PLGA Nanoparticle Platform for Trans-Ocular Barrier to Enhance Drug Delivery: A Comparative Study Based on the Application of Oligosaccharides in the Outer Membrane of Carriers

Introduction

The constancy of the microenvironment of the intraocular tissues and organs is protected from foreign particles by static and dynamic ocular barriers, like the tear film and cornea. The major dilemma encountered while developing new formulations of ocular drug with poor solubility is low bioavailability.¹ Other factors such as nasolacrimal drainage can necessitate recurrent drug administration. Therefore, lipophilicity, the degree of plasma protein binding and active membrane transport are prerequisites for effective ocular drugs.^2,3 Poly(lactide-co-glycolide) nanoparticles (PLGA NPs) as a carrier may effectively overcome ocular barriers owing to unique effects in terms of specific surface area, surface energy and surface atoms, and has become an effective strategy to solve the limitation of the ocular barrier.^4–6 The targeting efficiency of PLGA NPs depends on their cellular uptake, which in turn varies according to the epithelial cell types and the surface potential of the PLGA NPs itself. For instance, PLGA NPs are endocytosed and internalized by vascular smooth muscle cells through clathrin, whereas neither clathrin nor caveolin mediate endocytosis of PLGA NPs in rabbit's conjunctival epithelium cells.^7,8 Therefore, drug delivery through PLGA NPs to increase the amount of drugs transported across barriers can be selectively targeted by altering their particle size, surface potential and by introducing surface modification. Desai et al showed the effect of PLGA NPs size, concentration, and temperature on endocytosis of NPs through epithelial cells, and found that endocytosis is a process of activating endocytosis and the epithelial cell types determined the absorption of NPs.⁹ Furthermore, the hydrophilicity, colloidal stability and mucoadhesiveness of the NPs surface also affect their cellular uptake and drug transport volume. The research of Alonso et al showed that surface PEGylation can significantly improve hydrophilicity, stability and adhesion on the surface of intestinal cells of the NPs in vivo, as well as the bioavailability of the encapsulated macromolecular drugs.^10,11 In the past two decades, ophthalmic research has moved toward the formulation of novel and safe drug delivery systems to counteract eye barriers and maintain drug levels in target tissues.¹² Anterior segment drug delivery dosage forms are produced by modifying traditional topical formulations such as solutions, suspensions, emulsions, gels, and ointments. Novel advanced ocular delivery systems have been extensively investigated, such as in-situ forming gel, nanocarrier systems, inserts, and vesicular systems.^12,13 The improvement of surface hydrophilicity, targeting and transport rate of NPs via incorporation of hydrophilic and mucoadhesive biopolymers can increase their ability to penetrate the mucus layer and selectively adhere to the epithelial cells, thereby prolonging their retention, facilitating their endocytosis and increasing drug accumulation to the therapeutically significant dose.^14,15 In addition, a particle size range of 40–120 nm enables epithelial absorption through cellular uptake and paracellular pathway simultaneously.¹⁶ There was a growing need to develop new approaches that control particle size, enhance drug dissolution rate, and accordingly improve its bioavailability. Oligosaccharides like 2-hydroxypropyl-β-cyclodextrin (2-HP-β-CD) and chitosan oligosaccharide are promising biomaterials for constructing trans-ocular nano drug carriers.^17,18 Encapsulating a drug in biodegradable, biocompatible, natural or synthetic polymeric nanoparticles is one such approach. In the present study, we designed a triamcinolone acetonide-loaded PLGA nanoparticle platform for topical corticosteroids application, explored the transmembrane transport pathways and the distribution rules of the drug in the eyes, and analyzed the effect of different oligosaccharides on the physiochemical features and corneal permeability of the NPs in order to select the optimum formulation for ocular drug delivery.

