Thermosensitive hydrogel based on chitosan and its derivatives containing medicated nanoparticles for transcorneal administration of 5-fluorouracil
Received 6 September 2016
Accepted for publication 1 November 2016
Published 16 January 2017 Volume 2017:12 Pages 633—643
Checked for plagiarism Yes
Review by Single anonymous peer review
Peer reviewer comments 4
Editor who approved publication: Dr Thomas J Webster
Angela Fabiano,1 Ranieri Bizzarri,2 Ylenia Zambito1
1Department of Pharmacy, University of Pisa, 2NEST, Istituto Nanoscienze CNR (CNR-NANO) and Scuola Normale Superiore, Pisa, Italy
Abstract: A thermosensitive ophthalmic hydrogel (TSOH) – fluid at 4°C (instillation temperature), semisolid at 35°C (eye temperature), which coupled the dosing accuracy and administration ease of eyedrops with the increased ocular bioavailability of a hydrogel – was prepared by gelling a chitosan hydrochloride (ChHCl) solution (27.8 mg/mL) medicated with 1.25 mg/mL 5-fluorouracil (5-FU) with β-glycerophosphate 0.8 mg/mL. Polymer mixtures, where Ch was partially (10%, 15%, or 20%) replaced by quaternary ammonium–chitosan conjugates (QA-Ch) or thiolated derivatives thereof, were also used to modulate 5-FU-release properties of TSOH. Also, Ch-based nanoparticles (NPs; size after lyophilization and redispersion 341.5±15.2 nm, polydispersity 0.315±0.45, ζ-potential 10.21 mV) medicated with 1.25 mg/mL 5-FU prepared by ionotropic cross-linking of Ch with hyaluronan were introduced into TSOH. The 5-FU binding by TSOH polymers in the sol state was maximum with plain Ch (31.4%) and tended to decrease with increasing QA presence in polymer mixture. 5-FU release from TSOH with or without NPs was diffusion-controlled and linear in √t. The different TSOH polymers were compared on a diffusivity basis by comparing the slopes of √t plots. These showed a general decrease with NP-containing TSOH, which was the most marked with the TSOH, where Ch was 20% replaced by the derivative QA-Ch50. This formulation and that not containing NP were instilled in rabbits and the 5-FU transcorneal penetration was measured by analyzing the aqueous humor. Both TSOH solutions increased the area under the curve (0–8 hours) 3.5 times compared with the plain eyedrops, but maximum concentration for the NP-free TSOH was about 0.65 µg/mL, followed by a slow decline, while the NP-containing one showed a plateau (0.25–0.3 µg/mL) in a time interval of 0.5–7 hours. This is ascribed to the ability of this TSOH to control drug release to a zero order and that of NPs to be internalized by corneal cells.
Keywords: thermosensitive hydrogels, chitosan nanoparticles, chitosan multifunctional derivatives, 5-fluorouracil, ocular delivery
Ocular drug delivery is one of the more challenging tasks for pharmaceutical scientists. The unique structure of the eye restricts the entry of drug molecules at the required site of action. More than 90% of the marketed ophthalmic formulations are produced in the form of eyedrops, which are washed away from the eye by various mechanisms, ie, lachrymation, tear dilution, and turnover, resulting in low ocular bioavailability of drugs. Moreover, the human cornea, comprising the epithelium, substantia propria, and endothelium, restricts the entry of drug molecules.1 As a result of the action of these factors, less than 5% of the administered drug enters the eye.
