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Ginger Extract–Loaded Transethosomes for Effective Transdermal Permeation and Anti-Inflammation in Rat Model
Authors Hassan AS , Hofni A , Abourehab MAS , Abdel-Rahman IAM
Received 7 December 2022
Accepted for publication 21 February 2023
Published 15 March 2023 Volume 2023:18 Pages 1259—1280
Checked for plagiarism Yes
Review by Single anonymous peer review
Peer reviewer comments 2
Editor who approved publication: Dr Farooq A. Shiekh
Abeer S Hassan,1 Amal Hofni,2 Mohammed AS Abourehab,3 Iman AM Abdel-Rahman4
1Department of Pharmaceutics, Faculty of Pharmacy, South Valley University, Qena, Egypt; 2Department of Pharmacology and Toxicology, Faculty of Pharmacy, South Valley University, Qena, Egypt; 3Department of Pharmaceutics and Industrial Pharmacy, College of Pharmacy, Minia University, Minia, Egypt; 4Department of Pharmacognosy, Faculty of Pharmacy, South Valley University, Qena, Egypt
Correspondence: Abeer S Hassan, Department of Pharmaceutics, Faculty of Pharmacy, South Valley University, Qena, Egypt, Tel +201012060262, Email [email protected]
Introduction: Ginger extract (GE) has sparked great interest due to its numerous biological benefits. However, it suffers from limited skin permeability, which challenges its transdermal application. The target of the current work was to develop transethosomes as a potential nanovehicle to achieve enhanced transdermal delivery of GE through the skin.
Methods: GE–loaded transethosomes were prepared by cold injection using different edge activators. The fabricated nanovesicles were evaluated for particle size, ζ-potential, encapsulation efficiency, and in vitro drug release. The selected formulation was then laden into the hydrogel system and evaluated for ex vivo permeability and in vivo anti-inflammatory activity in a carrageenan-induced rat-paw edema model.
Results: The selected formulation comprised of sodium deoxycholate exhibited particle size of 188.3± 7.66 nm, ζ-potential of − 38.6± 0.08 mV, and encapsulation efficiency of 91.0%± 0.24%. The developed transethosomal hydrogel containing hydroxypropyl methylcellulose was homogeneous, pseudoplastic, and demonstrated sustained drug release. Furthermore, it exhibited improved flux (12.61± 0.45 μg.cm2/second), apparent skin permeability (2.43± 0.008× 10− 6 cm/second), and skin deposition compared to free GE hydrogel. In vivo testing and histopathological examination revealed that the GE transethosomal hydrogel exhibited significant inhibition of edema swelling compared to free GE hydrogel and ketoprofen gel. The animals that were treated with ginger transethosome hydrogel showed a significant decrement in reactive oxygen species and prostaglandin E2 compared to untreated animals.
Conclusion: Transethosomes might be a promising new vehicle for GE for effective skin permeation and anti-inflammation. To the best of our knowledge, this work is the first utilization of transethosomes laden into hydrogel as a novel transdermal delivery system of GE.
Keywords: nanovesicles, transethosomes, ginger, ex vivo permeation, transdermal delivery, inflammation
Several pathological disorders, such as rheumatoid arthritis and osteoarthritis, are triggered by inflammation. Active drug products that inhibit inflammation are potentially used to prevent the development of these disorders. Though different anti-inflammatory agents, either steroidal anti-inflammatory drugs (SAIDs) or non-SAIDs (NSAIDs), are utilized for inflammation management, they show several adverse effects. Using SAIDs may cause obesity and sodium retention, which result in serious health hazardous, including liver toxicity and gastrointestinal ulcers, the most common NSAID side effects.1 Clinical investigations have found local adverse effects in 6.3% of participants following local administration of NSAIDs, such as irritation at the application site and itching. Several studies have reported on new drug products that improve the anti-inflammatory performance of drugs and limit their undesirable effects. Natural plants are characterized by several bioactive phytochemicals possessing anti-inflammatory activity.2 Employing natural medicinal plants may have some advantages compared to conventional pharmaceuticals, such as a better safety profile and lower price. However, limited bioavailability, tissue permeability, and low levels of phenolic moieties in plant extracts are the major challenges of using these medicinal plant products.3 These shortcomings necessitate the production of reliable delivery nanovehicles to improve their permeability and boost therapeutic performance.