Materials and Methods

Materials

Triamcinolone acetonide was purchased from the He Hui Pharmaceutical Group Co. Ltd. (Tianjin, China), PLGA from Dai Gang Bioengineering Co. Ltd. (Jinan, China), and polyvinyl alcohol (PVA) from Cola International Trade Co. Ltd. (Shanghai, China). The 2-hydroxypropyl-β-cyclodextrin (2-HP-β-CD) was a kind gift from Qian Hui Biotechnology Co. Ltd. (Zibo, China). Trehalose was obtained from Wei Jia Technology Co. Ltd. (Guangzhou, China), and chitosan oligosaccharide from AK Biotech Co. Ltd. (Shandong, China). All other reagents and solvents were of analytical reagent grade.

Preparation of Nanoparticles

Triamcinolone acetonide-loaded PLGA NPs were prepared by the single emulsion and evaporation method as previously described.¹⁹ Briefly, 100 mg PLGA and 10 mg triamcinolone acetonide were dissolved in 5 mL acetone/ethanol (4:1) mixture to form the organic phase. Later, the organic phase was slowly injected into 2% w/v aqueous solution of PVA (40 mL) using a syringe under sonication (ultrasonic probe, JY88IIN, Ningbo, China). The resulting emulsion was stirred overnight (400 rpm) at room temperature to evaporate the organic phase. The different oligosaccharide-modified NPs were prepared by first dissolving 1.5% (w/v) 2-HP-β-CD, 0.2% (w/v) trehalose or 0.02% (w/v) chitosan oligosaccharide in aqueous PVA, and subsequent steps were followed as described. The carrier materials were hydrated and swollen during preparation, and their pH and osmotic pressure were adjusted to obtain uniform, non-aggregating NPs.²⁰

Determination of Drug-Nanoparticles Interactions

Differential Scanning Calorimetry (DSC)

DSC is used to evaluate crystalline structure of the interacting molecules in terms of enthalpy changes. Briefly, 8–12 mg samples were sealed in aluminum pans and the scans (DSC4000, Elma Perkin technology company, USA) were recorded from 30 °C to 300 °C at the heating rate of 10 °C·min⁻¹ in a nitrogen atmosphere. Empty pans were used as reference.

X-Ray Diffraction (XRD)

X-ray powder diffraction analyzes crystalline structure through the diffraction effect of X-ray, and the peak positions are used to determine the presence of specific compounds. XRD of different samples were measured using D8-Advance (Bruker company, Germany) at 40 mA and 40 kV, and scanned from 8° to 80° (2θ) at room temperature.

Fourier Transform Infrared Spectroscopy (FT-IR)

Infrared spectroscopy identifies organic and inorganic compounds and some inorganic substances based on the intensity and shape of infrared absorption peaks. The samples were mixed with potassium bromide and pressed into tablets. FT-IR (Spectrum100, Elma Perkin technology company, USA) scans were taken at ambient temperature from 400 to 4000 cm⁻¹, with blank potassium bromide as reference.

Characterization of Nanoparticles

Entrapment Efficiency and Drug Loading

Entrapment efficiency (EE%) and drug loading (DL%) were used to evaluate the drug encapsulation of different nanoparticle formulations and determined by the ultrafiltration method.²¹ Briefly, freshly prepared nanoparticles suspension (0.5 mL) was pipetted into an ultrafiltration filter tube (MW: 10 kDa) and centrifuged at 9000 rpm for 30 mins. The filtrate was collected and injected into a HPLC column to determine the amount of the non-encapsulated free drug. The nanoparticles were then lyophilized and weighed. The HPLC parameters for analyzing different concentrations of triamcinolone acetonide were based on a method previously described.²² Triamcinolone acetonide contents were determined for all formulations, with an anticipated range of 200.13 ± 0.15 μg·mL⁻¹. EE% and DL% of the nanoparticles were calculated using Equations (1) and (2):²³

(1)

(2)

Particle Size Distribution and Zeta Potential Analysis

Particle size and zeta potential are important physicochemical parameters determining the homogeneity and stability of nanoparticles. The average particle size, polydispersity index (PDI), and zeta potential of the different NPs were determined by dynamic light scattering (Delsa Nano C^® particle size and ξ-potential analyzer, Beckman Coulter Inc., USA) at 25 ± 1 °C. All the samples were diluted with deionized water, and the experiment was performed thrice.

