key: cord-0804003-ugwh1ar8
authors: Mahmood, Syed; Kiong, Kong Chak; Tham, Chun Shern; Chien, Tan Choo; Hilles, Ayah Rebhi; Venugopal, Jayarama Reddy
title: PEGylated Lipid Polymeric Nanoparticle–Encapsulated Acyclovir for In Vitro Controlled Release and Ex Vivo Gut Sac Permeation
date: 2020-10-14
journal: AAPS PharmSciTech
DOI: 10.1208/s12249-020-01810-0
sha: 48e24ec41206df1c3739c30315584b5620d2c00d
doc_id: 804003
cord_uid: ugwh1ar8

Currently, pharmaceutical research is directed wide range for developing new drugs for oral administration to target disease. Acyclovir formulation is having common issues of short half-life and poor permeability, causing messy treatment which results in patient incompliance. The present study formulates a lipid polymeric hybrid nanoparticles for antiviral acyclovir (ACV) agent with Phospholipon® 90G (lecithin), chitosan, and polyethylene glycol (PEG) to improve controlled release of the drugs. The study focused on the encapsulation of the ACV in lipid polymeric particle and their sustained delivery. The formulation developed for the self-assembly of chitosan and lecithin to form a shell encapsulating acyclovir, followed by PEGylation. Optimisation was performed via Box-Behnken Design (BBD), forming nanoparticles with size of 187.7 ± 3.75 nm, 83.81 ± 1.93% drug-entrapped efficiency (EE), and + 37.7 ± 1.16 mV zeta potential. Scanning electron microscopy and transmission electron microscopy images displayed spherical nanoparticles formation. Encapsulation of ACV and complexity with other physical parameters are confirmed through analysis using Fourier transform infrared spectroscopy, differential scanning calorimetry, and X-ray diffraction. Nanoparticle produced was capable of achieving 24-h sustained release in vitro on gastric and intestinal environments. Ex vivo study proved the improvement of acyclovir’s apparent permeability from 2 × 10(−6) to 6.46 × 10(−6) cm s(−1). Acyclovir new formulation was achieved to be stable up to 60 days for controlled release of the drugs. [Figure: see text]

INTRODUCTION Viral diseases are emerging as a major cause for the mortality of the human life. Emergence of these infectious virus causes a pandemic and an epidemic from time to time, disturbing normal life. Virus strains and their classifications are vast, their transmission (e.g. zoonotic spread) makes them additional biologically vulnerable to human. The recent issues of the occurrence of endangered coronavirus for threatening the world. Some examples of cross-species virus transmission are Ebola, severe acute respiratory syndrome (SARS), chicken pox, and herpes simplex virus (HSV). The herpes simplex virus (HSV) is from the family of Herpesvirida and mainly forms two main types (HSV-1 and HSV-2). HSV-2 infected more than 400 million people at the age of 15-59 worldwide with genital herpes with sexually transmitted and also lifelong incurable disease HSV-2 (1, 2) . Currently, the therapeutic drugs available are acyclovir, valaclovir, and famciclovir, in which acyclovir is referred as the most widely used drug to control disease. Acyclovir (ACV) is acyclic guanosine analog of purine nucleoside, (guanine substituted at (2-hydroxyethoxy) methyl) at 9 position (2amino-9-(2-hydroxyethoxymethyl)-1H-purin-6-one) (2) . It is mostly involved in the treatment of HSV-1 and HSV-2, given orally daily with a dose of 400 to 800 mg (2) (3) (3). In the Biopharmaceutical Classification System (BCS) class III drugs, the large dose and frequent administration are due to acyclovir having poor aqueous solubility (1.5 mg/mL) and poor permeability (0.12~2 × 10 −6 cm s −1 ), rendering acyclovir to have low oral bioavailability (10~30%) and short half-life (3 h) with molar mass 225.21 g/mol (4) (5) (6) (7) (8) . Oral acyclovir has a narrow absorption window, which is from the stomach to duodenum (9) . The low absorption depicts the need for a delivery system that could release effectively in either or both gastric and intestinal environment to target the disease.

