Novel lecithin-integrated liquid crystalline nanogels for enhanced cutaneous targeting of terconazole: development, in vitro and in vivo studies

Abstract

Terconazole (Tr) is the first marketed, most active triazole for vaginal candidiasis. Owing to poor skin permeation and challenging physicochemical properties, Tr was not employed for the treatment of cutaneous candidiasis. This is the first study to investigate the relevance of novel lecithin-integrated liquid crystalline nano-organogels (LCGs) to improve physicochemical characteristics of Tr in order to enable its dermal application in skin candidiasis. Ternary phase diagram was constructed using lecithin/capryol 90/water to identify the region of liquid crystalline organogel. The selected organogel possessed promising physicochemical characteristics based on particle size, rheological behavior, pH, loading efficiency, and in vitro antifungal activity. Microstructure of the selected organogel was confirmed by polarized light microscopy and transmission electron microscopy. Ex vivo and in vivo skin permeation studies revealed a significant 4.7- and 2.7-fold increase in the permeability of Tr-loaded LCG when compared to conventional hydrogel. Moreover, acute irritation study indicated safety and compatibility of liquid crystalline organogel to the skin. The in vivo antifungal activity confirmed the superiority of LCG over the conventional hydrogel for the eradication of Candida infection. Overall, lecithin-based liquid crystalline organogel confirmed its potential as an interesting dermal nanocarrier for skin targeting purpose.

Introduction

Since the early 1980s, the susceptibility and sensitivity to fungal infection have increased significantly in terms of frequency and also as a cause of morbidity and mortality.^1–3 Among different fungal infections, the occurrence of superficial mycotic infections has risen in the last decades, now affecting >20%–25% of the world’s population. In addition, cutaneous candidiasis caused by Candida species became the most prevalent superficial mycosis affecting most of human beings,⁴ particularly immuno-compromised ones.^5,6

Treatment of Candidal infections is still challenging and is restricted to a small number of antifungal drugs, mainly azole derivatives.^6–8 However, their application is usually limited due to increase in the incidence of azole resistance⁹ and other toxicity issues.^7,10 Moreover, many newer antifungal agents have limitations in terms of their spectrum of activity, pharmacokinetics, and drug–drug interactions besides their uncommon toxicities related to their long-term use.¹¹ Therefore, looking for preexisting antifungals that have not been investigated yet for cutaneous candidiasis may arise as a possible surrogate to overcome the drawbacks of azoles and other new antifungal agents. Thus, the first scope of our study was to investigate an old synthetic triazole vaginal antifungal known as terconazole (Tr) for the eradication of cutaneous candidiasis.

Tr was the first marketed triazole antifungal with a molecular weight of 532.47 Da.^12,13 It is approved by the Food and Drug Administration for the treatment of vulvovaginitis (moniliasis).¹⁴ It is a broad-spectrum antifungal agent against different fungi such as yeasts and dermatophytes. In addition, Tr was found to be one of the most active azoles against Candida species, using the relative inhibition factor methodology.¹⁵ It outperforms imidazoles in terms of activity and curing rates for the treatment of vulvovaginal candidiasis.¹⁶ It is still used as an effective first-line treatment against moniliasis particularly in cases resistant to other drugs.^17,18 Nevertheless, its potential in the treatment of skin mycosis has not been so far investigated, which will be first considered in this work.

Topical treatment of superficial fungal infections has various advantages over oral route such as targeting the site of infection, reduction of systemic side effects, enhancing the efficacy of treatment, and high patient compliance.¹⁹ The current available antifungal drugs are commercially available in conventional dosage forms including creams, ointments, gels, and lotions. The major drawback of these formulations is that most of them suffer from restricted drug delivery across the skin, resulting in therapeutic failure.²⁰ On the other hand, several excipients are often used in other formulations for enhancing drug permeation through stratum corneum (SC) such as Azone^21,22 and dimethyl sulfoxide.²³ These excipients cause disruption to the SC layers resulting in the penetration of antifungal drug into the deeper skin layers and, unfortunately, into blood circulation causing systemic side effects.²⁴ Therefore, in order to overcome obstacles faced by conventional topical formulations, new formulation approaches have been investigated.

In fact, as our research team believes in the significance of nanotechnology to achieve the unreachable goals, therefore, the team has developed different nanocarriers to enhance the efficacy of many bioactives.^25–27 Among them, lipid-based nanocarriers were one of our interests and have been utilized in different applications.^28,29 In recent years, attentions have been given toward lipid-based delivery systems as they seem to be well-preferred topical drug delivery systems.³⁰ They are considered attractive nanocarriers over polymeric nanocarriers because of the unique properties of lipids such as their physiochemical diversity, biocompatibility, and safety.^31,32 Among different types of lipid delivery systems, phospholipid (PL)- and lecithin-based organogels were found to be intriguing. In addition to being natural and nonallergic molecules, PLs are also recognized as permeation enhancers because of their similarity to bio-membrane composition. Among different types of lecithin organogels, lecithin-based liquid crystalline nano-organogels (LCGs) are considered promising topical nanocarriers because of their thermodynamical stability, considerable solubilizing capability for both oil and water soluble compounds, and very low skin irritation potential.^33,34 They have the potential to control the drug release, low toxicity, and versatility in applications across a range of administration regimes.

Therefore, the present study is the first to investigate the dermal potential of the known vaginal antifungal Tr via elaboration of novel Tr-loaded lecithin-based liquid crystalline organogel. Full in vitro appraisal of the nanogels would be carried out and supported by in vivo antifungal investigations and ex vivo and in vivo permeation studies.

Materials and methods

Materials

Tr was kindly provided by Medizen Pharmaceutical Industries Co. (Alexandria, Egypt). Capryol 90^® (propylene glycol [PG] monocaprylate, hydrophilic lipophilic balance [HLB] =6) was a gift from Gattefosse Co. (Lyon, France). Phospholipon 90 G (soybean lecithin of ~90% phosphatidylcholine) was obtained from Lipoid GmbH (Ludwigshafen, Germany). Hydroxypropyl methylcellulose K4m was obtained from Al Amriya Pharmaceutical Industries Co. (Alexandria, Egypt). Sabouraud dextrose agar was obtained from Oxoid Limited (Basingstoke, Hampshire, UK). All other chemicals and reagents used were of analytical grade.

