Improved skin permeation of methotrexate via nanosized ultradeformable liposomes
Authors Zeb A, Qureshi OS, Kim H, Cha J, Kim H, Kim JK
Received 30 March 2016
Accepted for publication 10 June 2016
Published 8 August 2016 Volume 2016:11 Pages 3813—3824
Checked for plagiarism Yes
Review by Single anonymous peer review
Peer reviewer comments 2
Editor who approved publication: Prof. Dr. Thomas J. Webster
Alam Zeb, Omer Salman Qureshi, Hyung-Seo Kim, Ji-Hye Cha, Hoo-Seong Kim, Jin-Ki Kim
College of Pharmacy, Institute of Pharmaceutical Science and Technology, Hanyang University, Ansan, Gyeonggi, Republic of Korea
Abstract: The aim of this study is to investigate methotrexate-entrapped ultradeformable liposomes (MTX-UDLs) for potential transdermal application. MTX-UDLs were prepared by extrusion method with phosphatidylcholine as a bilayer matrix and sodium cholate or Tween 80 as an edge activator. The physicochemical properties of MTX-UDLs were determined in terms of particle size, polydispersity index, zeta potential, and entrapment efficiency. The deformability of MTX-UDLs was compared with that of methotrexate-entrapped conventional liposomes (MTX-CLs) using a steel pressure filter device. The skin permeation of MTX-UDLs was investigated using Franz diffusion cell, and the skin penetration depth of rhodamine 6G-entrapped UDLs was determined by confocal laser scanning microscopy. MTX-UDLs showed a narrow size distribution, with the particle size of ~100 nm. The deformability of MTX-UDLs was two to five times greater than that of MTX-CLs. The skin permeation of MTX-UDLs was significantly improved compared with MTX-CLs and free MTX solution. The optimized UDLs (phosphatidylcholine: Tween 80 =7:3, w/w) showed a higher fluorescence intensity than conventional liposomes at every increment of skin depth. Thus, the optimized UDLs could be promising nanocarriers for systemic delivery of MTX across skin.
Keywords: ultradeformable liposomes, deformability, methotrexate, skin permeation, transdermal delivery
Transdermal drug delivery has been extensively studied for the past few decades as an attractive and valuable alternative for oral and parenteral administration.1,2 The major advantages of transdermal delivery are convenience, noninvasiveness, improved patient compliance, avoidance of first-pass metabolism, avoiding some serious side effects, and bypassing the variables affecting the drug absorption in the gastrointestinal tract.3 Despite these obvious advantages of transdermal delivery, the number of drug molecules administered via this route is quite limited due to the barrier function of stratum corneum, the outermost layer of the epidermis of skin.4 Various approaches including the use of permeation enhancers, microneedles, iontophoresis, electroporation, jet injection, and nanocarriers have been applied to increase drug penetration by overcoming the barrier function of skin.5
Liposomes as nanosized carriers are promising transdermal drug delivery systems since they are biocompatible and can carry both water-soluble and lipid-soluble drugs.6 Even though conventional liposomes (CLs), typically consisting of phospholipid and cholesterol (CH), have been investigated, their effectiveness in delivering a therapeutically significant amount of drug across skin is still a question mark.2 It was reported that liposomes with lower elastic modulus and higher deformability could be driven deep into the skin by hydration gradient when applied nonocclusively.7 Deformability was imparted to liposomes by incorporating surfactant known as an “edge activator” into lipid bilayers (Figure 1A). This new class of liposomes with an edge activator was termed as elastic, flexible, or ultradeformable liposomes (UDLs). The stress-dependent adaptability enables UDLs to squeeze themselves through the interstices of the stratum corneum by using transepidermal hydration gradient (Figure 1B), thus passing through the skin without disruption of vesicular structure.8 UDLs showed better in vitro and in vivo skin permeation than CLs when applied for diclofenac, ketotifen, triamcinolone acetonide, dexamethasone, hydrocortisone, estradiol, 5-fluorouracil, and insulin.9–15
Methotrexate (MTX) is a folate receptor antagonist that was originally developed as a chemotherapeutic agent to treat various kinds of malignancies, including leukemia, breast cancer, lung cancer, head and neck cancer, osteosarcoma, and non-Hodgkin’s lymphoma.16,17 It has also been reported that low doses of MTX are effective to treat some inflammatory and autoimmune conditions such as rheumatoid arthritis and psoriasis.18 Oral and parenteral administration of MTX is associated with serious side effects, including gastrointestinal and hepatic toxicity.19 Additionally, the first-pass metabolism with oral administration of MTX significantly reduces its bioavailability.20 Transdermal delivery of MTX can not only avoid the drawbacks of oral and parenteral formulations but also improve the therapeutic efficacy of MTX.21 However, the high polarity (log P=−1.85) and ionized form of MTX at physiologic pH make it challenging to be delivered transdermally via the lipophilic stratum corneum.19 For transdermal delivery of MTX, various kinds of nanocarriers such as nanostructured lipid carriers,21,22 magnetic silk fibroin nanoparticles,23 liposomes,24 ethosomes,20 solid-in-oil nanocarriers,19 and nanogels25,26 have been investigated. Considering the water solubility of MTX and the deformability of UDLs with aqueous phase, UDLs could be a promising nanocarrier for efficient transdermal delivery of MTX.
