Novel adapter method for in vitro release testing of in situ forming implants.

In situ forming implants are injectable liquid formulations which form solid or semisolid depots following injection. This allows for minimally invasive administration, localized drug delivery, and extended drug release. Unfortunately, this drug delivery strategy lacks standardized in vitro dissolution methods due to the difficulties in recreating implant formation in vitro that is biomimicry and with reproducible and controllable shape and dimensions. In the present study, an innovative, adapter-based in vitro release testing method was developed to solve this problem. Two distinctively different in situ forming implants (a risperidone formulation (suspension) consisting of PLGA dissolved in N-methyl pyrrolidone (NMP), where risperidone powder was suspended to form a drug suspension, and a naproxen formulation (solution) consisting of PLGA dissolved in NMP, where naproxen was completely dissolved to form a solution), were used as model in situ-forming implants. The results revealed that the implants formed in the custom-designed adapter with a water-dissolvable polyvinyl alcohol (PVA) film were bio-mimicking and reproducible in both shape and burst release of drug according to rabbit data. For both the suspension and solution formulations, this adapter-based in vitro release testing method resulted in consistent release data. Compared with a direct injection in vitro release testing method, the release profiles generated using the adapter-based method were capable of distinguishing the different release phases (initial release within 24 h, diffusion-facilitated release, and degradation-controlled release). In addition, the adapter-based method could discriminate formulation and dissolution apparatus changes and could be utilized to develop accelerated release testing methods. This adapter-based method has the promise of wide use in release testing of in situ forming implant formulations and has the potential to be used in the development of in vivo-predictive in vitro release methods.

Effect of implant formation on drug release kinetics of in situ forming implants.

In situ forming implants are attractive long-acting implant dosage forms due to their: i) ability to control drug release; ii) simple manufacturing process; and iii) minimally invasive administration. In situ forming implants are typically made of a drug, solvent, and a biocompatible polymer that controls drug release. Once injected in the subcutaneous tissue, they form solid depots through solvent/non-solvent exchange and phase separation of the biodegradable polymer (such as poly (lactic-co-glycolic acid), PLGA and poly (lactic acid), PLA). However, the mechanism of implant formation and the changes in their microstructure that determine drug release behavior are not fully understood. Furthermore, there is no standardized in vitro release testing method for in situ forming implants due to limitations in recreating bio-relevant and reproducible implant formation in vitro with controllable implant shape, dimensions and surface-to-volume ratio. In the present study, bio-relevant implant formation was recreated in vitro by testing five different methods to determine their effect on drug release kinetics, reproducibility, and internal microstructure formation. The leuprolide acetate formulation Eligard® was used as a model in situ-forming implant, consisting of lyophilized leuprolide acetate, and PLGA dissolved in N-methyl pyrrolidone. The results revealed that the in vitro implant formation method is a crucial step in the dissolution testing process that significantly impacts the release profile of in situ forming implants. An implant formation method that utilizes dissolvable polyvinyl alcohol (PVA) films allowed for initial drug burst release control by modulating implant dimensions (i.e. surface area) and resulted in reproducible in vitro release profiles. In addition, implant formation was shown to affect the internal microstructure of in situ forming implant and was the main factor controlling the release profile which consisted of an initial release phase followed by a release plateau (lag phase) and then a second erosion-controlled release phase.

An NMR Protocol for In Vitro Paclitaxel Release from an Albumin-Bound Nanoparticle Formulation.

The paclitaxel protein-bound particles for injectable suspension (marketed under the brand name Abraxane®) contains nanosized complexes of paclitaxel and albumin. The molecular interaction between paclitaxel and albumin within the higher-order nanostructure is analytically challenging to assess, as is any correlation of differences to differences in therapeutic effect. However, because the higher-order nanostructures may affect the paclitaxel release, a suitable in vitro assay to detect potential differences in paclitaxel release between comparator lots and products is desirable. Herein, solution NMR spectroscopy with a T2-filtering technique was developed to detect paclitaxel signal while suppressing albumin signals to follow the released paclitaxel in the NMR tube upon dilution. The non-invasive nature of NMR allows for precise measurement of a full range of dilution-induced drug release percentage from 14 to 92% without any sample extraction. The critical concentration of the drug product (DP) at 50% of release was 0.63 ± 0.04 mg/mL in PBS buffer. In addition, 2D diffusion ordered NMR spectroscopy (DOSY) results revealed that the released paclitaxel experiencing slightly slowed diffusion rates than free paclitaxel, which was attributed to paclitaxel in equilibrium with albumin-bound states. Collectively, the dilution-based NMR method offered an analytical approach to investigate physicochemical attributes of complex injectable products with minimal needed sample preparation and perturbation to nanoparticle formulation.