Construction of ternary phase diagram

In order to determine the concentration range of the system components (water/capryol/lecithin) that form lyotropic LCG, a ternary phase diagram was constructed using a water titration technique. For the titration process, a homogeneous mixture of capryol (CAP) and lecithin (G90) at varied weight ratios was slowly titrated using increasing amount of distilled water and was stirred at room temperature for a sufficient time in order to obtain equilibrium.³⁵ The mixtures were then checked visually, and slight hazy samples of high viscosity were additionally checked through the polarizing light microscope³⁶ (Model CX 31; Olympus, Hamburg, Germany). Appearance of turbidity was taken as end point. Because only region of liquid crystals was of our interest, no intention existed for the identification of other regions of the ternary phase diagram in detail.

Preparation of Tr-loaded LCG (Tr-LCG)

Based on ternary phase diagram, a mass ratio of 1:1.2 lecithin to CAP was selected for the preparation of the organogel. LCG was prepared by first dissolving Tr (1% w/w) in CAP oil. This solution was heated up to 40°C and then the preweighed lecithin was added to the solution and sonicated at 50°C–55°C until there is a complete dissolution of lecithin to obtain a homogeneous mixture of lecithin in Tr–oil solution. To this mixture, distilled water was titrated through a micropipette upon stirring with a magnetic stirrer (IKA Labortechnik, Germany) until the viscosity of the system was increased. The samples were then allowed to cool down and set aside to obtain homogenous gels at room temperature.

Preparation of Tr-loaded conventional gel

Tr-loaded conventional hydroxy propyl methyl cellulose (HPMC)-based hydrogel was prepared as a control gel for comparison with lecithin organogel. A batch of 25 g gel was prepared by first dispersing 250 mg of Tr (1% w/w) in 24 mL of distilled water under magnetic stirring at 50°C, and then 1 g of HPMC was added portion wise. The mixture was then allowed to cool down and set aside to obtain gel at room temperature.

Physicochemical characterization of liquid crystalline organogel

Organoleptic characteristics

The physical evaluation of pharmaceutical formulation is a critical step as it is directly related to patient acceptance. The prepared organogel was tested for color, odor, texture, phase separation, and the feel upon application (grittiness and greasiness). These features were also checked during stability studies.³⁴

Determination of pH

The pH of all prepared formulations was determined by pH papers at room temperature.

Viscosity measurement

The viscosity of selected Tr-loaded lecithin organogel and its placebo gel was evaluated using a cone and plate Brookfield viscometer (Model DV2T; Brookfield Engineering Laboratories, INC., USA) with a spindle 40. The sample was placed between the gap of the cone and plate, and the gap was closed gradually.³⁷ Then the sample was subjected to a dynamic shear rate ranging from 7.5 to 45 S⁻¹ (1–6 rpm) where shear stress and viscosity were measured. All the measurements were performed at isothermal condition at room temperature (25°C±2°C).

Content uniformity

For the determination of drug content homogeneity, 50 mg of the organogel formulation was diluted with appropriate amount of methanol, and the mixture was shaken to get a clear solution. The concentration of Tr was determined by a validated UV spectrophotometer at λ=243 nm. The placebo formulation was taken as blank after appropriate dilution with methanol. The drug content was calculated from the calibration curve and expressed as:³⁸

$$\text{Drug content}\%=\frac{\text{Actual drug content}}{\text{Theoritical drug content}}\times 100$$

Polarized light microscopy (PLM)

A drop of the slight hazy samples prepared during phase diagram study was put on a slide under a cover slip and was observed through the polarizing microscope.³⁹ The structure of the medicated and placebo LCG samples was examined by a polarizing microscope (Model CX 31; Olympus) using a magnification of 100×.³⁵

In vitro antifungal activity

The antifungal activity of Tr from LCG against Candida albicans (ATCC^® 2091) was determined by adopting the cup plate method reported by Ozcan et al⁴⁰ with slight modifications. The mean inhibition zone was calculated, and the value was taken as an indicator for the antifungal activity.

Fungal inoculum

Overnight culture of C. albicans was diluted with 0.9% sterile saline to obtain cultures containing 10⁶ colony-forming units (CFU)/mL of the microorganism.

Plate diffusion method

Tr-loaded LCG was compared to its placebo sample, and HPMC gel of Tr (1% w/w) was also enrolled in the study as a positive control. Petri dishes of 20 mL Sabouraud dextrose agar were seeded with 200 μL of the Candida inoculum (1% v/v). The plates were left to dry at room temperature for 15 min. Then, wells were cut out where 70 mg of each gel formulation was placed into each well. The plates were incubated at 37°C±0.1°C for 24 h. The results were recorded by measuring the inhibition zones around the wells.⁴⁰ All the determinations were made in triplicate for each formulation.

In vitro drug release study

In vitro drug release was carried out according to the dialysis bag method reported by Gupta et al⁷ and Kumar et al,⁴¹ with a slight modification. Tr release from LCG was compared to its release from HPMC-based hydrogel using the same final concentration and the same sink conditions. Tr solution in PG (1% w/v) was used as a control to ensure drug dialyzability.⁴² In all release experiments, each dialysis bag was fixed to a 50-mL glass beaker containing 25 mL of release medium of sodium phosphate buffer (SPB) with a pH value of 5.5. The experiment was carried out in a thermostated shaking water bath (Kottermann, type 3047; Hanigsen, Germany) at 32°C and 100 rpm. Drug solution in PG (0.5 mL), HPMC-based gel (0.5 g), and LCG (0.5 g) were added to dialysis bags (Visking 36/32, 28 mm, molecular weight cutoff 12,000–14,000; Serva, Heidelberg, Germany). Then, samples of 3 mL were withdrawn from release medium at fixed time intervals (0.5, 1.5, 2.5, 4, 6, 20, and 24 h) and filtered through a membrane filter (Nylon Acrodisc^®, 0.45 μ; Gelman Sciences Inc., Ann Arbor, MI, USA). After each sample withdrawal, the same volume of fresh phosphate buffer was added for compensation. All filtrated samples – in triplicates – were measured spectrophotometrically at 227 nm against blank. Results were represented as percentage release ± standard error of mean (SEM), and graph of % drug release versus time was plotted.⁴³

Ex vivo permeation studies

Preparation of skin samples

Female Wistar albino rats of a weight ranging from 150 to 200 g were used for the study. All animal work carried out in the current study was approved by the Animal Care and Use Committee (ACUC) at the Faculty of Pharmacy, Alexandria University and was in accordance with the International Principles for Laboratory and Care of the European Community Directive of 1986; 86/609/EEC. The animals were kept under standard laboratory conditions and veterinary supervision with access to water and food ad libitum. The animals were anesthetized by intraperitoneal injection (IP) of thiopental solution (40 mg/kg).⁴⁴ Dorsal hair of the animals was removed using shaving razor in the direction of tail to head, and the animals were then visually inspected to ensure the absence of any skin damage.⁴⁵ The shaven part of skin was separated from animals, and hypodermis was removed with scalpel.^40,46 The excised skin was washed with normal saline, stored in refrigerator (−20°C) and used within 1 week of harvest.^45,47

Permeation studies

Ex vivo release studies of Tr from lecithin-based LCG and HPMC hydrogel were carried out using modified Franz diffusion cells (surface of 3.14 cm² and volume =9 mL).^26,48 The receptor compartment of the Franz diffusion cells was filled with 9 mL of SPB of pH 5.5⁵,⁴¹ which was suitable for a proper sink condition. The temperature was maintained at 32°C±0.5°C^8,45,49 with shaking at 100 rpm throughout the experiment.