This study aimed to investigate the skin permeation potential of methotrexate-entrapped ultradeformable liposomes (MTX-UDLs) for transdermal delivery. MTX-UDLs were prepared by extrusion method using sodium cholate (SC) or Tween 80 (TW80) as an edge activator. MTX-UDLs with different ratios of lipid (L-α-phosphatidylcholine [PC]) to edge activator were prepared, and their physicochemical properties were characterized in terms of size, polydispersity index (PDI), zeta potential, and entrapment efficiency. The effect of different types and ratios of edge activators on the deformability of MTX-UDLs was evaluated and compared with methotrexate-entrapped conventional liposomes (MTX-CLs). The optimized MTX-UDLs formulations were then investigated for skin permeation by using Franz diffusion cell and confocal laser scanning microscopy (CLSM).
Materials and methods
MTX was kindly gifted by Huzhou Zhanwang Pharmaceutical Co., Ltd (Zhejiang, People’s Republic of China). PC was purchased from Avanti Polar Lipids Inc. (Alabaster, AL, USA). CH, SC, TW80, and Triton X-100 were purchased from Sigma–Aldrich Co. (St Louis, MO, USA). All other chemicals were of analytical grade and were used without any further purification.
Preparation of MTX-UDLs
MTX-UDLs were prepared by the extrusion method with slight modifications.27 Briefly, the mixture of a bilayer matrix (PC) and an edge activator (SC or TW80) was dissolved in 1 mL of chloroform/methanol (2/1, v/v). The organic solvent was removed by rotary evaporator (Rotavapor R-3; Büchi Labortechnik AG, Flawil, Switzerland) under reduced pressure at 40°C to form a thin lipid film. The thin film was further dried by using a stream of nitrogen gas for 30 minutes to remove the traces of organic solvent. The dried film was hydrated with the solution of MTX in phosphate-buffered saline (PBS) (pH 7.4). The hydration medium was preheated at 65°C, which is above the phase transition temperature (Tm) of PC. The hydrated suspension was sonicated in a bath type sonicator at 65°C for 30 minutes and extruded 20 times through 100 nm polycarbonate membrane by using a Mini-Extruder (Avanti Polar Lipids, Inc.). MTX-CLs were prepared by the same method except that CH was used instead of edge activator (SC or TW80). The prepared MTX-UDLs and MTX-CLs were stored at 4°C for further analysis. The composition of MTX-UDLs and MTX-CLs with different ratios of PC and SC/TW80/CH is presented in Table 1.