Several attempts have been made to enhance the delivery of oral acyclovir using polymeric mediated nanocarriers. Some of the delivery systems are interpenetrating polymeric network which is based on the close contact and molecular-scale interaction between different polymers to encapsulate the drug (10), poly (lactide-coglycolides) (PLGA) nanoparticles (2) , and chitosan ionic gelation with sodium tri-phosphate (TPP) (11) (12) (13) (14) . The use of polymers and amphiphilic molecules has constantly been involved in the delivery of hydrophilic and lipophilic molecules. Lecithin (phosphatidylcholine) is used in various nanocarrier-designed formulations like micelles, liposomes, and lipid nanoparticles (15) (16) . Lecithin is not only used due to its safe and biocompatibility properties, but also because it is the solubilising carrier for poorly water-soluble drugs (17) . Lecithin and chitosan can form spherical nanoparticle via supramolecular selforganising interaction (12) . Concept of PEGylation in oral delivery is also well studied for drug release. Mariyam et al. introduced that PEGylated dendrimer-based 5fluorourasil (5FU) gave better loading and slower release of 5FU than non-PEGylated polymer (18) . Moreover, the use of polyethylene glycol (PEG) imparts stealth properties on nanoparticles (19) , reducing the tendency to be eliminated by the reticuloendothelial system (RES), improving bioavailability and half-life of drug (20) . The hydrophilic properties of PEG could prevent interaction with other nanoparticles via sterical hindrance, improving the stability of nanoparticles (21) . PEG is also claimed to enhance mucoadhesive of nanoparticles (22) .

The present study aimed to design a PEGylated lipid polymeric nanoparticle system, utilising chitosan, lecithin, and poly (ethylene glycol) (PEG) 2000 that was hypothesised to produce nanoparticles with high encapsulation and good permeability, accompanied by a sustained release profile. PEGylated acyclovir-loaded lecithin-chitosan nanoparticles (PALNs) were formulated and optimised, and the physicochemical properties of PALN were characterised for stability of the nanoparticles. Simulated gastric fluid (SGF) and simulated intestinal fluid (SIF) were used to study the in vitro drug release of PALN. In contrast, rabbit intestine was used to evaluate the ex vivo permeation performance for the controlled release of the drugs for 60 days.

Acyclovir (ACV) was acquired from Pharmaniaga Research Centre Sdn. Bhd. (Malaysia). Phospholipon® 90G (lecithin) was bought from Lipoid GmbJ, Mattermannallee, Switzerland. Chitosan, propylene glycol (PG), and polyethylene glycol (PEG-2000, MW: 1900-2200) were purchased from Merck Sdn. Bhd (USA). Dialysis bag-110 (molecular weight cut-off (MWCO): 12,000-14,000 Da) was purchased from HiMedia Laboratories Pvt. Ltd. (India). Rabbit intestinal sac was obtained as a gift from SARSHA Riding Centre. HPLCgrade Acetonitrile was procured from Fisher Scientific Inc. (Malaysia). Water is purified using a MilliQ® Integral Water Purification System with a conductivity of 15 MΩ. Other chemicals were of analytical reagent grade.

A 3-factor, 3-level, 17-run Box-Behnken Design (BBD) was adopted to generate polynomial models for the optimisation process of the drug. Three determining factors were the amount of lecithin (X 1 ), chitosan (X 2 ), and PEG 2000 (X 3 ) as shown in Table I . Dependent variables to be optimised were entrapment efficiency (EE%) (Y 1 ), zeta potential (mV) (Y 2 ), and particle size (nm) (Y 3 ). Design-Expert® Software Version12 was employed to establish main effects, interaction effects, and quadratic effects from independent variables, and provide the solution for optimised formulation. The nanoparticle formulations involved, including five centre points, are tabulated in Table II . All experimental results measurement was analysed in triplicate and expressed as mean ± standard deviation and p < 0.05 was considered as significant for the data.

ALN was prepared by the method reported by Sedef and group with little modification (15) . An appropriate amount of lecithin and chitosan was weighed, as shown in Table II . Chitosan was dissolved in 15 mL of 0.1% v/v acetic acid followed by heating to 60°C. Lecithin prepared was dissolved in an organic solvent consisting of 2.5 mL methanol, 2.5 mL chloroform, and 2 mL PG. An amount 15 mg of ACV was 

PEGylation was performed by modifying an established method by Arya et al. (23) . Prepared PEG 2000 solutions were 200 mg/mL, 300 mg/mL, and 400 mg/mL. One millilitre of the solution was added into nano-suspension formed under Section C. The suspension was agitated at moderate intensity for 30 min, followed by probe sonication with 30% amplitude, pulse on/off the rate of 10 s/5 s, for 2 cycles. The formulated particles were centrifuged and supernatants containing any trace of free ACV were separated for the purification of drug. Final product PEGylated ACV-loaded lecithin/chitosan Nanoparticles (PALNs) were stored for further analysis to study the controlled release of drugs.