The excited dorsal rat skin was mounted between the donor and the receptor compartments of the diffusion cell where the SC was facing the donor side.⁵⁰ Then the gel preparations were applied uniformly on the membrane at an amount equivalent to 2 mg of drug. A 2 mL of aliquot was periodically withdrawn at suitable time intervals (2, 4, 6, 8, 10, 12, and 24 h) from the sampling arm of the receptor chamber and was replaced immediately with fresh release medium. All samples – in triplicates – were filtered through a 0.45 μm pore size Teflon membrane filter and analyzed by a validated HPLC method at 227 nm after appropriate dilutions against blank solution prepared under the same experimental conditions. The percentage of cumulative drug permeated through rat skin was calculated and plotted versus time.

Skin retention study

At the end of permeation experiments (24 h), the effective diffusion area of the skin was carefully separated, gently scraped using spatula, and washed with methanol to remove the excess formulations remaining on the skin surface. Skin was then cut into small pieces using a pair of scissors, and all the pieces obtained were vortexed (GEMMY vortex mixer, VM-300; Germany Industrial Corp., Taipei, Taiwan) with methanol. Then samples were left for soaking in methanol for 24 h⁴⁵ and shaking at 37°C⁵ at 100 rpm using thermostated in a water bath to ensure effective extraction of the retained drug from the skin. Then, they were subjected to bath sonication for 1 h, and the resulting mixture was then centrifuged (PLS-5 model; GEMMY Industrial Corp., Taiwan) at 8,000 rpm⁵¹ for 20 min. The supernatant was then filtered by 0.22 μm pore size Teflon membrane filter and was analyzed by a revalidated HPLC method at 243 nm after suitable dilution. Placebo skin extract was prepared by applying placebo formulations using the same experimental conditions. The placebo extract was set up for the study as blank in order to ensure the absence of interference at the measured wavelength.⁴³ The percentage of Tr deposited into the skin and that remained on its surface were calculated and expressed as mean ± SEM (n=3).

Reverse phase HPLC (RP-HPLC) analysis

The concentration of Tr was determined by a validated HPLC methodology. The HPLC instrument (Agilent 1260 Infinity, Germany) equipped with isocratic pump (G1310B), UV-variable wavelength detector (G1314F) and Agilent ChemStation^® software 32-bit version (revision B.02.01 SR1) was used. The mobile phase was composed of a degassed mixture of acetonitrile and potassium dihydrogen phosphate buffer solution (0.01 M, pH 6) with a ratio of 50:50 (v/v). Samples (20 μL) were manually injected on a reversed-phase C18 column (Agilent HC-C18 (2), 4.6×250 mm, 5 μm). The flow rate of mobile phase was maintained at 1 mL/min, and the retention time was 7.07±0.21 min. Detection of amount of Tr in the receptor medium was performed at 227 nm, while the detection of Tr deposited in the skin was shifted to another wavelength (λ=243 nm) in order to cancel the interference with the components of skin extract that occurred at λ=227 nm. Concentration of Tr was determined using the corresponding calibration curve constructed by the peak area. The HPLC method was validated at both the detected wavelengths. The method was found to be suitable for Tr quantification at the selected wavelengths where at λ=227 nm, the calibration curve was linear over the range of 2.5–200 μg/mL, R²=0.9999, the precision (%RSD) of intra-day and inter-day ranged from 0.06% to 2.58% and 0.33% to 7.91%, respectively, and the accuracy (% recovery) of intra-day and inter-day ranged from 91.27% to 106.18% and 92.76% to 103.85% respectively. While at λ=243 nm, R²=0.9999, %RSD of intra-day and inter-day ranged from 0.08% to 4.91% and 0.32% to 12.37%, respectively, and % recovery of intra-day and inter-day ranged from 94.88% to 103.44% and 94.43% to 101.42%, respectively.

In vivo studies

In vivo skin deposition study

The in vivo skin deposition study was carried out for Tr-loaded lecithin-based nanogel formulation (1% w/w) against HPMC hydrogel as was described by Aggarwal et al^8,52 with a slight modification. First, female Spargue Dawley rats weighing 250–300 g were anesthetized with an IP of cocktail anesthesia⁵³ of ketamine hydrochloride (80–100 mg/kg)^7,54 and xylazine (10 mg/kg). The dorsal skin of rats was shaved using shaving razor in the direction of tail to head and was visually observed to ensure the absence of any skin. Then, a proper weight of LCG and the control (equivalent to 2 mg of Tr) were applied on the dorsal prepared region. The animals were divided into five groups for sampling at different time points: 5 min, 2 h, 4 h, 6 h, and 24 h (n=4). They were sacrificed at the specified time intervals, and the dorsal back skin was excised carefully and washed with methanol to remove the residual formulations on skin surface. Then the skin was prepared as previously described in ex vivo drug retention study in order to extract Tr deposited on the skin and subsequently analyzed by HPLC under same chromatographic conditions used in ex vivo study.

In vivo antifungal activity of the organogel

In vivo antifungal activity study was performed according to the method described by Gupta et al⁵⁴ with slight modifications.

Preparation of the animals

Female Swiss albino mice, 6–8 weeks of age, were housed in individual cages where food and water were provided ad libitum. An area of ~2 cm² from each animal’s back was shaved 48 h before infection. In order to establish Candida cutaneous infection, animals were initially immunosuppressed by IP injection of methylprednisolone (10 mg/kg of body weight) for three successive days starting 48 h before infection.