Transdermal delivery systems using nanocarriers can offer sufficient quantities of active ingredients for long periods and avoid their extensive liver metabolism.4 Moreover, transdermal delivery of nanocarriers can be used to enhance local dermal effects and permeation through the skin for systemic performance.5 Recently, vesicular nanocarriers have received great interest in applications of topical and transdermal drug delivery because of their similarity to cell-membrane structure. They consist of an aquatic core surrounded by a lipid bilayer, which allows them to encapsulate both hydrophilic and hydrophobic drug molecules.6 Further, these nanovesicles provide sustained drug release and deep penetration of the skin layers.7
Liposomes are among the most frequently investigated lipid nanovesicles. These nanovesicles are spherical and made of phospholipid bilayers surrounding aqueous cores.8,9 The limited physical and chemical stability of liposomes hinders their pharmaceutical application. New deformable nanovesicles have been designed, such as ethosomes, transferosomes, and transethosome (TREs), to enhance the stability of conventional liposomes. A new category of vesicular structures, composed of phospholipid, ethanol (20%–40%), and water, are termed “ethosomes.” Using ethosomes enables additional advantages, including improved skin permeation of the drug through the stratum corneum and subsequent retention in the skin layers.10 A novel type of nanovesicles, TREs have been studied in recent literature. They are elastic, stable, malleable, biodegradable lipid nanovesicles combining the advantages of both ethosomes and transferosomes. Structurally, they are phospholipid carriers composed of basic components of ethosomes (lipid, ethanol, 20%–40%) and edge activators, such as Tween 80, sodium deoxycholate, and oleic acid.9,11 TREs act via fluidizing and squeezing into tiny holes in the skin, resulting in improved skin penetration. The presence of ethanol and edge activators allows them to stretch and pass through the skin without marked loss, thus offering efficient penetration of the vesicles.11,12 Studies have reported that TREs exhibit efficient stabilizing effects and enhanced transdermal permeation of active natural products.5,13–15
One of the plants utilized traditionally for several inflammatory disorders is ginger (Zingiber officinale), which belongs to the family Zingiberaceae. It is widely used in medicinal purposes and dietary condiments due to its therapeutic and nutrition value.16 Most traditional and complementary systems of medicine, such as Ayurveda, recommend ginger to manage various disease conditions as a result of their anti-inflammatory and antinausea properties.17,18 In recent times, the rhizome, or root, of ginger has been widely studied for exhibiting antimicrobial, antitumor, antidiabetic, and antioxidant properties.19 Fresh ginger has two wide-range categories: volatiles and nonvolatiles. Volatiles include sesquiterpene and monoterpene hydrocarbons, which are responsible for the distinct aroma and taste of ginger. Nonvolatile pungent compounds include gingerols, shogaols, paradols, and zingerone.16,20
Ginger extract (GE) has been known to exhibit anti-inflammatory activity by suppressing the biosynthesis of inflammatory mediators, 5-lipoxygenase and cyclooxygenase inhibition, and inhibition of nitric oxide production. These therapeutic activities may be attributed to the presence of different bioactive materials.17,21 However, these bioactive materials have high molecular weight, limited solubility, poor bioavailability, and poor permeability across the skin that may affect the transdermal delivery of GE.4 GE has been explored for its transdermal delivery using different nanocarrier systems. Bioadhesive dermal patches of ginger were developed by Rahman et al and utilized as an antibacterial agent.22 They found that >80% of bacterial infections were inhibited after the application of ginger bioadhesive patches in an ex vivo Staphylococcus aureus infection model in rat skin. Priprem et al4 encapsulated GE into niosome vesicles, then incorporated these into a gel for topical delivery. They found that GE niosomal gel enabled an improved anti-inflammatory effect in a croton oil–induced ear-edema mouse model. Abdallah et al23 examined the anti-inflammatory activity of GE in carrageenan-induced paw edema in rats. They employed transdermal delivery of niosome vesicles laden into emulgel formulated with sesame oil, finding a remarkable effect of sesame oil on the improvement of anti-inflammatory performance of GE niosomes and revealing a synergistic effect of sesame oil with GE. In view of this, transdermal delivery of GE using prospective TRE vesicles can provide improved permeability of active ingredients in ginger that are responsible for anti-inflammatory activity.
The goal of the current study was to investigate the prospective effect of loading a novel nanocarrier, TRE vesicles with GE (GE-TREs), on enhanced skin permeability and performance in the management of inflammation. To the best of our knowledge, this is the first work to present the potential use of TRE hydrogel as a nanocarrier for GE transdermal delivery through the skin. GE-TREs were fabricated and characterized in terms of particle size, ζ-potential, encapsulation efficiency (EE), and in vitro drug release. After that, the best GE-TRE formulation was incorporated into a hydrogel system using three gelling agents. The prepared ginger transethosomal hydrogels were evaluated in terms of viscosity, in vitro drug release, and ex vivo permeability through the skin of rats. Finally, the in vivo performance of the selected formulation was examined, employing carrageenan-induced paw edema in rats, and compared with free GE hydrogel and ketoprofen hydrogel as a reference anti-inflammatory.
Materials and Methods
Fresh ginger rhizome was purchased from a local market in Qena, Egypt. Identification of the plant was done at the Pharmacognosy Department, Faculty of Pharmacy, South Valley University, Qena, Egypt. A specimen (code Zo.82) was kept in the herbarium of the Pharmacognosy Department. Carrageenan, sodium deoxycholate, Tween 80, and cellulose membrane (molecular weight 12,000–14,000 Da cutoff) were obtained from Sigma Chemicals (St Louis, MO, USA). Phosphatidylcholine phospholipon 90G was purchased from Lipoid (Steinhausen, Switzerland). Cholesterol was obtained from Kanto Chemical (Tokyo, Japan). Sodium alginate was obtained from General Chemical and Pharmaceutical, Sudbury, UK. Chitosan (CS; low molecular weight, viscosity 100 cp, 98% degree of deacetylation) was obtained from Industrial Manufacturing, Tokyo, Japan. Hydroxypropyl methylcellulose 15,000 was obtained from El Gomhouria, Cairo, Egypt. Ethanol, potassium dihydrogen phosphate, and disodium hydrogen phosphate were purchased from the United Company for Chemicals and Medical Preparations (Cairo, Egypt). All other chemicals and solvents were of analytical grade and used as received.