Colloidal carriers have been widely exploited in the field of drug-delivery science, because they provide more selective targeting with sustained release of molecules at the desired site and can be used in the treatment of diseases affecting the anterior and the posterior segments of the eye. An ideal therapy requires selective targeting of an active agent for various eye diseases, such as choroidal neovascularization, diabetic retinopathy, and solid tumors. The retina does not possess any lymphatic system or angiogenesis, so this part of the eye has similar features to a solid tumor with enhanced permeability and retention effects.2,3 Delivery of a drug via nanotechnology mainly pursues the following three objectives: 1) enhancing drug permeation, 2) controlling drug release, and 3) drug targeting.3 Another interesting approach to ocular drug delivery is the use of hydrogel systems. Hydrogels are hydrophilic polymers able to swell in water or aqueous solvents. Preformed hydrogels do not allow accurate or reproducible administration of drugs, and after administration they often produce blurred vision, crusting of eyelids, and lachrymation. Therefore, the most promising approach is the use of in situ-forming hydrogels that can be instilled as eyedrops and undergo immediate gelation when in contact with the eye.4 In situ-forming hydrogels provide a response to environmental changes;5,6 indeed, they are liquid upon instillation and undergo phase transition in the ocular cul-de-sac to form viscoelastic gels.7,8 This class of biomaterials was first presented by Chenite et al.9 They described polymer–polyol salt aqueous solutions, which could be held liquid below room temperature and turned into monolithic gels at body temperature. In light of this information, in the present study, we felt it intriguing to combine the characteristics of a thermosensitive hydrogel with those of nanoparticles (NPs) to promote transcorneal penetration of 5-fluorouracil (5-FU). Among the various mucoadhesive polymers described in the literature, the cationic polymer chitosan (Ch) has been considered the polymer of choice to prepare NPs and hydrogels, because of its positive charge and ability to interact intimately with the cornea and conjunctiva, which are negatively charged. In the hydrogel formulation, in some cases, small fractions of Ch were substituted with quaternary ammonium–Ch conjugates (QA-Ch) or thiolated derivatives thereof (QA-Ch-SH),10 because of their improved mucoadhesiveness and ability to promote transcorneal penetration.11 NPs medicated with 5-FU were lyophilized and dispersed in the systems in the sol state. The formulations were compared on the grounds of their affinity with the drug and in vitro drug-release properties, in order to select the system on which to carry out in vivo pharmacokinetic studies. To this end, such a system had to be liquid at manageably low temperatures, undergo an immediate gelation when in contact with the physiological temperature of the eye, and be suitable for in vivo administration to rabbits. 5-FU was chosen as the model drug, as it is the drug of choice for the treatment of ocular cancer. A 1% 5-FU solution is currently being used by ophthalmologists, which is a high concentration for ophthalmic application. Bioavailability in the anterior segment of the eye is less than 5% of the applied dose because of drainage, lachrymation, and poor retention at the absorption surface.12 The ability of the selected NP-containing hydrogel to enhance transcorneal penetration of 5-FU compared to traditional eyedrops and produce a sustained drug level in the aqueous humor was tested in this study.
Materials and methods
5-FU, Ch of low molecular weight, β-glycerophosphate (β-GP) disodium salt, and trehalose dehydrate were from Sigma-Aldrich (St Louis, MO, USA). ChHCl was prepared as previously described.13 Fluorescein isothiocyanate (FITC) was from Sigma-Aldrich. The QA-Ch conjugates QA-Ch50 and QA-Ch60 and thiolated derivatives QA-Ch50-SH and QA-Ch60-SH were synthesized from Ch according to Zambito et al.10 For the Ch derivatives, the figures 50 and 60 refer to the respective temperatures (°C) at which the synthesis was carried out. Hyaluronic acid (viscometric molecular weight 470 kDa) was prepared as described by Zambito et al.10 Nylon 6.6 and cellulose membranes were soaked for at least 24 hours in water before use. All aqueous solutions/dispersions were prepared with deionized water. All other chemicals and solvents were of reagent grade. FITC labeling of Ch was carried out as previously described.14–17
Quantitative analysis of 5-FU
Quantitative analysis of 5-FU was carried out by high-performance liquid chromatography (HPLC). The apparatus (PerkinElmer, Waltham, MA, USA) consisted of a series 200 pump, 20 μL Rheodyne injector, ultraviolet detector, and Turbochrom Navigator HPLC software (PerkinElmer) for data integration. A Spheri-5 RP-18 5 μm 250×4.6 mm column was used. The mobile phase (flow rate 0.6 mL/min) was KH2PO4 0.05 M triethylamine 0.1%, and ultraviolet detection was set at 266 nm. Standard curves were constructed by analyzing six standard drug solutions in the eluent. All standard curves produced on different days were linear (r2>0.998) in the concentration range 0.3–5 μg/mL (limit of quantification 0.2 μg/mL, limit of detection 0.07 μg/mL). The retention time was 7.5 minutes. The concentration of each unknown sample, analyzed by the aforementioned, was determined using a standard curve produced on the same day.