Morphological Observation Using Transmission Electron Microscopy (TEM)

The surface morphology of NPs was analyzed by transmission electron microscopy (JEM-1400, JEOL, JAPAN). A drop of the NPs dispersion was placed on a carbon-coated copper grid and air dried, followed by staining with 2% (w/v) phosphotungstic acid solution. The copper grid was dried at room temperature and observed.

In vitro Drug Release

The amount of triamcinolone acetonide released from the NPs was determined by dialysis.²⁴ Briefly, 2 mL NPs suspension was placed into a dialysis bag (SWB-2000, Tianjin Automatic Science Instrument Co. Ltd, China) of molecular weight cut-off 8 kDa, which was then immersed in 25 mL simulated tear fluid. The samples were incubated in a shaker bath at 34 ± 0.5 °C, and 2 mL aliquots of the buffer were collected at 1, 2, 4, 6, 8, 12 and 24 h, and immediately replaced with the same volume of fresh buffer. The amounts of triamcinolone acetonide released from all formulations were investigated by HPLC after membrane filtration (φ = 0.22 μm). Three independent experiments were performed simultaneously. The cumulative release rate (Q) of the drug was calculated as follows:²⁵

(3)

: drug concentration at time point (μg·mL⁻¹); : drug concentration at the sampling points (μg·mL⁻¹); : total amount of drug in nanoparticles (μg); : sampling volume (2 mL).

In vitro Evaluation of Corneal Permeation

The corneal permeation ability of the NPs was determined ex vivo in rabbit corneas. The corneas were removed and mounted on Franz diffusion cells between the donor and receptor chamber, with the epithelial surface facing the former. The receptor chamber was filled with 5 mL artificial aqueous humor, and 0.5 mL of each sample was placed in the donor chamber. The chambers were incubated at 34 ± 0.5 °C in a thermostatic water bath with continuous stirring at 200 rpm for 24 h. Two milliliters aliquots were taken from the receptor chamber at different time points, and immediately replaced with an equal volume of fresh medium. The withdrawn samples were analyzed by HPLC in triplicate after membrane filtration (φ = 0.22 μm). The data processing was calculated from the linear portion of the permeation curve according to the following equation.^26,27

The cumulative amount (Q, μg·cm⁻²) of triamcinolone acetonide in the receiving chamber was calculated using Equation (4) based on a standard calibration curve:

(4)

: drug concentration at time point (μg·mL⁻¹); : drug concentration at the sampling points (μg·mL⁻¹); : the volume of the medium in the receiving chamber (5 mL); : effective penetration area (0.5024 cm²); : sampling volume (2 mL).

The apparent permeability coefficient (, cm·s⁻¹) was calculated according to Equation (5):

(5)

: initial drug concentration; A: effective penetration area (0.5024 cm²); : the slope of cumulative permeation versus time curves.

The steady flow (J_ss, μg·s⁻¹·cm⁻²) was calculated using Equation (6):

(6)

Pharmacokinetics of Nanoparticles in Aqueous Humor

The pharmacokinetics of nanoparticles in aqueous humor was determined by microdialysis.²⁸ Healthy New Zealand albino rabbits were anesthetized by injecting urethane (1 g·kg⁻¹) into the marginal ear vein, and their body temperature was kept constant using a homeothermic blanket. After dilating the pupils with tropicamide phenylephrine eye drops (5 mg·mL⁻¹), a linear probe (CMA 30; Sweden; Cuprophane membrane; 10 mm length; molecular weight cut-off, 6 kDa) was inserted into the aqueous humor using a 25-gauge needle just above the cornea scleral limbus, and traversed through the center of the anterior chamber. The needle was then removed, and the active dialysis membrane was adjusted within the anterior chamber. The probe was secured in the correct position with surgical tapes to prevent any disturbance during sampling. After setting the pump flow rate at 10 μL·min⁻¹, the probe was perfused with normal saline till liquid was ejected from the outlet. The flow rate was then reduced to 0.5 μL·min⁻¹, and the animals were stabilized for at least 1 h before adding 180 μL of each sample (22.5 μg·kg⁻¹) onto the corneal surface. Dialyzed samples were collected every 30 min over a period of 6 h, and analyzed by HPLC. The study was approved by the Institutional Animal Care and Use committee of Guangdong Pharmaceutical University, and performed as per the guidelines of the National Institutes of Health guide for the care and use of laboratory animals.