Adult male Sprague Dawley rats (weight 200–230 g, age 10–12 weeks) were utilized. The animals were obtained from the National Research Center, Giza, Egypt. During the experimental course, the animals were maintained under constant environmental conditions and subjected to cycling of dark and light of 14:10 h while food and water were available. They were left to adapt for 1 week, during which free access to standard commercial rat chow and tap water was offered. Blood samples were collected from the peripheral vein into sterile tubes at room temperature, and serum was collected and stored at −80°C until use. Prostaglandin E2 (PGE2) and TNFα concentrations were determined by ELISA.
Preparation of Ginger Extract
Fresh rhizome was washed with deionized water, sliced, dried in the sun for 1 week, and dried again at 50°C in an oven for 6 h. The dried rhizome was divided into small pieces, powdered by an electronic mill, sieved, and stored in a well-closed dark glass container until being used.24 The powdered plant material (300 g) was subjected to extraction by maceration in 1.5 L ethanol for 3 days with frequent stirring, followed by filtration. This process was repeated twice. The extract was then filtered using filter paper (Whatman 1) and evaporated utilizing a rotary evaporator under reduced pressure at 40°C. The solvent-free residue was stored at 4°C before use.25
Spectrophotometric Analysis of Ginger Extract
GE (10 mg) was dissolved in ethanol and diluted to concentrations of 5, 10, 15, 20, 25, 30, 35, 40, 45, 50, and 100 μg/mL. Then, the absorbance of these samples in the UV range of 200–600 was determined using a UV-vis spectrophotometer (Lisco, Bargteheide, Germany) using ethanol as a blank to measure the wavelength of maximum absorption (λmax) for GE. λmax was found to be 285 nm, then the calibration curve was obtained.
Preparation of Transethosomes Loaded with Ginger Extract
TRE nanovesicles were formulated utilizing cold injection using ethanol and distilled water at a ratio of 3:7 (v:v).13,26 In brief, a mixture composed of GE, phospholipon 90G, and cholesterol was added to an edge activator (Span 80, Tween 80, and sodium deoxycholate) and dissolved in ethanol at 30°C. Afterward, the aqueous phase (distilled water) was added dropwise to the organic phase and stirred continuously at 2000 rpm for 30 min with a magnetic stirrer. The resultant TRE suspensions were vortexed for approximately 5 min, then sonicated for an additional 2 min at 25°C. The fabricated TRE preparations were left overnight at 4°C for further characterization. The composition of different TRE formulations is summarized in Table 1.
Table 1 Composition of ginger extract (GE) transethosome (TRE) nanovesicles per 10 mL colloidal dispersion, and composition of GE transethosomal and nontransethosomal hydrogel formulations
In Vitro Characterization of Transethosomes Loaded with Ginger Extract
Particle Size and ζ-Potential
The particle size and polydispersity index (PDI) of the GE-loaded TREs were determined at 25°C via dynamic laser light scattering (DLS) utilizing a Malvern Zetasizer Nanoseries ZS (Malvern Instruments, Worcestershire, UK) equipped with a backscattered light detector operating at 173°. The ζ-potential of the fabricated TREs was measured via laser Doppler anemometry employing the Malvern Zetasizer. Determinations were conducted in triplicate.
Drug-Encapsulation Efficiency and Drug-Loading Percentage
EE was calculated indirectly via measuring free unentrapped content of GE employing UV-vis spectrophotometry. The unentrapped drug was obtained using cooling centrifugation (benchtop refrigerated centrifuge, Centurion Scientific, Sussex, UK) at 4°C and 15,000 rpm for 1 h to separate it.27 GE concentration in supernatant was estimated utilizing UV–vis spectrophotometry from a calibration curve of the hydroethanolic extract of ginger (wavelength at λmax of 285 nm for maximum absorption). EE and drug loading (DL) were determined via equations (1) and (2):28
Transmission Electron Microscopy
TEM (100 CX II; JEOL, Tokyo, Japan) was used for imaging of the TRE vesicles. Transethosomal dispersion (selected formulation) was diluted tenfold utilizing distilled water, then a drop was placed on a copper grid with a 300-mesh carbon coating and allowed to sit for a minute to allow some of the vesicles to stick to the carbon substrate. A piece of filter paper was used to remove extra dispersion, and the grid was then rinsed twice in deionized water for 3–5 seconds. The sample was then examined under a microscope utilizing 10–100× magnification and an accelerating voltage of 100 kV.