Table 1 Composition of MTX-UDLs and MTX-CLs in weight ratio
Physicochemical characterization of MTX-UDLs
The physicochemical properties of MTX-UDLs were characterized in terms of particle size, PDI, zeta potential, and entrapment efficiency. The average particle size and PDI of MTX-UDLs were determined by photon correlation spectroscopy using a Zetasizer Nano ZS (Malvern Instruments, Malvern, UK). Prior to measurement, MTX-UDLs were diluted 100 times with filtered deionized water. The zeta potential of MTX-UDLs was measured by electrophoretic light scattering using the same instrument. The entrapment efficiency of MTX-UDLs was determined by ultrafiltration centrifugation method.28 MTX-UDLs were added into Amicon Ultra-0.5 centrifugal filter units (Amicon Ultracel-10k; EMD Millipore, Billerica, MA, USA) and centrifuged at 14,000× g for 30 minutes. The separated vesicles were disrupted by 0.2% Triton X-100 in PBS (pH 7.4). The resultant solution was then analyzed for MTX contents by using UV–visible spectrophotometer (Ultrospec 7000; Biochrom Ltd, Cambridge, UK) at 303 nm. The entrapment efficiency (%) was calculated by using the following equation:
Transmission electron microscopy
The morphology of MTX-UDLs was confirmed by transmission electron microscopy (TEM) (JEM-2100F; JEOL, Tokyo, Japan) using a staining method.29 Diluted MTX-UDLs were placed on carbon-coated 400-mesh copper grid and were allowed to adsorb on to the grid. The sample was then negatively stained by adding a drop of 1% solution of phosphotungstic acid followed by drying at room temperature. Finally, MTX-UDLs were imaged with TEM operating at an accelerating voltage of 200 kV.
Deformability of MTX-UDLs
The deformability is a crucial property for an efficient skin permeation of UDLs. The deformability of MTX-UDLs was determined by using the stainless steel pressure filter device (Lipix Extruder; Northern Lipids Inc., Burnaby, BC, Canada).30 MTX-UDLs were extruded through 50 nm polycarbonate membranes at a constant pressure of 0.2 MPa. The rate of penetration was obtained from the volume of vesicles suspension extruded in 5 minutes. After extrusion, the average particle size of MTX-UDLs was measured by photon correlation spectroscopy using a Zetasizer Nano ZS (Malvern Instruments). The deformability index (D) of MTX-UDLs was calculated by the following equation:
where D is the deformability of vesicles, J is the rate of penetration through a permeability membrane, rv is the particle size after extrusion, and rp is the pore diameter of a permeability membrane (50 nm).
In vitro skin permeation of MTX-UDLs
Preparation of rat skin
Full-thickness skin was obtained from the abdominal area of healthy male Sprague Dawley rats weighing 260±20 g. The abdominal area of rats was shaved, and skin was carefully excised after sacrificing under deep isoflurane anesthesia. The underlying fats and connecting tissues of skin were carefully removed. Full-thickness skin was finally washed with saline and stored at −20°C.31 The skin was thawed for 30 minutes at room temperature prior to in vitro permeation study. All animal-handling procedures were performed according to the Guide for the Care and Use of Laboratory Animals of the National Institutes of Health and followed the guidelines of the Animal Welfare Act. All animal experiments were approved by the Institutional Animal Care and Use Committee of Hanyang University.
Skin permeation study
Skin permeation studies were performed using Franz diffusion cell assembly consisting of vertical diffusion cells (Model # 58-001-802; Hanson Research Corporation, Chatsworth, CA, USA), magnetic stirring control system, and heating circulation system with a programmable temperature control device. Franz diffusion cells had an effective permeation area of 1.77 cm2 and receptor cell volume of 7 mL. The receptor compartment was filled with 7 mL of PBS (pH 7.4) and constantly stirred at 500 rpm. The receptor compartment was maintained at 37°C±0.5°C with heating circulating system.31 The full-thickness rat skin was then mounted between donor and receptor compartments. Open hydration protocol was adopted to generate a driving force for the skin permeation of UDLs known as transepidermal hydration gradient.7,32 The upper surface of mounted skin was left dry and open for 12 hours, while the dermal side of the skin was in contact with the receptor medium. The aqueous dispersion of MTX-UDLs or MTX-CLs equivalent to 1.5 mg of MTX was loaded in the donor compartment, and 0.5 mL of the sample was withdrawn through the sampling port at predetermined times (0.5 hour, 1 hour, 2 hours, 4 hours, 8 hours, 12 hours, 16 hours, 20 hours, and 24 hours). The receptor phase was immediately replenished with an equal volume of fresh diffusion medium with the same temperature. Sink conditions were maintained throughout the experimental procedure. The collected samples were analyzed for MTX contents after suitable dilutions with PBS (pH 7.4).