Preparation of medicated NPs
FITC-labeled or unlabeled Ch-based NPs medicated with 5-FU were self-assembled upon portion-wise addition of a 950 μL volume of hyaluronic acid (1 mg/mL) and 5-FU (5.21 mg/mL) in demineralized water to 5 mL of 1 mg/mL FITC-labeled or unlabeled ChHCl in demineralized water. The final 5-FU concentration in the NP dispersion was 1.25 mg/mL, corresponding to the concentration contained in the commercial 5-FU eyedrops. Following preparation, the NPs were checked for size and ζ-potential (Nano ZS90; Malvern Instruments, Malvern, UK). Their drug-entrapment efficiency (EE) was evaluated by subjecting the dispersion to centrifugation (28,800 rpm for 1 hour at 4°C) and analyzing the supernatant for the drug by HPLC. EE was expressed as follows:
EE = (Mt − Ms)/Mt
where Mt is the total drug used for the preparation and Ms the mass found in the supernatant.
To obtain stable systems, the drug-loaded NP dispersions were lyophilized following the addition of 250 mg of trehalose dehydrate as cryoprotectant (VirTis Advantage; thermal treatment step −35°C for 180 minutes, drying cycle steps −30°C for 360 minutes, −10°C for 360 minutes, 10°C for 240 minutes, and 25°C for 180 minutes). The dispersions were able to be regenerated from the respective lyophilized products by adding 5 mL of water under gentle stirring.
Preparation of thermosensitive hydrogels medicated with 5-FU
Thermosensitive ophthalmic hydrogel (TSOH) was prepared by dissolving a mass of 500 mg of Ch, alone or mixed with different fractions (10%, 15%, or 20%) of Ch derivatives, namely, QA-Ch50, QA-Ch60, QA-Ch50-SH, or QA-Ch60-SH, in 18 mL of a 0.08 M HCl solution. The resulting solutions were kept under magnetic stirring at 4°C, and an adequate volume of β-GP solution (0.8 g/mL) was added dropwise. The resulting solution was heated to 35°C, after which a sol–gel transition was organoleptically evident. Medicated hydrogels containing 1.25 mg/mL 5-FU were able to be obtained by the aforementioned procedure. 5-FU only or lyophilized 5-FU-medicated NPs were added to the initial Ch-based solution. The content in Ch and Ch derivative of each formulation and the volume of β-GP necessary for its gelation are reported in Table 1. The formulations were given the codes Ch + QAx-Chy or Ch + QAx-Chy-SH, where x and y are two figures: x representing the fraction of Ch derivative in the polymer mixture (10%, 15%, or 20%) and y the type of Ch derivative (50 or 60).
Table 1 Composition of TSOH tested
Confocal microscopy and image analysis
To evaluate the possibility of redispersing lyophilized NP into hydrogel systems, the lyophilized FITC-labeled Ch-based NPs, prepared as described in the “Preparation of medicated NPs” section, were dispersed in the Ch + QA20-Ch50 TSOH at room temperature and observed under confocal laser-scanning microscopy (TCS SP5, Leica Microsystems, Wetzlar, Germany). Images were captured at 21°C and 35°C with the system in liquid and gel states, respectively. Excitation wavelength was set at 488 nm (10–20 μW power emission at objective), whereas emission was collected in the 500–550 nm range. Scanning speed was set at 400 lines per second for an image format of 512×512 pixels. A 63×1.25 numeric-aperture water objective was used, setting the pinhole aperture of the confocal system at 1 Airy unit.
Dynamic dialysis studies
A well-known procedure and underlying theory18,19 was used to assess reversible drug binding by Ch in fluid solution or the surface of the NPs in fluid dispersion. The diffusion cell, apparatus, and procedure were the same as those described in Bottari et al.18 These were used at a thermostat temperature of 35°C. The dialysis membrane, permeable to the drug and impermeable to the polymers and NPs, was made of porous cellulose (cutoff 12.5 kDa). At t=0, 5 mL of medicated NPs, regenerated after lyophilization, were introduced in the donor compartment of the cell. Sink conditions were maintained in the receiving phase (100 mL of demineralized water). Drug transport across the membrane was assessed by analyzing the receiving phase at intervals for the drug by HPLC. At the end of each run, the donor phase was withdrawn from the cell and checked for particle size, as reported in the “Preparation of medicated NPs” section. Dialysis was also carried out, using the same procedure and membrane type, for the plain-drug solution (control) and this solution containing 0.25 mg/mL of ChHCl dissolved in water.