Fourier-Transform Infrared Spectroscopy Analysis
The FT-IR spectra of free GE, blank empty TREs, and GE TREs (GE-TREs) were detected employing a Nicolet 6700 FT-IR spectrometer (Thermo Fisher Scientific, Waltham, MA, USA). The examined preparations were blended with spectroscopic-grade potassium bromide (KBr), then crushed into disks using a hydraulic press (15,000 Ib). The scanning range for the samples was 4000–400 cm−1.
Stability of Transethosomes Loaded with Ginger Extract
GE TREs were kept in a sealed 20 mL glass vial and investigated for 1 month at 4°±1°C and 5°±1°C.29 Physical stability of the TRE dispersion was evaluated based on visual inspection of sedimentation and particle-size measurement. TREs were tested for EE after 30 days to assess the GE content.
Preparation and Characterization of Ginger-Extract Transethosomal and Nontransethosomal Hydrogel Formulations
Hydrogel formulations were fabricated using cold injection as per D’Souza et al30 with slight modification. Three gelling agents were investigated: NaAlg (4% w:v), hydroxypropyl methylcellulose (HPMC; 3% w:v), and CS (2% w:v). The contents of the gelling polymers were selected in accordance with preliminary experimental trials to produce hydrogel of acceptable appearance and uniformity. In brief, GE 0.3% w:v was mixed with an aqueous solution of each gelling agent to develop free GE hydrogels (nontransethosomal). To prepare GE transethosomal hydrogels, freshly prepared GE-loaded TRE suspension (selected formulation TRE3) equivalent to 0.3% w:w GE was mixed with an aqueous solution of each gelling agent (NaAlg 4% w:v, HPMC 3% w:v, and CS 2% w:v) and then the hydrogels were adjusted to ane ultimate weight of 10 g under constant stirring on a magnetic stirrer until homogeneous hydrogel formulations were achieved. Finally, the fabricated transethosomal and nontransethosomal GE hydrogels were left in the fridge until further investigations. The composition of the hydrogel preparations is detailed in Table 1. The clarity, homogeneity, and phase separation of the preparations were examined visually.31
Ginger-Extract Content and pH of Transethosomal and Nontransethosomal Hydrogel Formulations
The contents of GE in the TRE hydrogel preparations were determined via dissolving precisely weighed hydrogels (0.5 g) in ethyl alcohol to dissolve the vesicles and extract a quantity of drug. After the solution was filtered using filter paper, the drug content was determined using a UV-vis spectrophotometry at a maximum wavelength of 285 nm. The pH of GE hydrogel preparations was measured utilizing a 3500 pH meter (Jenway, UK).
Viscosity of Ginger-Extract Transethosomal and Nontransethosomal Hydrogel Formulations
The viscosity of GE hydrogel formulations was determined using a Brookfield digital viscometer (DV-II, Brookfield Engineering Laboratories, Stoughton, MA) at 25°C. The viscosity measurements were detected using spindle number 96 at a shear rate of 15 rpm. The measurements were carried out in triplicate.31
Rheological Behavior of Ginger-Extract Transethosomal and Nontransethosomal Hydrogel Formulations
Rheological analyses were carried out using the Brookfield digital viscometer. The viscosities of the hydrogel preparations were estimated at a range of shear rates (5–60 rpm) at room temperature using spindle number 96. The rheological property of the hydrogels was exhibited using the flow curve of the viscosity values versus shear rate.31
Spreadability of Ginger-Extract Transethosomal and Nontransethosomal Hydrogel Formulations
The spreadability of the fabricated hydrogel formulations was evaluated employing a previously reported method.32 Specific weight (2 g) of hydrogel was placed on a glass slide (7.5 cm in length). Another slide of the same length was kept on the top of the hydrogel such that the hydrogel was trapped between the two slides and expanded at a certain distance. A weight of 100 g was fixed on the upper slide for 10 min to evenly compress the gel to a constant thickness, preventing any further gel spreading. After that, the time needed for separation the slides was measured in seconds. Then, the spreadability was estimated:
where S corresponds to spreadability (g.cm/s), M is weight fixed on the upper slide (100 g), L is the length of the utilized glass slides (7.5 cm), and T is the time consumed in seconds for complete separation of the slides. The measurements were performed in triplicate.
In Vitro Release of Ginger Extract from Transethosomal and Nontransethosomal Hydrogel Formulations
In vitro release was carried out utilizing a dialysis membrane approach across a semipermeable cellophane membrane (molecular weight cutoff 12,000–14,000 Da, Sigma Aldrich, St Louis, MO, USA) as mentioned in a previous report with slight changes.6 Briefly, 1 g samples of different GE transethosomal and nontransethosomal hydrogel formulations were precisely weighed and kept over dialysis semipermeable membrane previously soaked in PBS (pH 7.4 for 24 h) and fitted over the lower-end opening of a glass tube of 2 cm diameter. These tubes were dipped in a 100 mL beaker containing PBS (pH 7.4). The system was kept at 37°±0.5°C in a thermostatically controlled shaking water bath (Daihan Scientific, Seoul, South Korea) rotating at 50 rpm. Samples of 5 mL were removed at predefined time intervals (0.5 1, 2, 4, 6, 8, 12, and 24 h). Removed sample volumes were replaced by the same volume of freshly developed release medium at the same temperature to maintain sink conditions. The released content of GE was estimated by using UV-vis spectrophotometry at a maximum wavelength of 285 nm. The in vitro release of GE from selected GE-TRE3 dispersion and free ginger solution was studied for comparison. The in vitro drug release procedures were repeated in triplicate.