Bacteriomimetic poly-γ-glutamic acid surface coating for hemocompatibility and safety of nanomaterials.

Poly-γ-glutamic acid (PGA), a major component of the bacterial capsule, is known to confer hydrophilicity to bacterial surfaces and protect bacteria from interactions with blood cells. We tested whether applying a bacteriomimetic surface coating of PGA modulates interactions of nanomaterials with blood cells or affects their safety and photothermal antitumor efficacy. Amphiphilic PGA (APGA), prepared by grafting phenylalanine residues to PGA, was used to anchor PGA to reduced graphene oxide (rGO) nanosheets, a model of hydrophobic nanomaterials. Surface coating of rGO with bacterial capsule-like APGA yielded APGA-tethered rGO nanosheets (ArGO). ArGO nanosheets remained stable in serum over 4 weeks, whereas rGO in plain form precipitated in serum within 5 minutes. Moreover, ArGO did not interact with blood cells, whereas rGO in plain form or as a physical mixture with PGA formed aggregates with blood cells. Mice administered ArGO at a dose of 50 mg/kg showed 100% survival and no hepatic or renal toxicity. No mice survived exposure at the same dose of rGO or a PGA/rGO mixture. Following intravenous administration, ArGO showed a greater distribution to tumors and prolonged tumor retention compared with other nanosheet formulations. Irradiation with near-infrared light completely ablated tumors in mice treated with ArGO. Our results indicate that a bacteriomimetic surface modification of nanomaterials with bacterial capsule-like APGA improves the stability in blood, biocompatibility, tumor distribution, and photothermal antitumor efficacy of rGO. Although APGA was used here to coat the surfaces of rGO, it could be applicable to coat surfaces of other hydrophobic nanomaterials.

Layer-by-layer nanoparticle platform for cancer active targeting.

Nanoparticles as drug delivery carriers have been investigated over the last few decades, particularly for cancer treatment. The rationale in developing such nanoparticles is to maximize drug efficacy while minimizing toxic side effects. This can be most effectively achieved through target specific drug delivery. A novel biocompatible nanoparticle platform prepared using the core-shell self-assembly technique is reported. The core consists of calcium phosphate which is biocompatible and pH-sensitive, and the shell is composed of biocompatible polymers (hyaluronic acid, CD44 targeting moiety; and chitosan, physical cross-linker). Cisplatin was selected as a model drug and incorporated between the core and the shell. The nanoparticle composition was optimized for high serum stability and low protein binding. These nanoparticles demonstrated target specific delivery in human lung cancer cells (which overexpress CD44 receptors). The targeting ability of the nanoparticles was confirmed with an 8-fold increase of drug efficacy (IC50) compared to cisplatin. Furthermore, the pH-sensitive core of the nanoparticle platform led to controlled drug release through destabilization in acidic conditions. This platform technology provides a simple approach for the design of targeted biocompatible nanoparticles for cancer therapy.

Carboxymethyl Hyaluronan-Stabilized Nanoparticles for Anticancer Drug Delivery.

Carboxymethyl hyaluronic acid (CMHA) is a semisynthetic derivative of HA that is recognized by HA binding proteins but contains an additional carboxylic acid on some of the 6-hydroxyl groups of the N-acetyl glucosamine sugar units. These studies tested the ability of CMHA to stabilize the formation of calcium phosphate nanoparticles and evaluated their potential to target therapy resistant, CD44(+)/CD24(-/low) human breast cancer cells (BT-474EMT). CMHA stabilized particles (nCaP(CMHA)) were loaded with the chemotherapy drug cis-diamminedichloroplatinum(II) (CDDP) to form nCaP(CMHA)CDDP. nCaP(CMHA)CDDP was determined to be poorly crystalline hydroxyapatite, 200 nm in diameter with a -43 mV zeta potential. nCaP(CMHA)CDDP exhibited a two-day burst release of CDDP that tapered resulting in 86% release by 7 days. Surface plasmon resonance showed that nCaP(CMHA)CDDP binds to CD44, but less effectively than CMHA or hyaluronan. nCaP(CMHA-AF488) was taken up by CD44(+)/CD24(-) BT-474EMT breast cancer cells within 18 hours. nCaP(CMHA)CDDP was as cytotoxic as free CDDP against the BT-474EMT cells. Subcutaneous BT-474EMT tumors were more reproducibly inhibited by a near tumor dose of 2.8 mg/kg CDDP than a 7 mg/kg dose nCaP(CMHA)CDDP. This was likely due to a lack of distribution of nCaP(CMHA)CDDP throughout the dense tumor tissue that limited drug diffusion.