In vivo Ocular Compatibility Test

The biocompatibility of the different PLGA NPs was determined by the irritation test. Briefly, 50 μL of a single dose formulation was administrated to the left eyes of the rabbit model, and the same volume of normal saline was applied into the right eyes (n = 3) for a period of 2 weeks. The irritation of the eyes was scored according to the Draize scale.²⁹ The animals were sacrificed after the final observation, and the eyeballs were removed and stained with H＆E for histopathological evaluation.

Pharmacokinetic Calculation and Data Analysis

The pharmacokinetic parameters were calculated using the DAS 3.0 software package (Chinese Pharmacological Society, Shanghai, China), and all values were expressed as mean ± SD. The non-compartmental pharmacokinetic model was used to calculate maximum concentration (C_max), time to reach maximum concentration (T_max), area under curve from 0 to t (AUC_0–t), mean residence time (MRT) and variance of residence time (VRT).

Results and Discussion

Preparation and Characterization of PLGA NPs

The lactide/glycolide weight ratios (LA/GA ratios) and molecular weights (MWs) of PLGA may affect the particle size, biodegradation and even corneal permeation of the NPs. Therefore, we formulated PLGA NPs with LA/GA ratios of 50:50, 75:25 and 90:10, and MWs 10 kDa, 20 kDa and 30 kDa, and analyzed the physicochemical properties of each. As shown in Figure 1, the D90 or cumulative particle size distribution of 90% NPs (LA/GA 50:50) increased with their MWs, whereas the cumulative drug release rate (%) at 24 h showed an inverse correlation with the MW of PLGA (P < 0.05). A higher MW increased the inherent viscosity of the polymer network. Therefore, the net sheer stress upon PLGA polymers is reduced during preparation of NPs, resulting in larger particle size of NPs.^23,30,31 With a constant LA/GA ratio, a higher MW of PLGA impedes formation of sufficient water-filled pores on NPs surface compared to a PLGA with lower MW, which limits drug diffusion through the NPs matrix and therefore protracts drug release.^32,33 However, the release kinetics of all PLGA NPs with different MWs followed the Higuchi model, indicating that the MWs did not significantly affect release kinetics.

Figure 1 The effects of PLGA MWs on the NPs (LA/GA 50:50) particle size and in vitro drug release.

The parameters of PLGA NPs (MW 10 kDa) like cumulative drug release rate (%) and cumulative corneal permeation per unit area (μg·cm⁻²) varied with the LA/GA ratios (Figure 2). The cumulative drug release rate (%) over 12 h decreased continuously from 55.73% to 48.98% (P < 0.05) when the LA/GA ratio was increased from 50:50 to 90:10, and a moderate decrease in the cumulative corneal permeation per unit area (μg·cm⁻²) was also observed over the same duration. PLGA is a copolymer of a hydrophobic (lactide) and a hydrophilic (glycolide) monomer in the optimal ratio that allows drug release from PLGA NPs.^34,35 Increased proportion of lactide enhances the hydrophobicity of the NPs, which slows degradation of NPs in water and reinforces the drug-NPs affinity.³⁵ Accordingly, NPs with low LA/GA ratio release a higher amount of the drug compared to NPs with high LA/GA ratio in order to achieve a relatively higher corneal permeation. Regardless of the LA/GA ratios and MW, however, the PDI values of the PLGA NPs were within 0.2 and did not differ significantly. But the zeta potential distribution of PLGA NPs with LA/GA ratio 90:10 was the largest, indicating a risk of nano-system instability.

Figure 2 The effects of PLGA LA/GA ratios on in vitro drug release and corneal permeability of the NPs (MW 10,000).