The kinetics of drug release from the tested hydrogel formulations was studied using linear regression analysis. The in vitro release results were fitted in accordance with various kinetic models: zero order, first order, and Higuchi diffusion. A Korsmeyer–Peppas model was utilized to investigate the mechanism of drug release by plotting log cumulative percentage of drug released versus log time.33 The value of the exponent (n) evaluating the mechanism of drug release is calculated from the slope of the straight line produced. Where exponent (n) is ≤0.5, this corresponds to a Fickian diffusion mechanism, while 0.5<(n)<1.0 corresponds to a non-Fickian mechanism (anomalous diffusion). The non-Fickian diffusion indicates the combination of both diffusion and erosion-governed drug-release rate.
Ex Vivo Skin Permeability and Deposition
Skin permeability of selected GE-TRE hydrogel (HPMC-TRE3), free GE hydrogel (HPMC-GE) formulations, and GE hydroalcoholic solution was examined using abdominal skin of male rats according to a previously reported method.34 The experimental protocol was approved by members of the Research Ethics Committee and the head of Pharmacology and Toxicology Department, Faculty of Pharmacy, South Valley University, Egypt (PSVU 126/22). The animals were killed, then the dorsal side hairs of abdominal skin were removed with the aid of an electrical caliber. Then, the subcutaneous fat of the skin was washed three times with a cotton piece dipped in isopropyl alcohol. The skin was divided into appropriate-sized pieces and immersed in PBS (pH 7.4 for 4 h) to stabilize the skin membrane prior to the permeation experiment. Then, the skin was extended across the bottom open end of a glass tube of 2 cm diameter and immersed in a glass beaker containing 100 mL PBS and maintained in a vertical position such that the membrane was just below the surface of the solution. The donor (tubes) and receptor (beaker) were maintained at 37°±0.5°C in a thermostatically controlled shaking water bath rotating at 50 rpm. Tested preparations (0.5 g hydrogels, 0.5 mL drug solution) were placed on the skin (donor compartment). Aliquots of 5 mL were withdrawn from the receptor at predefined time intervals (up to 24 h) and replaced with freshly prepared release medium. The drug content was measured via employing UV-vis spectrophotometry at a maximum wavelength of 285 nm. Ex vivo permeation measurements were performed in triplicate. GE cumulative amount (µg) permeated through unit area was plotted on a curve versus time. The flux (J, µg.cm2/s) and permeability coefficient (Papp, cm/s) of GE through skin membrane were estimated utilizing Fick’s first law (Equations 4 and 5):
where dQ is change in drug amount (µg) across the skin and A (cm2) the area of skin surface.
where C0 is the drug concentration at zero time (µg/mL) in donor compartment.
Stability of Selected Ginger-Extract Transethosomal Hydrogel
The stability of the selected GE-TRE hydrogel formulation (F6) was carried out during the storage period. The tested formulation was stored in a sealed 20 mL glass vial in the refrigerator (at 4°±1°C) and at room temperature (25°±1°C) for 1 month. Then, the examined formulation was monitored for appearance, homogeneity, surface pH, spreadability, and viscosity. The stability study was conducted in triplicate.
In Vivo Animal Studies
Skin-irritation studies were conducted to prove that the GE and concentration of ingredients utilized for TRE development were safe and nonirritant to rat skin. The experimental procedures were carried out to assess any possible undesirable reaction of the GE formulation upon application on the skin surface of the rats in accordance with a technique described previously.35,36 The animals were divided into three groups (n=3): negative control (no treatment), 0.3% free GE hydrogel, and treated with selected transethosomal hydrogel (HPMC 3%-GE-TRE3). A dose of 1 g of GE hydrogel formulations was administered on a particular region of the shaved dorsal surface of the rats’ skin daily for 3 days.37 The skin was examined visually for the appearance of any sign of irritation or edema every day for 3 days. The examined skinwas compared with positive-control rat skin irritated with formalin solution (0.8% v:v) as standard irritant.35
Anti-Inflammatory Performance in Induced Paw-Edema Rat Model
The anti-inflammatory performance of the selected TRE hydrogel formulation was examined employing carrageenan-induced paw edema.38,39 The experimental animals were divided into four groups, each containing five rats. Group 1 rats were used as negative controls and intraperitoneally injected with 1 mL of vehicle (normal saline). Group 2 (carrageenan) rats were injected with 0.1 mL carrageenan in saline (1% w:v) into the left hind paw to induce edema. Group 3 (treated with selected formulation) rats received transethosomal HPMC hydrogel formulation (F6) containing 0.3% GE-loaded TREs prepared using sodium deoxycholate (GE-TRE3) prior to carrageenan injection in the same conditions as group 2. Group 4 (ketoprofen gel standard) rats were treated with ketoprofen (1%) gel as standard NSAID prior to carrageenan injection in the same conditions as group 2, with 0.5 g of the test formulation administered on edema paw tissue. The increment in paw thickness was determined using a Vernier caliper before the carrageenan injection, ie, at 0 h, and then at 1, 2, 3, 4, 5, 6, 7, and 8 h after carrageenan injection. The difference between paw thickness at 0 h and paw thickness at other times was used to calculate the increase in paw thickness. The detection of paw edema swelling and percentage inhibition of edema was carried out.