Preparation of Candida and mice infection

C. albicans (ATCC^® 2091) was grown overnight in YPD broth (yeast extract 10 g/L, peptone 20 g/L, and dextrose 20 g/L) containing 10% fetal bovine serum (FBS) for 14–18 h with vigorous shaking at 30°C. Next day, the grown culture was subcultured into fresh YPD broth containing 10% FBS and was further shaken at 37°C for 2–3 h. This step converted Candida to the virulent pseudohyphae form which has the ability to establish cutaneous infection.⁵⁵ C. albicans, 3×10⁵ CFU per 50 μL, was subsequently injected intradermally in the middle of the shaved area of individual mice used to induce infection.

Treatment of fungal infection

Treatment began 72 h after the infection was induced where test formulation was topically applied once daily for three consecutive days. Animals were divided into three groups each containing four mice. The first group was treated with liquid crystalline organogel loaded with Tr (1% w/w). The second group was treated with equivalent dose of Tr HPMC-based hydrogel while the third group served as a control receiving no formulation. All animals were sacrificed 24 h following the last treatment where the infected skin sites were excised and collected in sterile saline. Each skin sample was homogenized to release C. albicans cells from the skin into the sterile saline solution. Then, the skin homogenate was serially diluted in saline and plated onto YPD agar. Plates were incubated for 48 h at 37°C±1°C, and then CFU values were counted.⁵⁵

Skin sensitivity and histological examination studies

The purpose of these studies was to detect the skin sensitizing and irritant potential of the optimized formulation after topical application. Female Swiss albino mice of 20–25 g were selected for these studies. The negative control group was treated with normal saline⁴⁵ while formalin was used as a standard irritant^20,37 for the positive control group. The dorsal region of mice was shaved 24 h prior to the application of the formulations⁵² using a hair remover cream (Veet^®, Reckitt Benchiser). Then, 200 mg of LCG containing 2 mg Tr was applied on the shaved area with uniform spreading once daily for three consecutive days (n=3). The skin was checked for any visible difference, such as erythema after the application of formulations for three successive days. The erythemal scores were recorded (ranging from 0 to 4) on the basis of the degree of redness as follows: no redness =0; slight redness (barely perceptible-light pink) =1; moderate redness (dark pink) =2; moderate to severe redness (light red) =3; and severe redness (extreme erythema) =4 grade.⁵⁴

On the third day, animals were sacrificed, and the skin was cut and processed as reported by Azeem et al.⁵⁶ Briefly, specimens from control groups and the test group were fixed in 10% (v/v) buffered formalin. Subsequently, each tissue was rinsed thoroughly with water, dehydrated using a graded series of alcohols, embedded in paraffin wax, and microtomed. Then, the sections were stained with hematoxylin and eosin followed by observation under a high-power light microscope.

Statistical analysis

Statistical analysis of the results was carried out using analysis of variance (ANOVA) with the level of significance at P<0.05 (GraphPad Prism, version 6; GraphPad Software, Inc., La Jolla, CA, USA).

Results and discussion

The investigated lecithin organogel is composed of lecithin as gelator, nonpolar organic solvent as external phase, and polar solvent that is usually water. Natural lecithin such as Phospholipon 90 G containing not less than 90% phosphatidylcholine content of unsaturated fatty acids was selected for the organogel preparation. Different oils were screened for their ability to form organogel with the selected lecithin at two mass ratios of 1:1 and 1:2 (lecithin to oil). Among the screened oils, only capryol oil was able to form lecithin organogel at 1:1 mass ratio while others such as Plurol olique^® (ployglyceryl-6 diolate), Peceol^® (glyceryl mono-oleate), Maisine 35-1^® (glyceryl monolinoleate), and isopropyl myristate failed to form organogels with lecithin at both the selected ratios.

Construction of ternary phase diagram

As the phase behavior of PL–oil systems may be influenced by the addition of other compounds, the ratios of lecithin, water, and CAP oil that would lead to the formation of liquid crystals in a gel state at room temperature were first investigated. Ten mixtures were prepared, as depicted in Table 1. Visually, LCG appeared as slight hazy and viscous mixture,⁵⁷ and their structure was confirmed by PLM and transmission electron microscopy (TEM). Among the screened mixtures, only four samples (F1–F4) were able to form LCG. As shown in Table 1, addition of water in a range of 0.3%–26.67%, capryol oil in a range of 30.21%–40%, and phospholipon 90 G in range of 69.49%–33.33% resulted in the formation of LCG systems. Figure 1 represented the constructed ternary phase diagram of the investigated liquid crystalline system (lecithin/CAP/water). Our target in this study was to prepare stable gel that is able to enhance Tr skin deposition using the least possible concentration of lecithin in order to produce a commercial product at a reasonable cost. Thus, based on the phase diagram study, a lecithin to oil mass ratio of 1:1.2 was selected for further characterization. In addition, it was believed that organogel system holding the minimal water content would be of choice to avoid Tr precipitation upon storage due to its hydrophobicity and to maintain the whole system stability. Therefore, a formulation of lecithin to oil mass ratio of 1:1.2 comprising 38.46% lecithin, 46.16% capryol, and 15.38% water was chosen for further characterization. This formulation was given “FC” coding.

Table 1.

Composition of LCG constructing phase diagram (lecithin/capryol G90/water)

Formula	G90:CAP weight ratio	G90 (%)	CAP (%)	Water (%)	Visual observation
F1	2.3:1	64.97	28.25	6.78	Hazy gel
F2	1.5:1	42.61	28.41	28.98	Hazy gel
F3	1:1	36.23	36.23	27.54	Slight hazy gel
F4	1:1.2	33.33	40	26.67	Slight hazy gel
F5	1:1.5	29.07	43.60	27.33	Clear solution
F6	1:2	28.35	56.68	14.97	Clear solution
F7	1:3	20.49	61.48	18.03	Clear solution
F8	1:4	17	68.03	14.97	Clear solution
F9	1:7	11.16	78.13	10.71	Clear solution
F10	1:9	9.09	81.82	9.09	Clear solution

Abbreviations: LCG, liquid crystalline nanogel; G90, lecithin; CAP, capryol.

Figure 1.

Ternary phase diagram of the selected system components (lecithin/capryol 90/water) in weight percentage showing area of LCG.

Abbreviation: LCG, liquid crystalline nanogel.