Amount of encapsulated ACV in nanoparticles was identified indirectly in high-performance liquid chromatography (HPLC) (24) . Agilent 1260 Series HPLC system fitted with a photodiode array detector (DAD), and use Thermo Fisher Syncronis C-18 (5-μm particle size, 150 × 4.60 mm diameter) column. A fixed injection volume of 20 μl per sample, a column temperature of 25°C, and a wavelength of 254 nm were set. The mobile phase used was acetonitrile and pH 6.74 water (10:90, v/v), which was set at an isocratic flow rate of 0.5 ml/min for 10-min run time. Equation (1) showed a calibration curve that fit over the range 100-500 μg/ml with a correlation coefficient of r 2 = 0.99990.

where y represented the peak area in a milli-absorbance unit (mAu) and x represented the ACV concentration (mg/ml). In evaluating the entrapment efficiency (EE), PALNs prepared were stored in − 80°C freezer for 24 h. Then PALNs were thawed and isolated by centrifugation at 48,000×g at 4°C for 20 min. The supernatants consisted of the free drug were:

where EE was the entrapment efficiency, and M total and M free were a total mass of ACV added and free ACV in supernatant respectively.

Particle size, Poly-Dispersity Index (PDI), and zeta potential were determined by DelsaMax PRO Zeta Potential Dynamic Light Scattering Analyzer (Beckman Coulter, USA). To measure the size and zeta potential, 0.1 ml of prepared particles was diluted with 2.0 ml of deionised water loaded in flow cell and scanned for particles. The measurement was done in a 173°scattering angle. The experiment was done with a setting of 25 ± 0.5°C.

Morphology study of the nanoparticles was carried out using scanning electron microscopy (SEM) (4). The formulation was lyophilised and further dried using vacuum oven for 30 min and the powder was uniformly spread on the coverslip and further coated with platinum using 208HR High-Resolution Sputter Coater (Ted Pella, INC, CA, USA). Coated sample was then inserted into the specimen chamber and scanned using TM 3030 Plus scanning electron microscope (Hitachi, Tokyo, Japan), at 5 kV.

The optimised formulation was visualised by highresolution transmission electron microscopy (HRTEM). The formulation was diluted with water in ratio of (1:50) and placed on the copper film-coated grid, with a diameter of 3.05 mm and 400 mesh size (Ted Pella, CA, PELCO® 400 Mesh Grids). After placing the particle, they were air dried for 15 min and any access of water was removed using a filter paper. The analysis was done by using a Tecnai G2 20 Twin transmission electron microscope (FEI Company, Oregon, USA).

Thermal properties of optimised formulation were analysed using differential scanning calorimetry (DSC) 214 Polyma differential scanning calorimeter (NETZSCG- 

Gerätebau GmbH, German). Samples used included lecithin, chitosan, PEG 2000, optimised formulation, pure acyclovir, and a blend of acyclovir, chitosan, lecithin and PEG 2000 (physical mixture, PM). The optimised formulation was dried in SHEL LAB SVAC2-2 vacuum oven (Sheldon Manufacturing Inc., USA) under 35°C and 25 in. Mercury (Hg) before analysis (16) . Black alumina was used as a reference. Nitrogen gas purge rate was 20 mL/min. The analysis was conducted with settings shown in Table III . All the scanned samples were analysed in triplicate to plot the data.

The crystallinity of PALNs synthesised was studied through the sharpness of peak in the XRD spectra by X'Pert 3 Powder X-Ray Diffractometer with X'Celerator (Malvern Panalytical, UK). Samples used were lyophilised PALNs, pure ACV, and PM. Samples were radiated with CuK α radiation at 45 kV and 140 mA. 2θ scan range from 0°to 60°, with 3°/min scanning rate, and 0.05°step size were set (17) . All the tests were performed in triplicates.

Compatibility study was conducted using Nicolet iS50 FT-IR Spectrometer (Thermo Fisher Scientific Inc., Waltham, MA). Samples used included pure acyclovir, lecithin, chitosan, PEG 2000, optimised formulation, and PM. Before analysis, optimised formulation was vacuum-dried at 35°C and − 25 in Hg (17) . The analysis was done with sixteen scans at scanning range of 600 to 4000 cm −1 .