Interrupted-dialysis experiments were carried out to gain information on drug release from NPs while concurrently checking data according to suggestions from Zambito et al.19 To this purpose, the dialysis, carried out as described in the “Dynamic dialysis studies” section, was stopped after an established time from the start and the drug fraction contained in each of the NP matrix, NP-dispersion medium, and acceptor medium had been determined. This procedure was repeated, running the dialysis for different times, to construct the plots of the drug fraction in each phase versus time. To determine the drug fraction in the dispersion medium and calculate that in the NP matrix, ultracentrifugation of the donor phase followed by analysis of the supernatant was carried out.
Determination of drug–polymer interactions in TSOH
These interactions were determined as they could be determinant to in vivo drug residence in precorneal area, and thereby, to drug ocular bioavailability.
The dynamic dialysis technique described in the “Dynamic dialysis studies” section was used at the temperature of 4°C to determine drug–polymer interactions for the TSOH systems in the sol state, the composition of which is listed in Table 1. At t=0, 5 mL of medicated formulation was introduced in the donor compartment of the cell. Sink conditions were maintained in the receiving phase (100 mL of HCl 0.08 M and β-GP). Drug transport across the membrane was assessed by analyzing the receiving phase at intervals for the drug. In the course of a typical day of this study, the control was run in the first place, followed by sequential testing of two TSOH systems, and finally the control was repeated, without disassembling the membrane between runs. With this procedure, the slopes of the two control runs were not significantly different (Student’s t-test, P<0.05). This procedure allowed the daily, two-by-two determination of drug binding for the TSOH listed in Table 1. At the end of each run, the donor phase was withdrawn for particle-size checking. A fresh membrane was used each day.
In this case, the phase-equilibration technique, already described in detail in the literature,20 was used. In brief, the apparatus consisted of six cells, each made of two hemicells, one of which in all cases contained a 0.2 cm thick layer (2 mL) of gel of known drug concentration (1.25 mg/mL) separated by a nonporous nylon 6.6 membrane (surface area 10.2 cm2) from 7 mL of drug solution in phosphate buffer (PB; pH 7.4, 0.13 M) contained in the other hemicell. The initial drug concentration in the PB-containing hemicells was different among the different cells and spanned a range supposed to encompass the unknown equilibrium concentration with the gel. Each gel-containing hemicell was tightly connected with a PB-containing one by a clamp, and at time 0, the six assemblies were simultaneously shaken in a thermostatic water bath at 35°C. In each cell, the drug tended to equilibrate between the gel and PB phases via the membrane. After an appropriate interval (6 hours), sufficient for a positive or negative concentration change in each solution in PB to be detectable, such a change was determined and plotted vs the corresponding initial concentration. The resulting plot allowed calculation of the bound-drug fraction.
Studies on 5-FU release from TSOH
5-FU release from TSOH was carried out using a specially designed Teflon cell. The gel (0.5 mL, 1.25 mg/mL), containing (or not) medicated NPs, was introduced in the cylindrical cavity of the cell (diameter of the available area for diffusion 50 mm). A porous cellulose membrane (cutoff 12.5 kDa), kept in place by a circular Teflon plate and O-ring gasket, was used to separate the gel from the receiving phase (30 mL of PB, pH 7.4, 0.13 M). For use, the filled cell was placed in a jacketed beaker (internal height 11 cm, internal diameter 10 cm) connected with a constant-temperature bath and circulator set at 35°C. At time 0, the preequilibrated receiving phase was introduced in the beaker and stirred with a 300 rpm synchronous motor. Drug release was determined by analyzing the receiving phase at intervals.
In vivo studies
For in vivo tests, four types of medicated ophthalmic drops were prepared, with the following compositions: 1) 5-FU in PB (1.25 mg/mL, control, 310 mOsm), 2) the thermosensitive Ch solution containing 1.25 mg/mL 5-FU (210 mOsm), 3) the thermosensitive Ch + QA20-Ch50 solution containing 1.25 mg/mL 5-FU (367 mOsm), and 4) a dispersion of Ch-based NPs, medicated with 1.25 mg/mL 5-FU, in the thermosensitive Ch + QA20-Ch50 solution (416 mOsm). The eyedrops described in 1 had the same solvent and drug concentration as the commercial eyedrops.