Characterization of liquid crystalline organogel

Organoleptic characteristics

Various physical parameters were checked for the chosen formulations. The physical parameters involved color, appearance, smoothness/grittiness, and ease of application.³⁴ The selected organogel appeared yellowish, slight hazy, and smooth with no phase separation. The gel was free from any gritty particles and spread easily over the skin. It was slight greasy and tacky upon its application on the skin while after 5 min, the skin has no longer looked greasy or tacky.

pH

pH value of the selected formulation was estimated using pH paper, and it was found to be in a range of 5–6 approximating the normal pH range of skin. Thus, it was considered as the acceptable range that might help to reduce the irritation produced upon its dermal application.^8,41,51

Viscosity measurements

For any formulation to be used for topical drug delivery applications, it is essential to study its rheological behavior. Viscosity measurements were determined by applying increasing and decreasing values of shear rate, in order to reveal any possible thixotropic behavior. A plot of shear stress in dyne/cm² versus shear rate in 1/second (S⁻¹) was constructed where the shear rate was increased up to a certain value and then immediately decreased to the starting point.⁵⁸ As shown in Figure 2, the up and down curves did not completely superimpose on each other, and a hysteresis loop was formed due to the decrease in viscosity of the organogel with increasing shearing time. Thus, rheogram of the tested organogel showed a non-Newtonian pseudo-plastic behavior with a slight thixotropy.⁵⁹

Figure 2.

Rheogram showing the pseudoplastic behavior with a slight thixotropy of LCG (FC) loaded with 1% w/w Tr (constructed by cone and plate viscometer) (n=2).

Abbreviations: FC, 38.46% lecithin, 46.16% capryol, and 15.38% water; LCG, liquid crystalline nanogel; Tr, terconazole.

The effect of drug incorporation was investigated in this study where viscosity of both placebo and drug-loaded lecithin organogel samples was determined. It was observed that incorporation of Tr in liquid crystalline organogel led to insignificant reduction of gel viscosity (P>0.05). At 2 rpm, viscosity of Tr-loaded LCG, expressed in mean ± SEM, was 9.7±1.60 poise (n=2) while placebo organogel showed 10.01±1.68 at the same shear rate. It was reported that drug loading might influence the microstructure of liquid crystalline systems via interaction with curved bicontinuous lipid bilayer of liquid crystalline phase, by making the microstructure became unstable and thus resulting in a phase transformation.⁶⁰ However, the rheological behavior of Tr-loaded LCG revealed that Tr did not affect the microstructure of LCG significantly.

Drug content uniformity/homogeneity

The drug content of the studied formulation was evaluated considering the range of 90%–110% of the claimed drug content required for most dosage forms including topical semisolid preparations.^61,62 Drug content homogeneity of the chosen liquid crystalline organogel was determined by a validated UV spectrophotometric assay at λ=243 nm (y =0.0263x +0.0391, R²=0.9993, the precision (%RSD) ranged from 0.10% to 0.69% and 0.44% to 2.13% for intra-day and inter-day, respectively, the accuracy (% recovery) of intra-day and inter-day ranged from 98.80% to 101.52% and 98.48% to 101.72%, respectively. The drug content was calculated from the calibration curve and expressed as (mean % ± standard deviation [SD]), n=3 and compared with that obtained from the HPMC hydrogel.

$$\text{Drug content}\%=\frac{\text{Actual drug content}}{\text{Theoritical drug content}}\times 100$$

The results showed that drug content of HPMC hydrogel exceeded the acceptable range (137.43%±33.96%). Thus, it failed to load the drug homogenously throughout its matrix, and this was obviously clear from the high standard deviation of its triplicates. In fact, poor drug distribution through HPMC matrix could be attributed to the hydrophilic nature of the gel, which is considered as an unfavorable environment for hydrophobic drugs; hence, Tr tends to aggregate and form lumps in the gel matrix rather than freely dispersed in. On the other hand, developed lecithin-based organogel showed good homogeneity with acceptable loading efficiency (110.19%±0.24%) and with the absence of lumps.

Polarizing light microscope evaluation

The phase behavior of the chosen LCG was confirmed using a polarized light microscope. This technique was applied to identify the hazy systems within the ternary phase diagrams whether they were stable emulsions or LC phases. The anisotropic nature of liquid crystalline system was confirmed under PLM where it showed birefringence due to its molecular organization³⁹ as shown in Figure 3.

Figure 3.

Polarized light microscopy photomicrographs of Tr-loaded LCG (FC) (magnification ×100).

Abbreviations: FC, 38.46% lecithin, 46.16% capryol, and 15.38% water; LCG, liquid crystalline nanogel; Tr, terconazole.

As there are some parameters such as drug loading and the alteration of the system components proportions could affect the packing parameter of lecithin, thus affecting the prepared liquid crystalline phase,^60,63 whether drug loading and water capacity would affect the microstructure formed or not was investigated. It was observed that the structure features of the liquid crystals of LCG was not influenced by the incorporation of Tr into the system, but it was mainly affected by water content as depicted in Figure 4. Addition of water at the level of 0.90%–8.33% elucidated clear isotropic liquid solution (Figure 4A), which could be due to the formation of isotropic microemulsion or due to the formation of liquid crystals³⁵ that were too small to be seen with used magnification (×100). Upon increasing water content from 9.09% to 14.73% as shown in Figure 4B–D, a hazy liquid dispersion was formed which appeared as small and disaggregated liquid crystals under PLM. At the level of 15.38%–26.67%, the viscosity of formulation increase forming a LCG where it showed well-structured liquid crystals under PLM as was elucidated in Figure 3.

Figure 4.

Polarized light microscopy photomicrographs of Tr-loaded LCG (FC) showing the effect of water content on LC formation.

Notes: (A) Isotropic system formed at water content of 0.90%–8.33%. (B) Low-density LCs at 9.09% water content. (C) LC density increased at 10.57%. (D) High-density LCs at 14.73% water content (magnification ×100).

Abbreviations: FC, 38.46% lecithin, 46.16% capryol, and 15.38% water; LCG, liquid crystalline nanogel; Tr, terconazole.

TEM

TEM was performed for the selected Tr-loaded liquid crystalline-based organogel (1% w/w) to confirm morphology and for particle-size analysis.²⁰ TEM demonstrated irregular and discrete microstructures for liquid crystalline organogel. The system showed liquid crystals of small particle size <50 nm as shown in Figure 5. Small particle size of liquid crystals could be attributed to the surface activity of capryol 90 oil,^64–66 which could influence the surfactant layer curvature of lecithin,⁶⁵ resulting in the reduction of the size of liquid crystals.

Figure 5.

Transmission electron microscopy photograph of lecithin-based LCG (FC) with 10-fold dilution in capryol (magnification ×10,000).