A replicate of optimised PALN was prepared without lyophilisation and assessed for short-term physical stability for 60 days based on ICH guidelines. The sample was stored in 4°C chiller throughout the study period. Nanoparticle size of the sample was measured by using the method as described in section F at an interval of 0th, 15th, 30th, 45th, and 60th days. A p < 0.05 was considered as significant for the obtained data.

In vitro drug release profile was conducted on the optimised formulation by employing a dialysis bag method with USP apparatus II. Two sets of dialysis bag (MWCO: 14,000 Da) of suitable length to accommodate the sample were prepared and immersed in 37°C ultrapure water for 30 min for stabilisation. One end of the dialysis bags was tied securely with thread. Then 4 mL of optimised formulation with ACV concentration of 1 mg/mL was injected into each dialysis bag. Another end of the dialysis bags was then tied securely with a thread. The dialysis bags were kept in sink condition in two separated vessels of a RC-8DS dissolution tester (Sinopham Co., Ltd., China) filled with 400 mL of pH 1.2 hydrochloric acid buffer (SGF) and 400 mL of pH 6.4 phosphate buffer saline (SIF) respectively. Dissolution tester was set for 70-rpm rotation and 37°C water bath. One millilitre of sample was taken in triplicate at 0.5 h, 1 h, 2 h, 4 h, 8 h, 12 h, and 24 h. The same volume of fresh medium was re-filled into the corresponding vessel. Samples were analysed with HPLC method as described in section E. Another calibration curve with a smaller range from (1) was generated to ensure the accuracy of ACV concentration derived from peak area. Equation (3) showed a calibration curve that fit over the range of 5 to 50 μg/mL with r 2 of 0.99964.

The drug release profile of optimised formulation was plotted with a cumulative percentage of ACV released against time. Drug release data was fitted into one of the releasing models which were zero order, first order, Higuchi, Korsmeyer-Peppas, and Hixson-Crowell releasing model. A best model kinetic fit describing drug release of the formulation was selected according to the coefficient of determination (r 2 ) that calculated with aid from Microsoft Excel. Equation (4) was used as a formula for the cumulative percentage of drug-released calculation.

where DR was the cumulative percentage of drug released, and M released and M total were mass of acyclovir released and total mass of acyclovir in formulations used respectively.

Ex vivo study was performed according to an established method (25) with modification. The study was done using New Zealand white rabbit of age 5-6 months. The rabbit intestine sac was cleaned with cold saline. It was cut into several 9.5-cm-long segments. The intestine segment was tied up securely with thread at one end, followed by the introduction of 2 mL of optimised formulation with 1 mg/ mL of ACV concentration into the intestinal opening. The other end was then tied up securely with thread. The rabbit intestine sac containing the formulation was kept in sink condition in a beaker containing 80 mL of pH 7.4 PBS with 1% m/v sodium lauryl sulphate (SLS) at 37°C as releasing 

where DP was the cumulative percentage of drug permeated and M medium was the mass of acyclovir in releasing medium. Apparent permeability of the formulation as a function of the mucosal surface area was calculated by Eq. (6). In contrast, Eqs. (7) and (8) were used to calculate apparent permeability coefficient and steady-state flux, and J ss of acyclovir in formulation, respectively.

where P app was the apparent permeability coefficient, dQ/dt was the slope for the graph of the cumulative amount of ACV permeated against time in unit of mg/h, A is the surface area of intestinal tissue where the permeation of nanoparticles occurred in the unit of cm 2 , and C 0 gave an initial concentration of ACV in the intestinal sac that was 1 mg/mL (equivalent to 1 mg/cm 3 ).

PEGylated lipid polymeric nanoparticle (PALN) formation hypothesis is shown Fig. 1. The method follows the selforganising interaction between the combination of lecithin, chitosan, and PEG 2000 (15) . ACV, being polar in nature, attracts the hydrophilic head of lecithin (26) , while randomly dispersing in the solvent for fabricating nanoparticles. The lecithin/ACV solution was added into chitosan solution, the electrostatic interaction between chitosan, and lecithin led to the formation of chitosan hydrophilic shell layer surrounding the internal core of lecithin and ACV. The combination of chitosan and lecithin permitted the formulation of stiff and stable nanostructure (27) . Hydrogen bonding and physical entanglement might also occur between lecithin and chitosan (28) .

