONS: Inhalation of a single nominal dose of 120 mg liposomal amikacin results in prolonged retention of drug-loaded liposomes in the lungs of healthy volunteers. The treatment was well tolerated.

Characterization of nebulized liposomal amikacin (Arikace) as a function of droplet size.

The stress of nebulization has been shown to alter the properties of liposomal drugs. What has not been demonstrated is whether nebulized liposomes differ as a function of droplet size. Because droplet size influences lung deposition, liposomes with different properties could be deposited in different areas of the lung (e.g., central vs. peripheral). In this report, a liposomal amikacin formulation (Arikace, a registered trademark of Transave, Inc., Monmouth Junction, NJ) that is being developed as an inhaled treatment for gram negative infections was aerosolized with an eFlow (registered trademark of PARI, GmbH, Munich, Germany) nebulizer, reclaimed from the various stages of an Andersen cascade impactor (ACI) and analyzed for lipid-to-drug (L/D) (w/w) ratio, amikacin retention, and liposome size. For the nebulized solution, 99.7% of the total deposited drug was found on ACI stages 0 through 5, which have cutoff diameters of 9, 5.8, 4.7, 3.3, 2.1, and 1.1 microm, respectively. Properties were found to differ for drug reclaimed on stage 0 compared stages 1-5, which were not different from one another. For drug found on stages 1-5 (97% of total drug), the averages (n = 3) for L/D, percent encapsulated amikacin, and liposome mean diameter ranged from 0.59 to 0.68 (w/w), 71% to 75%, 248 to 282 nm, respectively. Drug found on stage 0 (2.8% of total drug) had an average L/D ratio of 0.51 and average liposome mean diameter of 375 nm. Examination of another batch of liposomal amikacin revealed no statistically significant differences between drug reclaimed on stages 0-5. Although a droplet size dependence was noted for one batch of Arikace aerosolized with the eFlow, the effect was considered to be inconsequential because the fraction in doubt represented nonrespirable particles >9 microm and accounted for <3% of the total deposited dose. The methodology applied here appears useful in evaluating aerosolized liposome systems. However, our results should not be assumed to apply to other liposome/drug compositions and nebulizers.

Formation of homogeneous unilamellar liposomes from an interdigitated matrix.

Phospholipid-ethanol-aqueous mixtures containing bilayer-forming lipids and 20-50 wt.% of water form viscous gels. Further hydration of these gels results in the formation of liposomes whose morphology depends upon the lipid type. Upon hydration of gels containing mixtures of the lipids 1-palmitoyl-2-oleoyl-phosphatidylcholine (POPC) and 1-palmitoyl-2-oleoyl-phosphatidylglycerol (POPG), small homogeneous and unilamellar liposomes were produced. In contrast, hydration of gels containing only POPC resulted in formation of large multilamellar liposomes. Likewise, mulitlamellar liposomes resulted when this method was applied to form highly fusogenic liposomes comprised of the novel negatively charged N-acyl-phosphatidylethanolamine (NAPE) mixed with di-oleoyl-phosphatidylcholine (DOPC) (7:3) [T. Shangguan, C.C. Pak, S. Ali, A.S. Janoff, P. Meers, Cation-dependent fusogenicity of an N-acyl phosphatidylethanolamine, Biochim. Biophys. Acta 1368 (1998) 171-183]. In all cases, the measured aqueous entrapment efficiencies were relatively high. To better understand how the molecular organization of these various gels affects liposome morphology, we examined samples by freeze-fracture transmission electron microscopy and X-ray diffraction. We found that phospholipid-ethanol-water gels are comprised of highly organized stacks of lamellae. A distinct feature of the gel samples that result in small unilamellar liposomes is the combination of acyl chain interdigitation and net electrostatic charge. We speculate that the mechanism of unilamellar liposome formation proceeds via formation of stalk contacts between neighboring layers similar to membrane hemifusion intermediates, and the high aqueous entrapment efficiencies make this liposome formation process attractive for use in drug delivery applications.

Association of hydrophobically-modified poly(ethylene glycol) with fusogenic liposomes.

We present results on using cooperative interactions to shield liposomes by incorporating multiple hydrophobic anchoring sites on polyethylene glycol (PEG) polymers. The hydrophobically-modified PEGs (HMPEGs) are comb-graft polymers with strictly alternating monodisperse PEG blocks (M(w)=6, 12, or 35 kDa) bonded to C18 stearylamide hydrophobes. Cooperativity is varied by changing the degree of oligomerization at a constant ratio of PEG to stearylamide. Fusogenic liposomes prepared from N-C12-DOPE:DOPC 7:3 (mol:mol) were equilibrated with HMPEGs. Affinity for polymer association to liposomes increases with the degree of oligomerization; equilibrium constants (given as surface coverage per equilibrium concentration of free polymer) for 6 kDa PEG increased from 6.1+/-0.8 (mg/m(2))/(mg/ml) for 2.5 loops to 78.1+/-12.2 (mg/m(2))/(mg/ml) for 13 loops. In contrast, the equilibrium constant for distearoylphosphatidylethanolamine-poly(ethylene glycol) (DSPE-PEG5k) was 0.4+/-0.1 (mg/m(2))/(mg/ml). The multi-loop HMPEGs demonstrate higher levels of protection from complement binding than DSPE-PEG5k. Greater protection does not correlate with binding strength alone. The best shielding was by HMPEG6k-DP3 (with three 6 kDa PEG loops), suggesting that PEG chains with adequate surface mobility provide optimal protection from complement opsonization. Complement binding at 30 min and 12 h demonstrates that protection by multi-looped PEGs is constant whereas DSPE-PEG5k initially protects but presumably partitions off of the surface at longer times.