Male New Zealand albino rabbits weighing 3–3.5 kg maintained under standard housing conditions were used. They were treated as prescribed in the Guide for the Care and Use of Laboratory Animals (revised 1985). All experiments were carried out under veterinary supervision, and the protocols were approved by the scientific ethics committee of the University of Pisa and the Italian Ministry of Education, Universities, and Research. The irritation, possibly caused in rabbit eyes by the ophthalmic drops, was evaluated by searching eyes for signs of conjunctival/corneal edema and/or hyperemia at the end of each in vivo experiment.21 For measurement of 5-FU intraocular penetration, preparations were made to 4°C, then one drop (50 μL) of each was instilled in the lower conjunctival sac. At preestablished times, rabbits were anesthetized by instilling one drop of Novesina®, then ~60 μL of aqueous humor was aspirated from the anterior chamber. For analysis, each sample was mixed with acetonitrile (1:2), then it was centrifuged and the supernatant subjected to evaporation of the acetonitrile by heating the mixture to 50°C under an airstream. The aqueous product was then lyophilized. The resulting lyophilized product was redispersed in a volume of mobile phase corresponding to the volume of the sample of aqueous initially withdrawn and analyzed by HPLC.22
The statistical significance of linear patterns was evaluated by subjecting data to linear regression analysis and computing the relevant slope and intercept and coefficient of determination (r2). The number of data points for each linear regression is specified in the text, table title, or figure caption. The number of repeats for the values listed in the tables is specified in the table title. Each data point of in vitro and in vivo nonlinear plots is the mean ± standard deviation of at least three repeats. The area under the curve (AUC) for the aqueous humor was calculated by the linear trapezoidal rule between 0 and 8 hours. The statistical methods described by Schoenwald et al23 were used to compare AUC values. The significance of differences was evaluated by Student’s t-test (P<0.05).
Results and discussion
Characteristics of medicated NPs immediately after preparation or regeneration after lyophilization
Mean particle size, polydispersity index (PI), EE, and ζ-potential values for freshly prepared NPs were 285.6±36.1 nm, 0.32±0.05, 36.6%±3.1%, and 10.32 mV, respectively, while the corresponding values for NPs regenerated from the lyophilized products were 341.5±15.2 nm, 0.31±0.04, 34.9%±2.9%, and 10.21 mV. In all cases, the PI values pointed to sufficiently homogeneous size distribution according to the literature.24–26 These results altogether indicated that the NPs could effectively be protected from mechanical stress caused by ice crystallization by adding the cryoprotectant trehalose.
Confocal microscopy and image analysis
The confocal images for FITC-labeled medicated NPs dispersed in the Ch + QA20-Ch50 TSOH are presented in Figure 1. Figure 1A refers to the fluid dispersion at 21°C (room temperature), while Figure 1B refers to the semisolid hydrogel at 35°C. Figure 1C is a magnified detail of Figure 1B. As can be seen, NPs are dispersed in either the liquid or in situ-forming hydrogel, the gelation of which did not involve any important modifications in NP-dispersion degree. Dimensional analysis of particles is reported in Figure 2. In particular, fluorescence was analyzed along a line equatorially crossing an NP, and the resulting fluorescence profile was fitted to a Gaussian function.27,28 A full width at half maximum of the Gaussian curve of about 360 nm was determined, which corresponded to the NP diameter and was not significantly different from that of freshly prepared NPs, reported in the “Characteristics of medicated NPs immediately after preparation or regeneration after lyophilization” section. The use of confocal microscopy was necessary, because it was not possible to determine the mean NP size by dynamic light scattering, due to the polymers in the solution interfering with the measurements.
Figure 2 Confocal microscopy analysis of FITC-labeled NP size.