Measurement of TNFα levels was carried out utilizing an ELISA kit for rat TNF (Biosource Europe, Belgium). Absorbance was measured using a plate reader (Spectra lll, Austria) at wavelengths of 450 and 550 nm. TNFα level was then normalized to protein content after calculating the protein concentration.
Prostaglandin E2 Levels
PGE2 was estimated employing an enzyme immunoassay (EIA) kit (Enzo Life Sciences, Switzerland). On a 96-well plate, goat antimouse IgG was utilized as a precoat before medium and PGE2 EIA conjugate were added. The plate was subjected to a final wash to eliminate any last traces of the antibody-enzyme reagent, followed by 2 h of response time. The amount of PGE2 present was measured in pg/mL, and the color intensity was detected at 405 nm.
Oxidative Stress Parameters
Cold Krebs–HEPES buffer (10 mmol/L glucose, 0.02 mmol/L Ca-Tritriplex, 25 mmol/L NaHCO3, 1.2 mmol/L KH2PO4, 120 mmol/L NaCl, 1.6 mmol/L CaCl2, 1.2 mmol/L MgSO4 7H2O, and 5 mmol/L KCl, pH 7.4) was used to homogenize the paw tissues as previously mentioned.40 Reactive oxygen species (ROS) generation was estimated in the presence of lucigenin, (5 µmol/L). NADPH (100 mol/L) was added to initiate the reaction, and over the course of 30 minutes, relative light units (RLU) of the chemiluminescence were measured in a luminescent spectrometer (PerkinElmer). Results were adjusted to the protein content of each sample and presented as counts per minute.
Thin and thick serial paw-skin slices from paraffin blocks were acquired, processed, and ultimately stained with hematoxylin and eosin (H&E), then inspected under a light microscope (Optika Microsystems, Italy). Thin- and thick-skin specimens of each animal’s inflammatory reaction intensity were graded: 0 = no inflammatory cells, 1 = inflammatory cells 10%, 2 = inflammatory cells 10%–50% and 3 = inflammatory cells >50%.41 All histopathological changes were blindly carried out by a pathologist.
The experiments were carried at least thrice, and the findings are presented as means ± SD. For statistical analysis, GraphPad Prism 8.4.3 (GraphPad, San Diego, CA) was utilized. Analysis was performed using one-way ANOVA with Tukey’s test. Differences were considered statistically significant at P<0.05.
Results and Discussion
Preparation of Transethosomes Loaded with Ginger Extract
TREs are a type of nanoplatform that has the potential to greatly improve drug delivery to skin layers. GE was successfully loaded into TREs using a cold method to enhance the permeability and transdermal delivery of plant extract across the skin. Phospholipid was used for TRE development at concentration of 3% as bilayer-producing agent. Three types of edge activator were employed for the fabrication of GE-TREs at concentration of 0.3%. They were selected according to their values of hydrophilic lipophilic balance (HLB) to examine their effect on the physicochemical characteristics of the prepared nanovesicles. HLB values were 4.3, 15 and 18 for Span 80, Tween 80 and sodium deoxy cholate.42
In Vitro Characterization of Transethosomes Loaded with Ginger Extract
Particle Size, ζ-Potential, Encapsulation Efficiency, and Drug Loading
Average particle sizes, polydispersity index, ζ-potential, EE, and DL of GE-loaded TREs are listed in Table 2. The developed nanovesicles showed small particles and narrow polydispersity (PDI) of 254.8±30.84 nm, 0.45±0.02, 286.23±10.54 nm, 0.327±0.012, and 188.3±7.66 nm, 0.276±0.021 (Figure 1B) using Span 80, Tween 80, and sodium deoxycholate as edge activators, respectively. The presence of sodium deoxycholate significantly (P<0.05) reduced the particle size when compared with other edge activators. This might be due to the anionic nature of sodium deoxycholate producing steric repulsion in nearby charged molecules that caused increase in curvature and reduced the size of vesicles.43 The lower PDI values indicate the size uniformity and good homogeneity of the developed vesicles. A crucial aspect that might affect vesicular properties, ζ-potential values can be used to partially suggest the stability of GE TREs. The continuous agglomeration of nanovesicles are dramatically reduced, and the stability is increased, attributed to electrostatic repulsion.42 The ζ-potential measurements illustrated that GE-loaded TREs fabricated using Span 80, Tween 80, and sodium deoxycholate had a value of −7.8±0.125 mV, −21.1±0.265 mV, and −38.6±0.08 mV, respectively. As shown, GE-TREs prepared using deoxycholate exhibited significantly higher ζ-potential when compared with Span 80 and Tween 80, which proved the stability of the vesicles and minimum electrostatic attraction avoiding vesicle aggregation. The TREs had EE of 79.26%±0.60%, 84.81%±0.73%, and 91.0%±0.24% and DL of 7.67%±0.04%, 8.20%±0.04%, and 8.8±0.03% for GE-TREs prepared using Span 80, Tween 80, and sodium deoxycholate, respectively. The significantly higher EE of GE-loaded TREs consisting of sodium deoxycholate may be related to the highly solubilizing characteristics and incorporation into the lipid bilayer, which enhances medication entrapment into nanovesicles. These findings are in accordance with previous work that revealed that the higher encapsulation of meloxicam and dexamethasone was obtained by employing sodium cholate as edge activator in the preparation of lipid nanovesicles.43,44 Based on the previous experimental results, GE-loaded TREs prepared using sodium deoxycholate (TRE3) exhibited appropriate attributes in terms of higher EE, DL, smaller particles, and higher ζ-potential than TREs prepared using Span 80 and Tween 80. Therefore, GE-loaded TREs comprised of sodium deoxycholate (TRE3) were selected for further studies and characterization.