In conclusion, the PLGA NPs with LA/GA ratio 50:50 and MW 10 kDa were the smallest and showed fastest drug release and corneal permeation, and were therefore selected for subsequent analyses.

Evaluation of Drug-Polymer Interactions

The physical state of drug-loaded PLGA NPs was determined by DSC analysis of pure drug/nanoparticles physical mixtures and drug-loaded nanoparticles. As shown in Figure 3, a single sharp endothermic melting peak of triamcinolone acetonide was observed at 292.57 °C for both the pure drug and nanoparticles physical mixtures. However, the peak disappeared in the DSC spectra of all drug-loaded nanoparticles, indicating the absence of crystalline drug in the NPs or drug solvation in the amorphous carrier.³⁶ We surmised therefore that triamcinolone acetonide existed in an amorphous or disorderly crystalline phase in dispersion or a solid solution state in the polymeric NPs.

Figure 3 Differential scanning calorimetry thermograms of (A) PLGA NPs, (B) 2-HP-β-CD/PLGA NPs, (C) trehalose/PLGA NPs and (D) chitosan oligosaccharide/PLGA NPs.

XRD analysis was performed to determine the crystalline structure of triamcinolone acetonide in the NPs. As shown in Figure 4, triamcinolone acetonide displayed numerous distinct peaks at 8–30°, indicating a crystalline nature.³⁷ The physical mixtures also exhibited relatively weak peaks at the same positions, which could be attributed to the low drug content and the amorphous nature of PVA, resulting in poor crystallization. In contrast, no distinct triamcinolone acetonide peaks were seen in the different NPs, further confirming the amorphous state of the drug as observed in the DSC analysis.

Figure 4 X-ray diffraction patterns of (A) PLGA NPs, (B) 2-HP-β-CD/PLGA NPs, (C) trehalose/PLGA NPs, and (D) chitosan oligosaccharide/PLGA NPs.

The FT-IR spectra of the different formulations are shown in Figure 5. The triamcinolone acetonide spectrum showed four characteristic peaks in the range of 1708–1600 cm⁻¹, indicating its C=C and C=O stretching vibrations.^36,38 The physical mixture also had the same characteristic peaks in the same wavelength range. However, these peaks were absent in the different NPs, which instead showed a major peak at 1740 cm⁻¹. This could be attributed to the formation of a hydrogen bond between the C=O group of triamcinolone acetonide with the polymer matrix.^6,36 Combined with the XRD and DSC spectra, these results further indicate that triamcinolone acetonide is present in the nanoparticles in an amorphous form.

Figure 5 Infrared spectrograms of (A) PLGA NPs, (B) 2-HP-β-CD/PLGA NPs, (C) trehalose/PLGA NPs, and (D) chitosan oligosaccharide/PLGA NPs.

Characterization of Physical Features of Oligosaccharides/PLGA NPs

The particle size distribution and zeta potential of the NPs is shown in Figure 6. The diameters of the PLGA, 2-HP-β-CD/PLGA, trehalose/PLGA and chitosan oligosaccharide/PLGA NPs were (145.3 ± 1.36), (132.7 ± 3.34), (117.7 ± 3.10) and (137.1 ± 2.19) nm respectively. The size distribution was homogenous in all samples, with PDI values of all within 0.2. Previous studies show that drug carriers larger than 10 μm irritate the ocular surface and can even damage healthy tissue structure.³⁹ Thus, all NPs were smaller than 200 nm and suitable for topical administration. Moreover, the small size of PLGA NPs and their surface-modified forms may offer several advantages like low toxicity, improved solubility, high surface area, dissolution rate and enhanced biodistribution.^40–42

Figure 6 Particle size distribution and zeta potential of (A) PLGA NPs, (B) 2-HP-β-CD/PLGA NPs, (C) trehalose/PLGA NPs, (D) chitosan oligosaccharide/PLGA NPs.