PEG can provide stealth property on nanoparticles to avoid RES elimination and prolong their circulation time (29) . Protonation on chitosan-free amino group in the acidic environment caused it to be positively charged. The dipoledipole or hydrogen bonding between chitosan shell and PEG became stronger than intra-molecular or intermolecular hydrogen bonding of chitosan chain and allowed PEG grafting onto it due to interaction between amine or amide nitrogen of chitosan, and hydroxyl and etheric oxygen of PEG (30) . Probe sonication was employed to reduce particle size as well as improving uniformity of size. PALNs formulated exhibited a pale white appearance with soapy texture. Pale white colour resulted from the massive amount of nanoparticles formed, while the frothy white texture was due to the presence of PEG 2000 in the formulation.

The Box-Behnken design with 3 × 3 factorial design generated 17 trail with 5 centre points runs for the preparation of PEGylated lipid polymeric nanoparticles (PALNs) as shown in Table II . The optimisation data shows that the concentration of independent factors lecithin (A), chitosan (B), and PEG 2000 (C) exerts an individual negative and positive effect on the dependent factors i.e. entrapment efficiency (Y1), particle size (Y2), and zeta potential (Y3). The best fitted equation was selected as quadratic for all the 3 dependent factors. The effect was shown through 3D response surface depicting the interaction between independent variables and dependent factors as shown in Fig. 2 . Before the BBD development, some preliminary studies were conducted using the ratio of the lecithin and chitosan was selected. The aim was to get the maximum entrapment efficiency and minimum range for particle size. The probe sonication was selected at 4 min, as in our preliminary studies, it was concluded that high sonication with leaded to breakage in the particle and 1--2-min sonication produced particles with large diameters.

The EE is shown in Table IV and Fig. 2 a represented the graphical presentation of EE for all formulations. The results obtained for the drug EE ranged from 68 to 87%. The use of sonication for solubilisation of ACV in organic solvent allowed it to be correctly attached to lecithin and get encapsulated into nanoparticles formed.

Design-Expert software generated Eq. (9) that expressed the effect from independent factors, which were the amount of lecithin (X 1 ), amount of chitosan (X 2 ), and amount of PEG 2000 (X 3 ) on drug entrapment efficiency of the formulation.

A positive value for coefficient indicates the increment in the factor results in an appropriate improvement in the response and vice versa. The equation with adjusted R 2 of 0.9398 indicates a good fit. Interaction between the factors affecting drug entrapment efficiency was as shown in Fig. 3 ac; it is to be noted that the X1 and X2 in the figures indicate the X-axis instead of the independent factors. Figure 3 a showed the increment of drug entrapment efficiency by increasing lecithin amount and decreasing chitosan. It is also observed that drug entrapment efficiency reduced at level 1 of lecithin, as micelle formed when lecithin concentration exceeds critical micelle concentration which could affect the encapsulation process. Lowering the amount of lecithin also led to poor encapsulation efficiency as less available hydrophilic heads to be attracted by ACV (26) . Increment in chitosan concentration amount improved selfassembling process between chitosan and lecithin, which also resulted in weakly attraction between ACV and lecithin and ACV will not be entrapped. It is noticed that the interaction effects between lecithin and chitosan have the most substantial impact on entrapment efficiency. Figure 3 b and c showed the interaction between PEG 2000 as well as between chitosan and lecithin on entrapment efficiency was weaker when compared with lecithin and chitosan. EE decreases slightly with an increment of PEG 2000 amount, which might be due to the interaction between the PEG 2000 and chitosan, as it affects the electrostatic interaction between lecithin and chitosan, causing the tight junction to be disrupted upon mixing, resulting in drug leaking. The disruption was attributed to the ability of PEG 2000 to enter the loosely packed structure (31) . A suitable amount of lecithin (X 1 ) should be used in pair with sufficient but not excessive amount of chitosan (X 2 ), and less PEG 2000 (X 3 ) for high EE.