Calculation of skin permeation parameters
The cumulative amount of MTX permeated per unit area was calculated by using the following equation:33
where Qn is the cumulative amount of drug permeated per unit area (μg/cm2) corresponding to the time of nth sample, Cn is the drug concentration in receptor fluid at the time of nth sample, Ci is the drug concentration in receptor fluid at the time of ith (n-1) sample, Vr is the volume of receptor solution (7 mL), Vs is the volume of sample withdrawn (0.5 mL), and A is the effective permeation area of diffusion cell (1.77 cm2).
The cumulative amount of MTX permeated per unit area (Qn) was plotted as a function of time. The steady-state flux (Jss expressed as μg/cm2/h) and lag time (tlag) were calculated from the slope and x-intercept of linear portion of graph, respectively. Permeability coefficient (Kp) was calculated by dividing the steady-state flux (Jss) by the initial amount of MTX in donor compartment. Enhancement ratio was calculated by dividing the flux of the test formulation by that of the control formulation (MTX-CLs).
Confocal laser scanning microscopy
CLSM was performed to evaluate the depth of skin penetration of UDLs using rhodamine 6G (R6G) as a fluorescence marker. R6G-entrapped UDLs (R6G-UDLs), R6G-entrapped CLs (R6G-CLs), and R6G solution (0.03% w/v) were applied to rat skin mounted on the Franz diffusion cell for 4 hours under the same conditions as in vitro skin permeation studies. After 4 hours incubation, the excess of each formulation was wiped off with a filter paper. The skin was washed with distilled water and finally frozen at −20°C. The frozen skin was vertically sectioned into 5 μm thick slices with a cryostat microtome. The skin sections were optically scanned at every 5 μm increment though the z-axis to measure the depth of fluorescence marker (R6G) penetration by using CLSM (TCS SP5; Leica Microsystems, Wetzlar, Germany). The optical excitation of R6G was carried out at 550 nm, while emission was observed at >560 nm. The images of skin sections (1,024×1,024 μm) were obtained at 10× magnification. The obtained images were then quantitatively analyzed for fluorescence intensity at various depths by using LAS AF Lite software.34–36
Evaluation of skin structure after MTX-UDLs treatment
The skin structure after MTX-UDLs treatment was investigated by differential scanning calorimetry (DSC) and attenuated total reflectance Fourier transform infrared spectroscopy (ATR-FTIR). The alteration of lipid organization in stratum corneum was analyzed since the permeation enhancers or transdermal formulations mainly induce structural changes in epidermis area, specifically stratum corneum.37 Epidermis from rat skin was separated by immersing in deionized water at 60°C for 2 minutes followed by gentle peeling off with forceps.38 The isolated epidermis was treated with the optimized MTX-UDLs (MTX-UDLs-T3) for 4 hours on Franz diffusion cell under the same conditions as in vitro skin permeation studies. The epidermis treated with MTX-UDLs was washed carefully with PBS and subjected to DSC and FTIR after blot-drying.
Thermal analysis of the epidermis was performed with a differential scanning calorimeter (DSC Q20; TA Instrument, New Castle, DE, USA). The epidermis samples weighing 5–10 mg were crimped in a standard aluminum pan and heated from 30°C to 150°C at 10°C/min heating rate with 50 mL/min nitrogen flow. The lipid organization of stratum corneum in epidermis was further studied by monitoring the molecular vibrations of lipid components from ATR-FTIR. The infrared transmission spectra were recorded using an FTIR spectrophotometer (FTIR-4100; JASCO International Co., Ltd, Tokyo, Japan). The epidermal sample of 1 cm2 was mounted on a diamond ATR crystal, and the spectra were recorded over the wave number range of 4,000–650 cm−1 at a resolution of 4 cm−1.
The storage stability of the optimized MTX-UDLs (MTX-UDLs-T3) was evaluated at 4°C and 25°C for 90 days. For the stability study, the formulation was stored in sealed glass vials flushed with nitrogen gas. Samples were collected at 0 day, 15 days, 30 days, 60 days, and 90 days and monitored for changes in particle size, PDI, zeta potential, and entrapment efficiency.