The zeta potential of the PLGA, 2-HP-β-CD/PLGA, trehalose/PLGA and chitosan oligosaccharide/PLGA NPs were (−22.46 ± 4.76), (−19.09 ± 1.99), (−16.24 ± 4.65) and (−7.12 ± 0.75) mV respectively. Since the surface charge is an indicator of NP stability, the results indicate that PLGA NPs were the most stable, followed by trehalose/PLGA NPs, 2-HP-β-CD/PLGA NPs and chitosan oligosaccharide/PLGA NPs.³⁹

The shape and surface morphology of the NPs were assessed by TEM. The particle size of the NPs as observed by TEM were different from that measured by DLS, which is likely due to the drying step in the former that results in NPs aggregation. As shown in Figure 7, all NPs were spherical and of uniform size.

Figure 7 TEM images of (A) PLGA NPs, (B) 2-HP-β-CD/PLGA NPs, (C) trehalose/PLGA NPs, and (D) chitosan oligosaccharide/PLGA NPs.

The EE (%) of the PLGA, 2-HP-β-CD/PLGA, trehalose/PLGA and chitosan oligosaccharide/PLGA NPs were (39.1 ± 1.41%), (63.2 ± 3.51%), (47.6 ± 3.01%) and (40.7 ± 1.92%) respectively. The highest EE (%) of 2-HP-β-CD/PLGA NPs suggested a synergy between 2-HP-β-CD and the PLGA matrix that increased drug loading capacity.⁴³ However, the DL (%) of all PLGA NPs were similar, and that of 2-HP-β-CD/PLGA and trehalose/PLGA NPs were in fact lower compared to the PLGA NPs. This could be due to greater particle weight of 2-HP-β-CD and trehalose-modified PLGA NPs, which decreased the calculated DL (%) as per Equation (2).

Evaluation of in vitro Characteristics

Topical eye drops usually have low therapeutic efficacy due to poor ocular bioavailability.⁴⁴ Therefore, it is essential to formulate NPs that can sustain a therapeutically effective concentration of the drug over a certain time window. The encapsulated triamcinolone acetonide showed an initial burst release from all oligosaccharides modified PLGA NPs, and the release of trehalose/PLGA and chitosan oligosaccharides/PLGA NPs decreased thereafter. During the first 4 hours, surface-embedded or loosely bound hydrophobic drug was released rapidly from the polymer phase into the simulated tear fluid. The steady diffusion of the buffer into the polymer matrix and subsequent swelling then released the PLGA-entrapped drug. The initial burst release can help achieve the therapeutic dose of the drug in minimal time, and the later slow release maintained effective drug concentration.

As shown in Figure 8A, 89.66% of triamcinolone acetonide was released from 2-HP-β-CD/PLGA NPs into the simulated tear fluid within 12 h compared to only 55.63%, 47.35% and 48.64% from the PLGA, trehalose/PLGA and chitosan oligosaccharide/PLGA NPs respectively. This could be due to the presence of a hydrophobic cavity in 2-HP-β-CD which can accommodate and increase aqueous solubility of triamcinolone acetonide. Furthermore, the amorphous, non-crystalline nature of 2-HP-β-CD further increased its solubility. In addition, the presence of cyclodextrin in the NPs can enhance drug permeability into the cornea by fusing with the cholesterol and phospholipids present in the epithelial cell membrane.⁴⁵ Consistent with the in vitro observations, the cumulative amount of drug that permeated into the cornea from 2-HP-β-CD/PLGA NPs reached 28.71 ± 3.24 μg·cm⁻² at 8 h, which was 5.71-, 3.55- and 3.25-fold higher compared to that from PLGA, trehalose/PLGA and chitosan oligosaccharide/PLGA NPs respectively (P < 0.05) (Figure 8B).

Figure 8 (A) The cumulative percentage of triamcinolone acetonide released in artificial tear fluid. (B) Permeability of triamcinolone acetonide across excised rabbit corneas (■: PLGA NPs; ▼: 2-HP-β-CD/PLGA NPs; ▲: trehalose/PLGA NPs; ●: chitosan oligosaccharide/PLGA NPs).