Zeta potential for all formulations was determined and tabulated in Table IV as observed values. Figure 2 b showed the graphical presentation of zeta potential measurement for 17 formulations. The zeta potential ranged from + 20.77 ± 5.59 to + 50.47 47 ± 1.65 mV. The zeta potential was mainly determined by lecithin and chitosan used. However, PEG 2000 as a polymer grafting on the lecithin-chitosan core-shell structure might be impacting the stability of the nanoparticle. The values can be used as an indicator that all the prepared hybrid nanoparticle formulations were highly stable. Using Design-Expert software, the relationship between the used amount of lecithin, chitosan, and PEG 2000 on zeta potential can be explained using Eq. (10) with a high R 2 value of 0.9294. Figure 3 d showed positive linear relationship between zeta potential and amount of chitosan used for developing the nanoparticles. The relationship was predictable since chitosan dissolves in an aqueous solvent, exhibiting net positive charges due to the protonated amine group (30) . When the amount of lecithin used decreases, the zeta potential increases, proving that negatively charged lecithin had reacted with positively charged chitosan, producing a negative effect on zeta potential. The same trend can be seen in Fig. 3 e, where PEG 2000 with a surface charge of − 2 to − 7 mV also had a negative effect on zeta potential, but to a lower extent to that of lecithin (32) . It can be seen that chitosan was capable of producing formulation with zeta potential greater than 50 mV. Still, the use of PEG 2000 and lecithin, or to be exact, the electrostatic interaction between chitosan and other components, causes the reduction of zeta potential. Figure 3 f further supported the point that lecithin and PEG 2000 were responsible for zeta potential decrement. When a higher proportion of PEG2000 (40 mg) and lecithin (300 mg) was used, the zeta potential significantly decreases in the nanoparticles.

Particle size and PDI obtained from all 17 formulations were recorded in Table IV as observed values and illustrated in Fig. 2 c. The particle size ranged from 155.31 ± 6.87 to 264.82 ± 4.33 nm, with PDI ranged from 0.179 ± 0.03 to 0.429 ± 0.12. In overall, the results were accepted as it is capable of Fig. 1 . Schematic diagram for PALNs formation. a Hydrophilic head attracts towards the polar head. b Lecithin-chitosan leads to electrostatic interaction and formation assembly. c Self-organisation between the lecithin, chitosan, and PEG 2000 exhibiting enhanced permeability and retention (EPR) effect. Equation (11) describes the effect of three independent factors on particle size, with high r 2 value of 0.9162 to prove that the equation is reliable. 

We observed that particle size was significantly impacted by amount of lecithin, chitosan, and PEG 2000 used, as shown in Fig. 3 g-i.

The particle size of PALN increased with the amount of lecithin and chitosan used in the nanoparticles. As more lecithin and chitosan were used, more drugs attracted and entrapped in the core, forming bulkier nanoparticle. The nanoparticles formed showed a size smaller than 200 nm, as a proven larger proportion of smaller nanoparticle size area in Fig. 4 . To decrease the amount of chitosan injudiciously was not preferred as it might be insufficient to form a complete spherical structure with lecithin, which was bulkier with attached drug. Thus, lecithin to chitosan ratio must be adjust to ensure complete self-assembling process as it leads to rigid spherical nanoparticle occupying less space. On the other Fig. 2 . Graphical presentation of a drug entrapment efficiency, b zeta potential, and c particle size and PDI PALNs formulation hand, increment in PEG 2000 thickens the layer on PALN, resulting in size increment (32) . It is also observed that without sufficient PEG 2000, the drug residence time in systemic blood circulation might not be able to be significantly prolonged for nanoparticles.

Table V summarised quadratic equation used in describing the effect of three independent variables on three dependent variables. All factor with (p value< 0.05) were considered as significant. The expected values for Y 1 , Y 2 , and Y 3 was shown in Table IV . Due to negligible difference between observed and predicted value, a quadratic Eqs. (9), (10), and (11) can serve as a good indicator of behaviour and interaction relationship between the independent factors.

The measurements considering for all obtained and software's recommendation, formulation PALN1 with high EE of 83.81 ± 1.93%, the particle size of 187.7 ± 3.75 nm, and PDI of 0.238 ± 0.01. The values of PALN1 were selected due to its higher EE and optimum size. The zeta potential of + 37.70 ± 1.16 mV of PALN1 was found to be very stable. The ratio of lecithin to chitosan for the optimised formulation is exactly 20:1, which was known to be the perfect proportion of both materials to get a small-sized nanoparticle with spherical shape (33) .