Data are expressed as the mean ± standard deviation (SD) of three independent experiments. Student’s t-test was applied using SPSS software (SPSS Inc., Chicago, IL, USA) to determine the statistical significant differences between groups. A value of P<0.05 was considered to be statistically significant.
Results and discussion
Preparation of MTX-UDLs
MTX-UDLs with different ratios of PC to edge activator were reproducibly prepared by extrusion method. In this study, SC and TW80 were selected as edge activators to impart deformability to the lipid vesicles. SC and TW80 are pharmaceutically acceptable and extensively investigated as edge activators for UDLs.32,39–41 Amphiphilic molecules such as bile salts (SC and sodium deoxycholate), Tweens (ethoxylated sorbitan esters), and Spans (sorbitan esters) have been extensively studied to provide deformability to liposomes.14,32,41 Bile salts and Tweens were preferred over Spans since hydrophilic surfactants induce more deformability by increasing membrane fluidity and forming transient holes in lipid bilayers than lipophilic ones.27 SC was selected from the bile salts due to nonsignificant difference in deformability between SC and sodium deoxycholate liposomes.15 From the results demonstrating that the unsaturated and highly flexible hydrocarbons in nonionic surfactants form more deformable membranes, TW80 was used to prepare UDLs in this study.27 The high curvature radius and mobility of edge activators enable UDLs to transform their shape and volume at lower energy. When exposed to mechanical stress or space confinement, edge activators relocate themselves in the zones of higher curvature, while phospholipids are positioned in the bilayer regions with smaller curvature. The readjustment of edge activators in UDLs was speculated to be the main reason why UDLs pass through the pores smaller than their own diameter without being disassembled.42,43 Optimal PC to edge activator ratios were selected as 8:2 and 7:3 (w/w) on the basis of particle size, PDI, entrapment efficiency, and deformability index from our preliminary studies. In the preliminary studies, MTX-UDLs with PC to edge activator ratio of 9:1 and 6:4 were also prepared and evaluated. MTX-UDLs with 9:1 (PC to edge activator ratio) showed low deformability index at 19.9 for SC and 22.3 for TW80, which were not significantly different from that of MTX-CLs. In the case of MTX-UDLs with 6:4 (PC to edge activator ratio), the entrapment efficiencies were <20% for SC and TW80. Considering the low deformability and low entrapment efficiency, MTX-UDLs with these ratios were excluded from further studies. MTX-CLs (PC:CH =8:2) were also prepared as a control formulation for comparison. The amount of MTX was kept constant at 1.5 mg/mL in all the formulations.
Physicochemical properties and morphology of MTX-UDLs
The physicochemical properties of the optimized MTX-UDLs were evaluated in terms of particle size, PDI, zeta potential, and entrapment efficiency (Table 2). The optimized MTX-UDLs showed mean particle sizes around 100 nm with narrow size distribution indicated by PDI values <0.150. The particle size distribution curve was unimodal in shape (Figure 2A). There were no statistical significant differences (P>0.05) in the particle size between UDLs containing the same PC to edge activator ratio. However, a slight reduction in the particle size was observed on increasing the amount of edge activator (PC:edge activator ratio, 8:2 vs 7:3). The particle size of MTX-UDLs decreased from 94.9 nm to 81.6 nm and from 102.6 to 87.7 nm when the amount of SC and TW80 increased, respectively. The decrease in particle size resulted from the increase in the curvature of UDLs at a higher edge activator amount.44,45 The increased curvature in UDLs with smaller particle sizes is also accompanied with the reduction of aqueous phase volume for MTX entrapment.13 From the results, the reduction in MTX entrapment in UDLs was related to the increased curvature with reduced aqueous phase volume at a higher edge activator amount. The zeta potential of MTX-UDLs indicated a negatively charged surface of vesicles. The negative zeta potential of UDLs with SC as an edge activator is originated from the anionic nature of SC (cholate anions). Even though TW80 is a nonionic surfactant, UDLs with TW80 showed the negative value of zeta potential due to the partial hydrolysis of polyethylene oxide head groups (CH2-CH2-O)n of TW80.40,44,46 TEM image of the optimized MTX-UDLs (MTX-UDLs-T3) confirmed their vesicular morphology with spherical shape and unilamellar structure (Figure 2B). The initial large multilamellar vesicles were converted into unilamellar MTX-UDLs after extrusion process. The particle size of MTX-UDLs was consistent with that from photon correlation spectroscopy. MTX-UDLs were uniform in particle size and showed a well-defined inner aqueous phase surrounded by lipid bilayer.