The effect of triamcinolone acetonide dose on the corneal permeation of different formulations were analyzed using a series of kinetic models (Table 1). The Ritger-Peppas kinetic model was best-fitted with the PLGA, trehalose/PLGA and chitosan oligosaccharide/PLGA NPs based on the correlation coefficient (R²), whereas 2-HP-β-CD/PLGA NPs was best fitted with a first-order kinetic model that is directly proportional to the drug concentration.⁴⁶ The Ritger-Peppas kinetic model with n > 0.85 is possibly controlled by the skeleton dissolution release mechanism.^25,47 Based on the results so far, we concluded that surface modification with 2-HP-β-CD can significantly enhance the ability of NPs to penetrate the cornea and increase drug concentration in the aqueous humor.

Table 1 Release Models of Triamcinolone Acetonide from Determination Preparations Across Corneas in vitro

As shown in Table 2, 2-HP-β-CD/PLGA NPs had the greatest thus confirming its optimum corneal permeability. In addition, the for 2-HP-β-CD/PLGA NPs, chitosan oligosaccharide/PLGA NPs and trehalose/PLGA NPs were respectively 4.76, 1.38 and 1.33 folds higher compared to that of PLGA NPs (P < 0.05). The value of 2-HP-β-CD/PLGA NPs indicated that they can form a drug reservoir by adhering to the corneal epithelium and allowing sustained drug release. Therefore, administering triamcinolone acetonide via 2-HP-β-CD/PLGA NPs can prolong its corneal retention and permeation.

Table 2 Permeation Parameters of the Different Preparations Through the Excised Corneas

Pharmacokinetic Study of Aqueous Humor

Microdialysis is a well-established, minimally invasive technique for in vivo pharmacokinetics assays in different tissues, including the eye. The ocular pharmacokinetics of triamcinolone acetonide was accordingly analyzed in anesthetized rabbits. The time-concentration profiles of the drug in aqueous humor after topical application of the different formulations are shown in Figure 9, and the corresponding kinetic parameters are summarized in Table 3. Continuous dilution by tears can disrupt the nanocarriers in contact with ocular membranes, impeding more drugs from penetrating the cornea and releasing in the aqueous humor to implement their therapeutic effects.^44,48 Taken together, 2-HP-β-CD/PLGA is a highly promising nanocarrier for targeted ocular drug delivery and sustained drug release.

Table 3 Pharmacokinetics Parameters of Triamcinolone Acetonide in Aqueous Humor After Topical Instillation

Figure 9 Pharmacokinetic profiles of the NPs in aqueous humor. (■: PLGA NPs; ▼: 2-HP-β-CD/PLGA NPs; ▲: trehalose/PLGA NPs; ●: chitosan oligosaccharide/PLGA NPs).

In vivo Ocular Compatibility

The Draize test showed that neither single nor multiple-dosing administration caused any abnormities in the cornea, iris or conjunctiva of the rabbit eyes. Moreover, the corneal sections of eyeballs post-treated with different oligosaccharide-modified NPs did not show any significant differences compared to PLGA NPs (control) (Figure 10), thus confirming that all PLGA NPs were non-irritant and completely biocompatible.

Figure 10 Histopathological images of rabbit corneas treated with (A) PLGA NPs, (B) 2-HP-β-CD/PLGA NPs, (C) trehalose/PLGA NPs, and (D) chitosan oligosaccharide/PLGA NPs.

Conclusion

Mucoadhesiveness in ocular drug delivery is a robust approach that prolongs drug retention and increases the membrane permeability and intracellular uptake of drugs. Polymers like polylactic-co-glycolic acid (PLGA) and 2-HP-β-CD are often used to overcome the ocular barriers, and they also help achieve mucoadhesive ocular controlled drug delivery. The present study aimed to enhance ocular bioavailability of triamcinolone acetonide by preparing and evaluating 2-HP-β-CD/PLGA NPs. 2-HP-β-CD/PLGA NPs displayed rapid drug release and optimum corneal permeability, and the higher AUC and C_max of 2-HP-β-CD/PLGA NPs compared to PLGA, trehalose/PLGA and chitosan oligosaccharide/PLGA NPs have indicated that 2-HP-β-CD/PLGA NPs can significantly enhance the bioavailability of triamcinolone acetonide.