Abbreviations: FC, 38.46% lecithin, 46.16% capryol, and 15.38% water; LCG, liquid crystalline nanogel.

In vitro antifungal activity

As C. albicans is primarily responsible for various skin infections, it was used in the current study as a reference for the evaluation of in vitro antifungal activity of Tr. The in vitro antifungal activity of Tr against C. albicans (ATCC^® 2091) was determined in terms of mean diameter of inhibition zone (mm) ± SD (n=3). Tr-loaded LCG (1%w/w) showed significant higher in vitro antifungal activity (32.33±0.88) when compared to HPMC hydrogel (29.46±0.68), P<0.05. Surprisingly, this study was the first to reveal that placebo capryol-based formulations possessed an in vitro antifungal activity, where the placebo LCG showed nearly half of the in vitro antifungal activity of its drug-loaded formulation. This may be attributed to physicochemical properties of CAP oil. Capryol oil was reported to have a surface activity acting as nonionic surfactant⁶⁴/or cosurfactant^65,66 (HLB =6). Nonionic and cationic surfactants were suggested to have antifungal activity due to the inhibition of the steroidal component of the fungi, which forms an integral part of its cell wall by their surface-tension-lowering activity.^37,67 Moreover, capryol 90 contains 10% capric acid, which was reported to have antifungal activity.⁶⁸ Therefore, it is worthy to note that the in vitro antifungal potential of Tr-loaded liquid crystalline organogel was partially due to capryol oil itself. The higher in vitro antifungal activity of Tr compared to HPMC hydrogel confirmed the enhancement of physicochemical characteristics of Tr upon its incorporation in nanogel system.

In vitro release study

In vitro release of Tr from lecithin-based LCG was assessed using dialysis bags with proper molecular weight cutoff value (12–14,000). Solubility study of Tr in phosphate buffers of different pH was carried out at λ_max=227 nm. It was found that drug solubility, expressed as mean ± SD (n=3), was significantly decreased with pH increase (P<0.05). Tr solubility was lower in phosphate buffer of pH 7.4 (0.08±0.01 mg/mL) than phosphate buffer of pH 5.5 (2.75±0.14 mg/mL). This could be attributed to the basic functional group of the drug (NH-piperazine, pKa 8.7) that tended to be ionized in the acidic environment provided with buffer of pH 5.5. Consequently, drug release testing was carried out in phosphate buffer of pH 5.5 to attain proper sink condition.⁶⁹ Initial drug strength was unified among all formulations screened to omit the effect of concentration gradient.²⁷ Release profiles of Tr from liquid crystalline organogel, HPMC hydrogel, and plain drug solution in PG were performed using the dialysis bag method as shown in Figure 6.

Figure 6.

In vitro drug release profile of Tr from different formulations through dialysis bag: LCG (FC), HPMC hydrogel, and plain drug solution in PG.

Notes: The values represent mean ± SEM (n=3). Some error bars are too small to be shown.

Abbreviations: FC, 38.46% lecithin, 46.16% capryol, and 15.38% water; HPMC, hydroxy propyl methyl cellulose; LCG, liquid crystalline nanogel; PG, propylene glycol; SEM, standard error of mean; Tr, terconazole.

It was clear from the graph that LCG showed a delay in the release rate and also a decrease in the amount of Tr released in comparison with its release from the plain solution and the hydrogel. The percentage of Tr (%) released after 24 h from plain drug solution in PG- and HPMC-based hydrogel was 98.90%±2.00% and 64.77%±4.53%, respectively, which was significantly higher than LCG (P<0.01). As expected, Tr release rate was retarded when it was embedded into hydrophobic gel matrix.⁴⁹ Whereas, the high drug flux from HPMC gel could be attributed to increase its thermodynamic activity through the hydrophilic gel matrix. According to Higuchi,⁷⁰ the flux of a drug through a membrane increases as the drug thermodynamic activity increases.²³ This can be done either by increasing the drug concentration in the vehicle or by decreasing the drug solubility in the vehicle.⁷¹ Thus, Tr preferred diffusion through dialysis membrane rather than dispersion in hydrophilic gel unlike in case of PL-based gel.

Ex vivo studies

Ex vivo permeation study

Drug penetration into the skin could be enhanced using liquid crystalline phases that have been recently investigated for topical application.^36,63,72,73 In order to confirm this, comparative ex vivo permeation studies of Tr were performed from lecithin-based liquid crystalline organogel and HPMC-based hydrogel. The ex vivo release pattern of Tr from each formulation was shown in Figure 7.

Figure 7.

Ex vitro skin permeation of Tr from LCG (FC) against HPMC hydrogel through dorsal skin of rats using the Franz diffusion cell method.

Note: The values were expressed as a mean ± SEM (n=3).

Abbreviations: FC, 38.46% lecithin, 46.16% capryol, and 15.38% water; HPMC, hydroxy propyl methyl cellulose; LCG, liquid crystalline nanogel; SEM, standard error of mean; Tr, terconazole.

The percentage of the cumulative amount of Tr released in the diffusion medium (SPB of pH =5.5) at different time intervals was calculated from the calibration curve in SPB and expressed as mean % ± SEM as shown in Figure 7. Permeation of Tr was improved upon its incorporation into organogel matrix as Tr showed nearly twofold increase in its permeation when compared with its permeation from HPMC hydrogel. This could be attributed to the physicochemical characteristics of the organogel components. Both lecithin^30,74,75 and capryol 90^® oil^76,77 were reported as skin penetration enhancer. In addition, perhaps the particle size was one of the parameters that influenced percutaneous permeation of Tr.⁷² The small particle size of the system (<100 nm) might create a large surface area for the drug to transfer deeply into the skin, thus improving its partition through the skin. Finally, skin penetration and percutaneous delivery of Tr might also be affected by the interactions of the different liquid crystalline systems with the SC.^63,78 A comparison between in vitro Tr release and its ex vivo permeation and deposition through rat skin, after 24 h, was shown in Table 2.

Table 2.

In vitro release through dialysis membrane, ex vivo permeation, and ex vivo skin retention studies from LCG- and HPMC-based hydrogel

Formulation codea	% Tr released across dialysis bagc	% Tr permeated through the skinc	% Tr accumulated into skinc
LCG	9.93±0.21	3.22±0.34	12.25±0.40
HPMC	64.77±4.53	1.81±0.31	2.61±0.31
Tr solutionb	98.90±2.00	–	–

Notes:

^aAll formulations are loaded with equivalent amount of Tr (1% w/w).

^bTr solution in PG was enrolled in in vitro release study to prove its dialyzability.