Table 2 Physicochemical properties of MTX-UDLs and MTX-CLs
Figure 2 Particle size distribution (A) and TEM image (B) of MTX-UDLs.
Deformability of MTX-UDLs
Deformability is a unique characteristic of UDLs, which facilitates the skin permeation across pores smaller than UDLs diameter. The deformation of lipid bilayer induced by an edge activator plays a crucial role in transdermal application of UDLs. The degree of stress-dependent adaptability and shape transformation in UDLs is represented by deformability index.47,48 The deformability indices of MTX-UDLs and MTX-CLs are shown in Figure 3. The deformability indices were in the order of MTX-UDLs-T3 (81.2) > MTX-UDLs-S3 (67.8) > MTX-UDLs-T2 (38.9) > MTX-UDLs-S2 (31.6) > MTX-CLs (15.8). There were significant differences (P<0.01) in deformability index between MTX-UDLs and MTX-CLs. The deformability of MTX-UDLs was attributed to the incorporation of SC and TW80 into lipid bilayer instead of CH. From the results, the deformability of MTX-UDLs was affected by the amount and type of the edge activator. MTX-UDLs-T3 and MTX-UDLs-S3 showed better deformability indices than MTX-UDLs-T2 and MTX-UDLs-S2, respectively. As the amount of SC and TW80 increased, the deformability index of MTX-UDLs also increased. At a higher amount of edge activator, the deformability of MTX-UDLs did not increase significantly and incorporation efficiency decreased compared with MTX-UDLs-T3 and MTX-UDLs-S3. Moreover, MTX-UDLs with TW80 showed a better deformability index than MTX-UDLs with SC. This could be attributed to the difference in chemical structures between two edge activators. TW80 has long, nonbulky, and highly pliable hydrocarbon chains in the structure, thus providing more flexibility to lipid bilayer, whereas SC has steroidal rings that are less flexible than hydrocarbon chains.27,49
In vitro skin permeation of MTX-UDLs
In vitro skin permeation studies using Franz diffusion cell were performed to evaluate the potential of MTX-UDLs for transdermal delivery. The cumulative amount of MTX permeated at each time point was plotted as a function of time to obtain skin permeation profiles of MTX-UDLs as shown in Figure 4. There were distinct differences between MTX-UDLs and MTX-CLs after 4 hours in the cumulative amount of MTX. From the skin permeation profiles of MTX-UDLs, various skin permeation parameters including the cumulative amount of MTX permeated for 24 hours, steady-state flux (Jss), lag time (tlag), permeability coefficient (Kp), and enhancement ratio were calculated and presented in Table 3. The skin permeation parameters were improved in the order of MTX-UDLs-T3 > MTX-UDLs-S3 > MTX-UDLs-T2 > MTX-UDLs-S2 > MTX-CLs > MTX solution. The cumulative amount of MTX permeated, steady-state flux, and permeability coefficient of MTX-UDLs were at least three times greater than those of free MTX solution regardless of the type and ratio of edge activators. From the results, MTX-UDLs were superior to MTX-CLs in all skin permeation parameters (P<0.01). The cumulative amount of MTX permeated for 24 hours and steady-state flux were the highest for MTX-UDLs-T3 at 470.3 μg and 20.2 μg/h/cm2, respectively. Accompanied by the increased steady-state flux, permeability coefficient, and enhancement ratio, MTX-UDLs-T3 showed the shortest lag time (0.68 hours), indicating the rapid achievement of steady state in skin permeation.50 These findings were in agreement with the results of deformability study. The enhanced skin permeation of MTX-UDLs in comparison to MTX-CLs as a control formulation could be explained by their ability to squeeze themselves through skin pores. The space detentions by skin pores bring about the shape transformation of UDLs, thus enabling them to deliver entrapped drugs across the skin.51 The driving force for shape transformation is originated from a transepidermal hydration gradient induced by water content difference between skin surface and epidermis.7,8,52,53 The destabilization of intercellular lipids and the increment of membrane fluidity in stratum corneum had been proposed as an alternative mechanism for enhanced skin permeation using UDLs.39,54 Considering the low log P-value and ionization tendency in physiological conditions, the skin permeation of free MTX via lowered barrier function of stratum corneum by UDLs would be limited. After in vitro skin permeation studies, the particle size of MTX-UDLs around 100 nm was detected in the receptor media. There was no structural change of skin after treatments with UDLs, which was confirmed by DSC and FTIR analysis. Therefore, the enhanced skin permeation of MTX-UDLs could be governed mainly by the shape transformation derived from their deformability.