Cationic drug-derived nanoparticles for multifunctional delivery of anticancer siRNA.

Combined treatment of anticancer drugs and small interfering RNAs (siRNAs) have emerged as a new modality of anticancer therapy. Here, we describe a co-delivery system of anticancer drugs and siRNA in which anticancer drug-derived lipids form cationic nanoparticles for siRNA complexation. The anticancer drug mitoxantrone (MTO) was conjugated to palmitoleic acid, generating two types of palmitoleyl MTO (Pal-MTO) lipids: monopalmitoleyl MTO (mono-Pal-MTO) and dipalmitoleyl MTO (di-Pal-MTO). Among various lipid compositions of MTO, nanoparticles containing mono-Pal-MTO and di-Pal-MTO at a molar ratio of 1:1 (md11-Pal-MTO nanoparticles) showed the most efficient cellular delivery of siRNA, higher than that of Lipofectamine 2000. Delivery of red fluorescence protein-specific siRNA into B16F10-RFP cells using md11-Pal-MTO nanoparticles reduced the expression of RFP at both mRNA and protein levels, demonstrating silencing of the siRNA target gene. Moreover, delivery of Mcl-1-specific anticancer siRNA (siMcl-1) using md11-Pal-MTO enhanced antitumor activity in vitro, reducing tumor cell viability by 81% compared to a reduction of 68% following Lipofectamine 2000-mediated transfection of siMcl-1. Intratumoral administration of siMcl-1 using md11-Pal-MTO nanoparticles significantly inhibited tumor growth, reducing tumor size by 83% compared to untreated controls. Our results suggest the potential of md11-Pal-MTO multifunctional nanoparticles for co-delivery of anticancer siRNAs for effective combination therapy.

Anionic amino acid-derived cationic lipid for siRNA delivery.

Viable siRNA therapeutic strategies require the concurrent development of effective and safe delivery systems. Here, we described the synthesis of a new cationic lipid, N,N''-dioleylglutamide (DG), and evaluated DG-based liposomes as an siRNA delivery system. DG, an amino acid derivative, was synthesized by peptide bond linkage of oleylamine to each carboxylic acid group of glutamic acid. Gel retardation assays showed that DG-based cationic liposomes and siRNA began to form complexes from the N/P ratio of 1.8. The viability of A549, HeLa and WM266.4 cells was significantly higher after treatment with DG-based liposomes than with Lipofectamine 2000 and cationic 3beta-[N-(N',N'-dimethylaminoethane)-carbamoyl] cholesterol (DC-Chol)-based liposomes. The DG-based cationic liposomes could effectively deliver a fluorescent model siRNA into A549, HeLa, and WM266.4 human cancer cell lines, showing at least 2-fold higher fluorescence mean intensity values than did Lipofectamine 2000. When survivin-specific siRNA was delivered to cells in lipoplexes, survivin mRNA levels were reduced by DG-based liposomes to the higher extent than Lipofectamine 2000 and DC-Chol-based liposomes. When red fluorescent protein (RFP)-expressing cells were treated with RFP-specific siRNA (siRFP), RFP expression significantly decreased in cells treated with DG-based liposomes. Molecular imaging revealed that intratumoral injection of siRFP and DG-based liposome complexes significantly reduced fluorescence in RFP-expressing tumor tissues in mice. These results suggest that DG-based cationic liposomes would be of value for cellular delivery and in vivo local delivery of siRNA.

Novel cationic cholesterol derivative-based liposomes for serum-enhanced delivery of siRNA.