The SEM images revealed a round and spherical shape morphology with a smooth surface of the nanoparticles (Fig.  4a, b) (34) . Figure 4 c shows the range of particle size from 172 to 198 nm. The HRTEM measurement was in the agreement with dynamic light scattering (DLS) measurement of PALN1 particle size of 187.7 ± 3.75 nm. Also, the figure shows a twolayer structure of nanoparticles, which corresponds to the formation of chitosan shell layer around the lecithin core (35) . Figure 5 a lecithin showed a low-intensity endothermic peak at 47.2°C, which was the chain melting transition point where it transformed into a liquid crystalline form from a gel form with enhanced ability to act as a drug carrier (36) . Two endotherms were observed for chitosan, where 83.8°C was attributed to water loss and polymeric chain decomposition at 303.7°C (37) . PEG 2000 endothermic peaks at 53.5°C, indicating melting process of the sample (36) . ACV had four thermal effects shown in Fig. 5 a. The analysis for ACV used was ACV polymorph form VI, with 1:2 ratio of ACV to water. The first endothermic peak at 116.5°C was assigned to the dehydration process. It leads to recrystallisation of ACV form VI to ACV form V, which undergoes a phase transition to IV at 174.6°C. Further heating leads to endotherm at 255.7°C, indicating ACV melting point (MP). Last exothermic peak at 259.1°C was assigned to the exothermic decomposition of the ACV (38) .

The physical mixture for the first endotherm was assigned to the lecithin and PEG2000. ACV endothermic peak diminished but a new peak emerged at 151°C. It might be due to molecular interaction between drug, lecithin and chitosan. The interaction causes ACV to have decreased crystallinity and increased amorphous properties of acyclovir, or turned into semi-solid form, or dissolution in the matrix melt (39) . For PALN1, peak diminishments of lecithin, Table 4 . Observed and predicted value of encapsulation efficiency (Y 1 ), particle size (Y 2 ) and zeta potential (Y 3 Table III showed that heating rate for acyclovir and PM was higher than PALN1. Higher heating rate results in MP shifted to a higher temperature which is in agreement from the previous report of acyclovir MP (40). (12) with the aids of OriginPro Graphing & Analysis 2020 software. The ACV crystalline and total peak area were found to be 53,181.75 and 56,443.52 unit area, respectively, with crystallinity index calculated to be 0.9422, which was very crystalline

where Area Crystalline and Area Total were integrated areas for crystalline structure and total integrated area, respectively. ACV peak was diminished from PM diffractogram. This suggested possibility of ACV turned into the disordered crystalline state due to the molecular interaction with lecithin and chitosan. By comparing ACV and PALN1 diffractogram, a broad peak emerged with sharp peak diminishment indicating ACV entrapped in LPNPs system in the amorphous state of the nanoparticles (41). (42, 43, 45) . A peak at 894 cm −1 is attributed to the pyranoid ring of chitosan (46) .

Lecithin' IR spectrum displays characteristic N-H group stretching at peak 3379 cm −1 (47) . Symmetry stretching of C-H for the cis-double bond is depicted at 3009 cm −1 . Saturated aliphatic ester carbonyl stretching (-C=O) is represented at peak 1735 cm −1 (48) . A strong, sharp peak at 1087 cm −1 shows a symmetric stretching of phosphate groups (42) . The asymmetric stretchings of P=O which overlapped with P-O where both co-exist in phosphodiester group, together with P-O-C stretching, were at peaks 1238 cm −1 and 1062 cm −1 respectively. The peak at 968 cm −1 is attributed to N + -(CH 3 ) 3 asymmetric stretching overlapped with O-P-O deformation (49) . Out of plane bending of HC-CN is depicted at 818 cm −1 (50) .

Acyclovir IR spectrum shows intermolecular and intramolecular hydrogen-bonded hydroxyl group (O-H) stretchings at 3515 cm −1 and 3470 cm −1 (51), while NH 2 symmetrical stretching is at 3438 cm −1 (52) . Secondary amine stretching is at 3290 cm −1 (42) . A peak at 3177 cm −1 is attributed to N-H stretching overlapped with O-H stretching (47) . C-H and H-C-H stretchings are represented at 2927 cm −1 and 2854 cm −1 (42) . The presence of C=O at 1708 cm −1 , presence of C 8 -H together with ring vibration of (42) . The IR spectra of PM represent the combination of all characteristic peaks, such as 2884 cm −1 and 2860 cm −1 (PEG 2000); 3354 cm −1 and 3291 cm −1 (chitosan); 3379 cm −1 and 3009 cm −1 (lecithin); and 3470 cm −1 , 3438 cm −1 , and 3177 cm −1 (ACV). The peaks showed very slight shifting (± 5 cm −1 ), indicating no bonding interaction between drug and other formulation ingredients. PALN1 was observed that none of the ACV characteristic peaks emerged, indicating encapsulation of the drug.