Dynamic dialysis data were used to assess reversible drug interactions with Ch in fluid solution or the surface of the NPs in fluid dispersion. According to the established theory on determination of drug–macromolecule binding by dynamic dialysis (or permeation), the data obtained in this work were plotted according to the following equation, which was derived by applying Fick’s first law to the transfer of a solute across a membrane under quasi-steady-state conditions:17–19,29
ln [(Cd/Cd0) × 100] = 4.605 − Km·Ff·t
where Cd is the drug concentration in the donor phase, Cd0 is the drug concentration in the donor phase at time 0, Ff is the noninteracting-to-total drug ratio in the donor phase, and Km is the dialysis-rate constant. Once Ff is determined from the slope of the log-linear plot, the bound fraction can readily be calculated as 1 − Ff. The dialysis data for plain 5-FU (control), 5-FU-loaded NPs, and 5-FU in the presence of Ch in solution are plotted in Figure 3 as ln (Cd/Cd0) ×100 versus t. All plots are significantly linear, as shown by the respective r2 values, namely, 0.999, 0.996, and 0.994. Such linearity indicates that in all cases Equation 2 was obeyed and Ff was actually constant with varying Cd and time at least over the time of dialysis. For the plain drug (control), Ff =1; therefore, according to Equation 2, the slope of the relative log-linear plot was equal to the dialysis-rate constant Km. The slopes of the straight lines ± standard deviation in Figure 3 were 0.841±0.029 hours (control, Km), 0.894±0.052 hours (5-FU in Ch solution), and 0.543±0.019 hours (5-FU in loaded NP dispersion). These data indicate a nonsignificant 5-FU–Ch binding in solution and a 35.4% bound fraction in the NP dispersion. From here, it was deduced that the drug fraction reversibly adsorbed on the NP surface was significantly higher than that reversibly interacting with Ch in solution. Since the NPs were made of mucoadhesive polymers,30 their binding to both the ocular surface and drug was encouraging in terms of bioavailability.
There is still debate in the literature about the validity of dynamic dialysis as a method to obtain release data from NP systems.19 To make a further contribution to the discussion, a procedure was used in the present work based on interrupted dialysis, followed by ultracentrifugation of donor phase, as described in the “Materials and methods” section. Results from the kinetic analysis of phases are plotted in Figure 4. The drug fractions in the dispersion medium and NP matrix showed parallel decreasing patterns, suggesting a substantial thermodynamic equilibrium between these phases all along the release process. Moreover, at whatever time of the process the drug fraction in the dispersion medium was significantly higher than in the NP matrix, suggesting that the former was no perfect sink for drug release from NPs. This indicates that such a process was under the control of the dialysis membrane. Indeed, if this were not the case, and drug release from NPs was NP-controlled, the 5-FU decrease in the NP-dispersion medium would have been faster than in the NP matrix and the drug fraction in the former would soon have become lower than in the latter. The data support previous reports stating that dialysis is not always a safe method for studying drug release from nanoparticulate systems because of diffusional resistance to release, opposed by the dialysis membrane.19 Anyway, a piece of useful information still emerges from the data in Figure 4, ie, in such a medium as tear fluid, where sink conditions for the present NPs would be respected, the release of 5-FU from Ch-based NPs would be complete in less than 180 minutes.
Determination of drug interactions with polymers used to prepare TSOH
Dynamic dialysis data were used to assess reversible drug interactions with the polymers used to prepare the hydrogel formulations in the sol state. The considerations reported in the “Drug-binding studies” section also apply to the present cases, only the experiments were carried out at 4°C. The dialysis data for plain 5-FU (control) and those for the polymers used to prepare the hydrogels are reported as ln (Cd/Cd0) ×100 versus t in Figure 5A and B. The linearity of plots appears from the figure. The significance of linearity is confirmed by the respective r2 values, listed in Table 2. From the data, it appears that the partial substitution in the formulation of Ch with its derivatives generally weakened 5-FU interaction with the formulation polymers in the sol state to negligible values.
Table 2 Results of analysis of dynamic dialysis data obtained at 4°C for 5-FU plotted in Figure 5 according to Equation 2
In this case, drug–polymer interaction was studied by the phase-equilibration technique described in the previous “Gel state” section. The positive or negative concentration change in each solution in PB was plotted versus the correspondent initial concentration. As expected,20 a straight line with a negative slope was obtained in all cases, the significance of which is shown by the relevant r2 values (r2≥0.993). The abscissa intersection of each straight line gave the equilibrium concentration with the gel. This corresponded with the unbound-drug concentration in the hydrogel, from which the bound concentration could readily be calculated. From data in Table 3, it appears that the drug binding to Ch in the gel was much stronger than in the sol state and the partial substitution of Ch in the hydrogel by Ch derivatives caused a further increase in the drug–gel interaction. This increase was perhaps due to a stiffening of the polymer network that could correlate with the presence of fixed positive charges of Ch derivatives. This hypothesis is endorsed by the higher drug–gel interaction registered with the conjugate QA20-Ch50. Indeed, in this polymer, the number of QA ions was higher than the other derivatives,10 where the structure of these conjugates is shown. A shielding action of thiols reduced this effect, as shown in Table 3.