^cThe data of the drug released after 24 h were expressed as % mean ± SEM (n=3).

Abbreviations: FC, 38.46% lecithin, 46.16% capryol, and 15.38% water; HPMC, hydroxy propyl methyl cellulose; LCG, liquid crystalline nanogel; SEM, standard error of mean; Tr, terconazole.

Skin retention study

Skin retention study was carried out to investigate whether the LCG could target Tr into skin layer with a sustained localizing effect or not. Thus, skin samples were collected at the end of permeation study to estimate Tr percentage deposited in the skin. The amount of Tr retained in the skin was estimated using HPLC technique under the same chromatographic conditions applied in the section of skin permeation study except for the wavelength used for the detection. The amount of Tr permeated into the release medium was detected at 227 nm, while the deposited amount in the skin was detected at λ=243 nm in order to cancel the interference with components of skin extract that appeared at λ=227 nm.

Tr accumulation into the skin was greater than its percutaneous permeation from LCG. This was obviously revealed from the results of ex vivo skin retention study given in Table 2 where each point was represented as a mean % ± SEM. In addition, LCG showed approximately fivefold significant higher accumulation of Tr (P<0.01) when compared to HPMC hydrogel. A comparison between the percentage of Tr permeated through the skin and its % deposited in the skin from LCG against HPMC gel was depicted in Figure 8. The significant enhanced drug deposition from capryol-based LC organogel could be attributed to more than one factor. One of the mechanisms reported for lyotropic liquid crystals (LLCs) was that they demonstrate high similarity to the intercellular lipid membrane of the skin so they might result in good adhesiveness to the skin and good delivery of the drug.^35,39,63 The LLC systems could also exhibit good penetration, due to the very low interfacial surface tension arising at the oil/water interface, and they may facilitate the progressive diffusion of the drug into the skin.^79,80 In addition, small particle size of LCs that was probably due to the surface activity of capryol oil (HLB =6) might also increase Tr partitioning into the skin as mentioned earlier. Furthermore, capryol oil could affect Tr permeation by another mechanism rather than its impact on particle size. Generally, nonionic surfactants were reported to emulsify sebum and extract skin lipids, thus enhancing the partition of the drug and allowing it to penetrate into the cells more effectively.⁴⁵

Figure 8.

Comparison of the percentage of drug permeation and drug retention from different gel matrices through ex vivo skin permeation studies after 24 h.

Abbreviations: HPMC, hydroxy propyl methyl cellulose; LCG, liquid crystalline nanogel; Tr, terconazole; h, hours.

In vivo studies

In vivo skin deposition studies

Liquid crystalline organogel was investigated to assess the proportion of dermal deposition of Tr at different time intervals. In fact, it is more preferable for a skin targeting formulation to exhibit rapid penetration into the SC with drug depot properties as suggested by Aggarwal et al.⁵² The results of in vivo skin deposition, representing the amount of Tr retained in the skin (mean μg ± SEM), as shown in Table 3 revealed that lecithin-based liquid crystalline organogel exhibited rapid penetration of Tr into the skin. Where after 5 min, ~72.1±1.9 μg of Tr was deposited from LCG into the skin showing 2.4-fold significant increase when compared with its release from HPMC hydrogel (P<0.01). Then the amount of Tr was gradually decreased regardless the formulation used. Yet a significant higher drug deposition was attained from the nanogel in comparison with the hydrogel up to 4 h post application (P<0.01). Whereas, 6 h after application, LCG showed 1.4-fold higher increase in Tr skin localization than HPMC gel, but this increase was not significant (P>0.05). However, at later stages (24 h), LCG showed 2.67-fold increase in Tr deposition, which was significant (P<0.05) when compared with its deposition from HMPC hydrogel. The differences in Tr skin deposition between LC organogel and HPMC hydrogel could be attributed to various factors such as microstructure of the organogel matrix, penetration enhancing effect of system components, and particle size of liquid crystals of the organogel. The effect of these parameters on skin deposition was mentioned previously in ex vivo retention study. It is worthy to note that there was difference in the results of both ex vivo and in vivo skin retention studies where ex vivo study revealed 12.25%±0.34% deposition of Tr in the skin at 24 h post application. This percentage was much higher than that obtained from in vivo study at all investigated time intervals. This difference could be attributed to the accelerated drug elimination from the skin to the systemic circulation due to the presence of blood supply to the dermis of the rat skin. Although the experimental conditions were different, the results obtained from the in vivo study confirmed our ex vivo observation that lecithin-based organogel system could enhance skin targeting of Tr into the skin much higher than HPMC hydrogel. It is also imperative to notify that the current investigation has focused substantially on cutaneous targeting of Tr into the skin and not on its percutaneous permeation. Consequently, focus was completely on drug deposition in the skin, and no attempt was adopted to analyze its concentration in the blood.

Table 3.

In vivo skin deposition study representing amount of Tr deposited in the skin at various time intervals after single topical application of LCG- and HPMC-based hydrogel

Time (hour)	Formulationsa,b (μg deposited)
	LCG	HPMC gel
0.08c	72.1±1.9	30±0.8
2	67.1±2.8	24.8±2.8
4	63.1±1.8	18.4±8.0
6	24.4±5.8	17.4±2.0
24	20.5±1.5	7.7±3.9

Notes:

^aBoth the gels were loaded with equivalent amount of Tr (1% w/w).

^bThe data were expressed as mean ± SEM (n=4).

^c0.08 h is equivalent to 5 min.

Abbreviations: FC, 38.46% lecithin, 46.16% capryol, and 15.38% water; HPMC, hydroxy propyl methyl cellulose; LCG, liquid crystalline nanogel; SEM, standard error of mean; Tr, terconazole.

In vivo antifungal activity

The optimized liquid crystalline organogel containing 1% w/w Tr was assessed for its in vivo antifungal potential against C. albicans using female Swiss albino mice in comparison with conventional gel. Induction of fungal infection was performed, and the in vivo antifungal activity of LC organogel was assessed through a quantitative analysis of the fungal infection in terms of CFUs found in the skin lesion of infected mice following the treatment course. In vivo microbiological activity of Tr-loaded LCG was compared to HPMC hydrogel loaded with equivalent amount of Tr (2 mg Tr). Negative control receiving no formulation was also enrolled in the study for comparison. Three days after the treatment course, the mice were sacrificed, each skin sample was homogenized in sterile saline, and C. albicans count was determined. The results are shown in Figure 9. Lecithin organogel showed log CFU of 1.03±0.35 while groups receiving HPMC gel and untreated group showed 2.3±0.12 and 3.55±0.04, respectively. Applying one-way ANOVA test with post hoc Tukey–Kramer test, Tr-loaded lecithin nanogel revealed a significant reduction of the fungal infection after the application for three successive days when compared to the group receiving HPMC gel (P<0.01) and to the group receiving no formulation (P<0.0001). Therefore, in vivo antifungal results were in agreement with the results of both ex vivo and in vivo deposition studies confirming the improvement of physicochemical properties and skin targeting of Tr after its incorporation in liquid crystalline organogel matrix. Nanosize of the organogels improved contact and adhesion as well as the use of penetration enhancers, all contributed to the superior effectiveness of LC nanogel over conventional hydrogel.