Skin penetration of fluorescence marker (R6G)-entrapped UDLs
CLSM was conducted to investigate the depth of UDLs skin penetration by monitoring the accumulation of fluorescence marker (R6G). UDLs-T3 with optimal PC to TW80 ratio (7:3, w/w) was selected to entrap R6G for CLSM due to its excellent skin permeation parameters. The rat skin was treated with R6G-UDLs-T3, R6G-CLs, and R6G solution for 4 hours since all the formulations reached the steady state at this time point in skin permeation study. The confocal images of the skin at various depths are illustrated in Figure 5. From the photomicrograph, R6G-UDLs-T3 and R6G-CLs showed a higher fluorescence than R6G solution, specifically from 10 to 40 μm skin depth. For the comprehensive and quantitative analysis of R6G penetration, the fluorescence intensity was plotted versus the corresponding skin depth (Figure 6). From the results, the fluorescence intensity of R6G-UDLs-T3 was higher than that of R6G-CLs at every increment of skin depth. The maximum fluorescence intensity of R6G-UDLs-T3 was observed as 45.8 AU (arbitrary units) at 20 μm skin depth, which was 4.8 and 13.9 times higher than that of R6G-CLs (9.5 AU) and free R6G solution (3.3 AU), respectively. The higher fluorescence intensity of R6G-UDLs-T3 was in accordance with the results from in vitro skin permeation studies. The higher fluorescence intensity of UDLs corresponded to the improved skin permeation since the penetration and accumulation into viable epidermis area are regarded as the processes of percutaneous absorption.34,36
Figure 5 Confocal laser scanning photomicrographs with different depths of rat skin after 4 hour treatments with R6G-UDLs, R6G-CLs, and R6G solution.
Effects of MTX-UDLs on skin structure
The effects of MTX-UDLs on the lipid organization of stratum corneum were investigated by DSC after treating rat epidermis with MTX-UDLs-T3 for 4 hours. Stratum corneum, flat keratinized corneocytes embedded in intercellular lipid matrix, is regarded as a main permeability barrier in transdermal delivery. Permeation enhancers or transdermal formulations containing alcohols, terpenes, fatty acids, and surfactants penetrate into the intercellular regions and reduce the barrier function of stratum corneum by destabilization and fluidization of lipid bilayers.37,38,55 MTX-UDLs-T3 was selected for this study due to its efficient skin permeation among all MTX-UDLs. As shown in Figure 7A, the untreated skin showed endothermic transitions at 65.1°C, 82.5°C, and 115.4°C for the melting of intercellular lipids, protein-associated lipids, and denatured proteins in stratum corneum, respectively.56 When the intercellular lipid bilayer structure of stratum corneum is disrupted, lipid transition temperature around 65°C is significantly reduced.57 After the treatment with MTX-UDLs-T3, three endothermic transitions at 64.9°C, 82.3°C, and 115.6°C were observed indicating the absence of marked changes in lipid organization. These results suggest that the enhanced skin permeation of MTX-UDLs was not the consequence of structural changes of intercellular lipid layers in stratum corneum.