Table 2 Characterization of ginger extract (GE)-loaded transethosome (TRE) nanovesicles. Data presented as means ± SD (n=3)
Figure 1 (A) Transmission electron microscopy and (B) size distribution of GE-loaded transethosomes prepared using sodium deoxycholate. Magnification 72,000×, scale bar 100 nm.
Transmission Electron Microscopy
Particle size and morphology of the prepared nanovesicles were monitored by TEM. Figure 1A demonstrates the photomicrograph of GE-loaded TREs (TRE3) prepared using sodium deoxycholate as edge activator. The vesicles are spherical and nonaggregated with uniform and homogeneous distribution. It was noticed that the average size on TEM imaging was 28.83±7.19 nm for the fabricated TREs. This is smaller than that produced by DLS measurements (188.3±7.66 nm). This difference may be due to the dryness of the examined samples during TEM examination.45,46
Fourier-Transform Infrared Spectroscopy Analysis
The FT-IR spectra of GE, blank TREs and GE TREs (TRE3) prepared using sodium deoxycholate are presented in Figure 2. The FT-IR spectra of pure GE (Figure 2, trace A) present the characteristic peaks of phenol products: a broad beak was found at 3590 cm−1 due to hydrogen bond O–H stretching of hydroxyl groups. Bands at 2928 and 2857 cm−1 corresponded to CH2 stretching peaks, bands at 1374 cm−1, 1268 cm−1, 1100 cm−1, and 891 cm−1 corresponded to aromatic C–H stretching, –C–O–C stretching, and –C–O stretching of –C–O–H bonds. The characteristic peak of gingerol (main constituent of ginger) was observed at 1642, which represented C=O.47–49 The FT-IR spectra of the blank TREs (Figure 2, trace B) illustrated characteristic peaks of phosphatidylcholine at 2920 cm−1, 2854 cm−1 and 1736cm−1 corresponding to C–H stretches and carbonylic C=O stretch of ester, respectively. Also, the main characteristic peak of sodium deoxycholate in blank TREs (Figure 2, trace B) was shown at 3405.10 cm−1 due to the aliphatic O–H stretch. In the spectrum of GE-TRE3 (Figure 2, trace C) the broad peak (3590 cm−1) was shifted to lower wavelength. This may be due to the formation of a new hydrogen bond. In addition, it was noticed that the absorption peaks of GE at 1268, 1100 and 891 cm−1 disappeared. These results may indicate the development of nanovesicles with appropriate shape, size, and better stability, as reported in a previous study.50
Figure 2 FT-IR spectra of (A) pure ginger extract, (B) blank transethosomes, and (C) ginger-extract transethosomes prepared using sodium deoxycholate (TRE3).
Stability of the Selected Transethosomes Loaded with Ginger Extract
As shown in Table 3, GE TRE formulation prepared using sodium deoxycholate were found to be stable when stored at 4°C and 25°C±1°C for 1 month, they showed no sedimentation or aggregation. Moreover, the tested formulation exhibited a nonsignificant (Ρ>0.05) change in vesicle size and polydispersity when stored at 4°C and 25°C±1°C. In addition, GE-TRE formulation stored at these temperatures showed an improved chemical stability because of the GE content being maintained during storage. The results revealed that TREs protected GE from degradation and improved stability. Verma et al51 proved that encapsulating drug products into nanovesicles is a promising approach to improve their stability. This is due to the opportunity of these nanosystems to protect the drug products inside the core, preventing them from being exposed to the environment.
Table 3 Physical appearance, mean vesicle size, polydispersity index (PDI) and entrapment efficiency (EE) of GE-loaded TREs after 1-month storage at 4°C and 25°C. Data presented as means ± SD (n=3)
Preparation and Characterization of Ginger-Extract Transethosomal and Nontransethosomal Hydrogel Formulations
The visual detection of the developed GE gel formulations proved that the prepared hydrogels of free GE were clear and homogeneous. Also, GE-loaded TRE hydrogels presented slight opacity and good homogeneity and consistency without any lumps or air bubbles. The pH values of GE transethosomal and nontransethosomal hydrogels were in the range of 6.9–7.2 (Table 4), which might not produce irritation. Therefore, they were considered appropriate for skin application.