Table VI displays the particle size of PALN1 at different sampling time. The t tests were conducted with a p value higher than 0.05 for all tests suggested that there was an insignificant variation in PALN1 particle size on each sampling time as compared with 0th day's measurement. The obtained results were in agreement with a PALN1 zeta potential of 37.70 ± 1.16 mV which render the suspension stable by avoiding particle aggregation due to strong surface charge that repels each other. In brief, optimised formulations exhibit good physical stability for up to 60 days. There was no significant difference was observed p < 0.05.

In Vitro Drug Release Figure 7 a and b showed ACV release profile in pH 1.2 (SGF) and pH 6.4 (SIF) respectively. Various kinetic models were employed for a comprehensive understanding of drug release mechanisms from the optimised formulation. Table VII shows the values of correlation coefficient (r 2 ) and releasing model constant (k). Higuchi model showed the best fit with the highest r 2 value and can be concluded that the PALN formulation showed modified release. This model corresponds to the sustained release properties of lecithinchitosan nanoparticle. The drug release mechanism was identified based on the diffusion constant, n, from Korsmeyer-Peppas equation, as shown in Eq. (11) . The mathematical adjustment of Eqs. (13) and (14) was obtained: Table VIII shows that at the 10th hour, only 58% of the drug was permeated to the releasing media. The drug permeation profile had been prolonged due to the smaller porosity and thicker intestinal membrane compared with the dialysis membrane. The surface area of the intestine accommodating formulation was 5 cm 2 . P app cm s −1 À Á ¼ 1:1626mg 10  60  60s  1 5cm 2  1mg=cm 3 ¼ 6:4589  10 −6 cm s −1 ð15Þ J ss mg cm −2 s −1 À Á ¼ 6:4589  10 −6 cm s −1  1mg=cm 3 ¼ 6:4589  10 −6 mg cm −2 s −1 ð16Þ P app of 6.4589 × 10 −6 cm/s was a 3.2-fold improvement as compared with reported value of 0.12 × 10 −6 to 2.0 × 10 −6 cm s −1 (8) . The optimised PALN formulation had the potential to be used in tablet formulation with improved drug intestinal permeability.

PEGylated lecithin-chitosan nanoparticle-encapsulated acyclovir were successfully formulated with particle size less than 200 nm, optimum PDI, entrapment efficiency greater than 80%, and with positive zeta potential value greater than + 30 mV. SEM and HRTEM images showed the spherical structure of the nanoparticle. FTIR analysis with the diminishment of all ACV characteristic peaks in formulation 6 . Stacked spectra of ATR-FTIR from 4000 to 600 cm −1 for PALNs, physical mixture, acyclovir, lecithin, chitosan, and PEG 2000 spectrum indicates its encapsulation. DSC thermogram depicted a left shift, evidencing acyclovir's state changes from crystalline to amorphous property. The obtained results is further proved by the presence of a broad peak of PALN1 and diminishment of ACV crystalline peak in XRD diffractogram. In vitro release profile of ACV in nanoparticles had shown 24-h sustained release following Higuchi model with non-Fickian mechanism in both SGF and SIF. Ex vivo permeation study displayed a 3.2-fold improvement for acyclovir's apparent permeability. The formulation was stable up to 60 days from the aspect of particle size. The results demonstrated the ability of PEGylated lecithin-chitosan nanoparticles not only in providing high encapsulation of ACV and 24-h sustained release profile in both SGF and SIF, but also in enhancing the permeability of ACV. These findings suggested that PEGylated lecithin-chitosan The italicized is done to show the Nanoparticle release model is folloing Higuchi release model. It is done just to make it more visible nanoparticles may be used for drugs with poor aqueous solubility and permeability. Further, study on in vivo performance should be conducted to assess the improvement in oral bioavailability of ACV, as well as the applicability of this formulation on other BCS class III drugs.

The work was financially supported by the UMP internal grant (RDU 180371 and 180336).Abbreviations 

World Health Organization. Herpes simplex virus

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