The lipid organization of stratum corneum was further investigated by ATR-FTIR. FTIR is a reliable technique to give an insight into the molecular organization of lipid matrix by offering bands at different wave numbers. Stratum corneum produces bands at different wave numbers corresponding to lipid and protein molecular vibrations. The peaks of major importance are the asymmetric and symmetric stretching vibrations of CH2 around 2,920 cm−1 and 2,850 cm−1, respectively, derived from the lipid hydrocarbon chains. Moreover, bands around 1,650 cm−1 and 1,550 cm−1 are attributed to the stretching vibrations of amide I (C=O stretching) and amide II bonds (C–N stretching and N–H bending) in stratum corneum proteins, respectively.37,55 The structural changes and fluidization of lipid bilayers in stratum corneum result in a shift of CH2 stretching vibrations to higher wave numbers.55 FTIR spectra of the untreated epidermis showed peaks at 2,927.4 cm−1, 2,857.9 cm−1, 1,639.2 cm−1, and 1,553.4 cm−1, which are assigned to asymmetric stretching vibration of CH2, symmetric stretching vibration of CH2, and stretching vibration of amide I and amide II bonds, respectively (Figure 7B). Furthermore, treatment of the epidermis with MTX-UDLs did not significantly change these vibrations and bands appeared at 2,927.4 cm−1, 2,858.5 cm−1, 1,639.2 cm−1, and 1,549.4 cm−1. Taken together, the results of DSC and FTIR suggest that the enhanced permeation of MTX-UDLs is attributed to elasticity and shape transformation ability without severe structural changes in skin.
Stability of MTX-UDLs
The stability of the optimized formulation, MTX-UDLs-T3, was evaluated on storage at 4°C and 25°C for 90 days. MTX-UDLs-T3 was chosen due to its superior skin permeation to all formulations. MTX-UDLs-T3 was evaluated for changes in the physicochemical properties during storage. Lipid vesicular formulations have a natural tendency to fuse, disintegrate, or aggregate during storage, which leads to changes in particle sizes, PDI, and zeta potential.49 These changes also bring about drug leakage from the vesicles and reduction in the entrapment efficiency.20
MTX-UDLs-T3 moderately maintained its physicochemical properties on storage at 4°C for 90 days, while there were marked changes at 25°C (Table 4). At 25°C, the substantial increase in particle size was observed from 87.7 to 158.6 nm along with a drastic increase in PDI representing heterogeneous particle size distribution. The decrease in zeta potential was also more prominent at 25°C than at 4°C. The particle size growth was accompanied by a decrease in entrapment efficiency of MTX-UDLs-T3 resulting from drug leakage in fusion, disintegration, and aggregation process. A statistically significant drug leakage from MTX-UDLs-T3 at 25°C was observed as 25.3% after 90 days, while only 7.1% of MTX was lost at 4°C. Higher temperature not only increases the kinetic energy and collision of the vesicles but also affects the gel-to-liquid transition of lipid bilayers, increasing the chance of lipid degradation and defective membrane packing.58 Based on the results, MTX-UDLs have better stability at low temperature compared with room temperature and need to be stored at 4°C in aqueous dispersion.
In this study, MTX-UDLs were prepared by varying the type and ratio of edge activators and were evaluated in terms of physicochemical properties, deformability, and skin permeation. The nanosized homogeneous MTX-UDLs were formed with spherical unilamellar structure. The deformability of MTX-UDLs increased as the amount of the edge activator (TW80 or SC) increased in their composition. Skin permeation and deformability of MTX-UDLs were significantly improved compared with those of MTX-CLs. As an edge activator, TW80 was more effective than SC with respect to deformability and skin permeation. The optimized UDLs with TW80 (PC:TW80 =7:3, w/w) were superior to other formulations in MTX delivery across skin. Consequently, MTX-UDLs could be potential nanosized carriers for low-dose MTX treatment of psoriasis and rheumatoid arthritis, while reducing the adverse effects of oral and parenteral administration. In vivo application of the optimized MTX-UDLs to a rheumatoid arthritis rat model is currently under investigation.
This research was supported by Basic Science Research Program through the National Research Foundation of Korea (NRF) funded by the Ministry of Science, ICT & Future Planning (NRF-2013R1A1A1010181).
The authors report no conflicts of interest in this work.
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