Most cationic liposomes used for gene delivery suffer from reduced transfection efficiency in the presence of serum. In this study, we report serum-enhanced delivery efficiency of siRNA via the use of newly synthesized liposomes that contain cationic lipids. Two cholesterol derivatives, cholesteryloxypropan-1-amine (COPA) and cholesteryl-2-aminoethylcarbamate (CAEC), were synthesized. A fluorescein label was then used to visualize cellular uptake of small interfering RNA (siRNA) via COPA or CAEC-based liposomes. The presence of serum had different effects on the cellular delivery of siRNA when siRNA was complexed to different cationic liposomes. CAEC-based liposomes showed significantly reduced cellular delivery of siRNA in serum-containing media as compared to serum-free media. Conversely, COPA-based liposomes (COPA-L) provided serum-enhanced delivery of siRNA in Hepa1-6, A549, and Hela cell lines. Following delivery of the oncogene survivin-specific siRNA, COPA-L reduced the mRNA expression levels of the target gene more efficiently than did Lipofectamine 2000. The delivery of green fluorescent protein-specific siRNA with COPA-L reduced the expression of green fluorescent protein in 293T stable cell lines. The apoptosis of Hepa1-6 significantly increased by delivery of survivin-specific siRNA by COPA-L. Additionally, Hepa1-6, A549, and Hela cells were >80% viable after treatment with COPA-L. These results suggest that the newly synthesized cholesterol derivative, COPA-L, could be further developed as a serum-enhanced delivery system of siRNA.

Zygomaticotemporal nerve passage in the orbit and temporal area.

Injury of the zygomaticotemporal nerve causes paresthesia in its distributed area, and its entrapment induces protractive pain in case of manipulation of the orbital lateral wall, a Gillies or Dingman reduction procedure for a zygomatic fracture, or an endoscopic subperiosteal facelift. The aim of this study was to elucidate the surgical anatomy of the zygomaticotemporal nerve in the orbit and temporal area. Twenty hemifaces from 10 adult Korean cadavers (10 male and 10 female) were used in the study. The zygomaticotemporal nerve ran along the lateral wall of the orbit, passed through the zygomaticotemporal foramen, and reached to the temporal fossa. The point where the zygomaticotemporal nerve appears at the margin of zygomatic bone is defined as the vulnerable point (Vp); hence, the nerve might be injured during surgical procedures. The Vp was 11.29 +/- 2.65 mm below the zygomaticofrontal suture and 21.76 +/- 2.76 mm from the superior border of zygomatic arch. The most vulnerable points were within a 10-mm diameter circle (vulnerable zone). Its center was 11 mm from the zygomaticofrontal suture at an angle of 45 degrees inferolaterally. The zygomaticotemporal nerve ran between the deep layer and the superficial layer of the deep temporal fascia. It ran just superficial to the deep layer of the deep temporal fascia toward the temporal area and innervated the temporal skin. The area innervated by terminal branches of the zygomaticotemporal nerve included a circle with 30-mm diameter, with the center located 10 mm superior to the top of the auriculocephalic sulcus and 30 mm lateral to the lateral canthus. Precautions should be taken when working in the area of the vulnerable zone during the Dingman procedure involving periorbital incision in case of zygomatic fracture.

Cutaneous distribution of infraorbital nerve.

The aim of this study is to elucidate precisely the cutaneous distribution of the infraorbital nerve. Ten hemifaces of five Korean adult cadavers (2 males and 3 females) were subjected to the dissection. The cutaneous branches of the infraorbital nerve were distributed over the infraorbital area, which bounds on superiorly the lower eyelid margin, inferiorly the horizontal line crossing the mouth corners, medially 0.5 cm to midline, and laterally 2 cm lateral to the temporal canthus of the eyes. The infraorbital nerve had 19.5 branches (range, 15-24 branches). The mean area supplied by the infraorbital nerve was 25.8 cm2 (range, 24.0-28.2 cm2). The mean area of the superior labial branch was 13.1 cm2 (range, 11.2-14.3 cm2) and broader than either the 7.5 cm2 (range, 6.6-8.8 cm2) of the lower palpebral branch or the 7.6 cm2 (range, 6.7-9.3 cm2) of the external nasal branch. The external nasal branch was overlapped with the lower palpebral and superior labial branch, but the last two branches do not overlap each other. The nonoverlapped branch of the infraorbital nerve exhibits a restricted anesthesia, but the overlapped branch sustains sensory perception to some extent when being damaged.