Figure 9.

In vivo antifungal efficacy of LCG (FC) as compared to HPMC gel and untreated group (control) after three successive days of single application per day.

Notes: Data were expressed as mean ± SEM (n=4). *P<0.01, **P<0.0001.

Abbreviations: C. albicans, Candida albicans; CFU, colony-forming unit; HPMC, hydroxy propyl methyl cellulose; LCG, liquid crystalline nanogel; SEM, standard error of mean.

Skin sensitivity and histological examination studies

Topical formulation should be evaluated not only in terms of carrier capacity and enhancing drug permeation through the skin but also in terms of its tolerability and toxicity. Liquid crystalline organogels were composed of large amounts of surfactants and oil; hence, it was particularly important to consider the potential skin irritation and toxicological reactions resulting from topical application. The test was carried out for both blank and medicated organogels. The negative control group was treated with normal saline⁴⁵ while formalin was used as a standard irritant^20,37 for the positive control group.

The skin was observed for any visible change, such as erythema at 24, 48, and 72 h after the application of formulations. The mean erythemal scores were recorded (ranging from 0 to 4) depending on the degree of redness. There was no apparent sign of edema, erythema, papules, wrinkling, or dryness on mice skin 2 days after application of all the formulations including the positive control receiving formalin. However, on the third day severe erythema of grade 4 was appeared on the positive control group and only slight skin dryness and wrinkling appeared on the mice skin receiving other formulations including untreated group receiving saline (Figure 10). Perhaps, skin dryness occurred due to the effect of the depilatory cream and not because of the formulations.

Figure 10.

Histological microphotographs of vertical section of mouse skin after hematoxylin and eosin staining.

Notes: (A) Positive control treated with formalin at low-power view (×100); (B) negative control treated with saline at low-power view (×100); (C) positive control treated with formalin at high-power view (×400); (D) negative control treated with saline at high-power view (×400).

After visual examination of the skin of the animal groups for three consecutive days, the skin specimens were histologically examined to confirm the clinical assessment of skin sensitivity study. Microscopic pictures of the optimized placebo and Tr-loaded organogels, positive control (formalin), and negative control (saline 0.9%) were shown in Figure 10A and B. It was observed that skin of negative group treated with saline had a compact SC with closely conjugated corneocytes layer⁷⁵ at high-power lenses (×400) (Figure 10D). The skin specimens also showed normal epidermis, dermis, and subcutaneous tissues when observed at low-power lenses (×100) under photomicroscope (Optika B-159; Optika Microscopes, Italy) as shown in Figure 10B. On the other hand, the negative group treated with formalin showed significant change in the histology of the skin. The formalin-treated specimen showed obvious disruption in the SC organization in addition to the presence of edema and inflammatory cellular infiltration in the dermis (Figures 10A and 11C). The photomicrograph of formalin skin samples along with the apparent signs of skin irritation (severe erythema) observed upon visual examination of the skin specimens confirmed the irritation potential of formalin.⁵⁶

Figure 11.

Histological microphotographs of vertical section of mouse skin after hematoxylin and eosin staining.

Notes: (A) Skin sample treated with placebo capryol-based LCG (FC) at low-power view (×100); (B) skin sample treated with Tr-loaded capryol-based LCG (1% w/w) at low-power view (×100); (C) skin sample treated with placebo capryol-based LCG at high-power view (×400); (D) skin sample treated with Tr-loaded capryol-based LCG at high-power view (×400).

Abbreviations: FC, 38.46% lecithin, 46.16% capryol, and 15.38% water; LCG, liquid crystalline nanogel; Tr, terconazole.

It was worthy to note that the histological samples of the optimized placebo organogel and the medicated gel were nearly similar. They showed skin structure more or less similar to skin treated with the negative control (Figure 11). The dermis layer of the optimized organogels was devoid of any inflammatory cells confirming their nonirritant effect on skin.⁵⁶ Whereas, the application of these nano-based organogels caused a change in the SC where an increase in the overall thickness of the SC was observed at high-power lenses (×400) as depicted in Figure 11C and D, respectively. This might be one of the possible contributing factors by which lecithin nanogels increased the permeation of Tr into the skin. The increase in the thickness of SC could be attributed to the composition of lecithin organogel where lecithin itself could mix and fuse with skin lipids resulting in loosening of the skin structure and disorganization of the lamellar arrangement of the lipids.^81,82

To conclude, lecithin organogels could weaken the SC barrier and consequently facilitate Tr permeation through the skin. Moreover, they were considered nonirritant delivery systems according to their visual observation and histological examination of the treated skin samples. Hence, lecithin-based liquid crystalline organogel seemed to be effective and safe nanocarriers for dermal delivery.

Conclusion

The current study aimed to investigate the relevance of nano-sized lecithin-based liquid crystalline organogel to improve the physicochemical characteristics of Tr in order to implement its dermal application in skin candidiasis. A graphical abstract was designed to summarize the main findings of the whole study. The study revealed that lecithin/capryol 90/water mixtures were able to form in situ liquid crystalline organogel at certain component ratios as shown in the phase diagram study. The microstructure of LCG was confirmed by PLM and TEM observations where PLM showed a birefringent behavior while TEM images showed discrete and irregular shapes with particle size <100 nm. A rheological study showed a non-Newtonian behavior with slight thixotropic properties. The results of ex vivo and in vivo skin deposition studies showed that lecithin liquid crystalline organogel could significantly enhance skin targeting of Tr with a skin drug reservoir properties when compared to HPMC hydrogel. The absence of any sign of skin inflammation during the acute irritation study indicated the safety of LCG for dermal drug delivery. In addition, the histological examination revealed a morphological alteration of the SC where its thickness was increased with a loose conjugation of corneocyte layers. This resulted in an increase in the permeation of Tr into skin dermis.