A remarkable affinity of the mucoadhesive TSOH and NPs for 5-FU has been evidenced in the foregoing discussion. In vitro release data are still lacking to guide the selection of an NP-containing TSOH to be tested in vivo as a potential controlled ophthalmic 5-FU-delivery system.
Drug release from NP-containing TSOH
Data on drug release from TSOH, obtained as described in the “Studies on 5-FU release from TSOH” section and plotted as percentage of released drug vs √t, yielded linear plots (not reported for clarity) with few zero intercepts (between −2.66% and 1.18%) and high r2 values (between 0.97 and 0.99; n=6). This pattern in all cases fitted well a well-known model assuming release is entirely governed by drug diffusion in the releasing vehicle. The slope of each straight line is a useful parameter allowing comparison of the different cases on the basis of drug diffusivity in the hydrogel. In this light, an insight into the data listed in Table 4 shows that the substitution of some fractions of Ch in the gelling mixture with a QA-Ch derivative exerted some effects on the release characteristics of the TSOH, depending on the particular derivative. A decreasing effect on the slope of the percentage-release-vs-√t plot and on cumulative release in 5 hours was significant, with the Ch + QA15-Ch50 and Ch + QA20-Ch50 hydrogels containing medicated NPs. Also, it should be pointed out that in all cases the slopes of the √t plots for the plain hydrogels were higher than those for the NP-containing ones. Considering that for a mucoadhesive vehicle, drug–vehicle binding is directly related, while drug diffusivity in a vehicle is inversely related to drug retention in the precorneal area, the data described so far encouraged us to choose the NP-containing Ch + QA20-Ch50 formulation for the in vivo tests. For this formulation, indeed, Tables 3 and 4 show the highest bound concentration and the lowest diffusivity-related parameters, respectively.
Table 4 Characteristics of 5-FU release from plain or NP-containing TSOH
In vivo tests
When instilled in rabbit eyes, the ophthalmic drops were biocompatible and caused no apparent irritation signs, such as conjunctival/corneal edema and/or hyperemia. The relevant concentration–time profiles are shown in Figure 6, while the pharmacokinetic data are listed in Table 5.
The results of the in vivo tests shown in Figure 6 demonstrate the ability of the selected TSOH + NP system to increase bioavailability with respect to the control. This system produced maximum concentration and AUC values significantly higher than that relative to the reference. Note that the AUC value for the hydrogel obtained from plain Ch was significantly lower than that relative to the hydrogel containing the Ch derivative. This was probably due to the ability of the Ch + QA20-Ch50 formulation to control the release of 5-FU. The AUC values shown in Table 5, relative to the Ch + QA20-Ch50 hydrogels containing (or not) NPs, were not significantly different. However, the NP-containing hydrogel showed a concentration plateau in the range 0.5–7 hours. This pattern points to zero-order transcorneal absorption kinetics, which can be ascribed to controlled drug release from the selected NP-containing TSOH, perhaps accompanied by prolonged TSOH residence in the precorneal area, in turn due to the mucoadhesiveness of formulation components. Also, NP internalization by the corneal cells could be an important factor determining pharmacokinetics in the aqueous humor.
TSOH was successfully prepared from solutions of Ch and its mucoadhesive derivatives. The sol–gel transition occurred in the interval 30°C–35°C. The TSOH and Ch-based NPs showed a remarkable affinity for 5-FU. Drug-binding and in vitro drug-release studies guided the selection of an NP-containing TSOH to make a potential controlled 5-FU-delivery system for ophthalmic application. Increased bioavailability of 5-FU in the aqueous with respect to the reference resulted from in vivo experiments in rabbit eyes. The NP-containing hydrogels mediated to a zero-order 5-FU absorption, leading to a time-constant anticancer concentration in the aqueous for up to 7 hours from instillation. The TSOH and NPs coupled their properties to produce an interesting sustained-release formulation for ophthalmic application.
The authors report no conflicts of interest in this work. The preliminary data of this research paper were presented at the 10th World Meeting on Pharmaceutics, Biopharmaceutics and Pharmaceutical Technology, April 4–7, 2016, in Glasgow.
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