Table 4 Characterization of ginger extract transethosomal and nontransethosomal hydrogel formulations. Results presented as a means ± SD (n=3)
GE content in the fabricated hydrogel formulations ranged from 97.6%±0.93% to 99.4%±1.21% (Table 4). This proved the high homogeneity of the developed hydrogel formulations. Spreadability is considered a crucial parameter in patient enforcement and helps in homogeneous administration of hydrogel to the skin or inflamed area. An appropriate hydrogel that has elegant spreadability spreads easily via minimum shear. As illustrated in Table 4, The spreadability values ranged from 7.63±0.23 to 13.71±0.17 g.cm/s. The spreadability of GE-loaded TRE hydrogels exhibited significantly higher spreadability than hydrogel formulations containing free GE. Our findings in this work are in agreement with the results of a previous study.52
As shown in Table 4, the developed GE TRE hydrogels prepared using different edge activators exhibited significantly (P<0.05) higher viscosity values than the free GE hydrogels at constant shear rate 15 rpm. The increased viscosity of the transethosomal gel might be related to the effect of TRE lipid bilayer vesicles prepared using Span 80, Tween 80, and sodium deoxycholate compared with hydrogel contacting free GE. These results revealed that the incorporation of TRE vesicles into the hydrogel system might offer enhanced stability and transdermal drug delivery due to drug protection and retardation of vesicle fusion.9,53 Generally, higher values of viscosity and spreadability of transethosomal hydrogels improve transdermal delivery of GE across the skin.
Rheological properties of the prepared GE transethosomal and nontransethosomal hydrogel formulations (F1, F2, F3, F4, F5 and F6) were evaluated. The observations of viscosity for each hydrogel formulation at different shear rates are presented in Figure 3. It was observed that all the hydrogel formulations showed shear rate-thinning behavior with thixotropy (pseudoplastic fluid characteristics). Thixotropy means decreasing viscosity with an increase in shear rate and is a crucial characteristic for topical and transdermal application31. The pseudoplastic behavior possesses controlled drug release and appropriate application of the hydrogel on the affected skin area compared to Newtonian fluid.52 The prepared GE-loaded TRE hydrogel formulations have acceptable thixotropy and viscosity and offer a promising transdermal delivery system.
Figure 3 Rheological profiles of GE transethosomal and nontransethosomal hydrogel formulations at 25°C (n=3).
In Vitro Release of Ginger Extract from Transethosomal and Nontransethosomal Hydrogel Formulations
Cumulative GE released from different hydrogel preparations containing three investigated gelling agents (F1, F2, F3, F4, F5, and F6) was conducted in PBS (pH 7.4 at 37°C) utilizing dialysis membrane diffusion. The release profiles of GE from hydrogel formulations (F1, F2 and F3) compared with free GE hydroalcoholic solution are depicted in Figure 4A. Also, release profiles of GE from TRE hydrogel formulations (F4, F5 and F6) were compared with GE-loaded TRE suspension (Figure 4B). It was observed that free GE solution exhibited a significant higher amount of drug released (P<0.05) after 2 h (72.22%±0.28%) compared with GE hydrogels. This was probably due to the existence of gelling agents that performed as a resistant barrier to drug release because of their viscosity. It was reported that water migration into the gelling network and the diffusion of drug through the swelled matrix regulate and control drug release from hydrogel formulations.9 Similar conclusions were reported by Khurana et al,54 who found that meloxicam was released in a controlled pattern form hydrogel formulation compared to meloxicam solution. HPMC hydrogel formulation of GE demonstrated a significant higher drug release of 58.4% after 2 h when compared with CS hydrogel (47.5%) and NaAlg (26.1%) after the same time (Figure 4A). Then, HPMC hydrogel exhibited 92% of the drug that was released after 24 h. This result is related to the variations of the employed gelling agents’ structure and viscosity, as well as the difference in interaction between drug and gelling polymer. As observed in the viscosity results, the hydrogel with lower viscosity presented higher GE release as obtained from hydrogel containing HPMC (F3), while those with higher viscosity showed lower percentage of drug release. These observations are consistent with the results observed in previous reports.55,56 Regarding the hydrogel of GE-loaded TREs (Figure 4B), the highest release percentages at all time intervals were observed in HPMC (F6), followed by CS (F5) then sodium alginate (F4) hydrogel matrix. This was probably due to the highest viscosity of sodium alginate and possible attraction between negatively charged TREs and cationic CS hydrogel network, which consequently limit drug release.52
Figure 5 shows that the GE-loaded TRE dispersion displayed an initial burst drug release of 27% during the first 2 h, then a slow sustained drug release (87.4%) over 24 h. The release profile of GE from the TRE dispersion exhibited a significantly slower release pattern thane free GE incorporated in HPMC hydrogel (F3) (50% after 2h), probably as a result of the rigidity of the lipid bilayer membrane.7 Further, the cumulative amount of GE released from TREs incorporated into the HPMC hydrogel (F6) was found to be 20% within 2 h, then a sustained release rate of 80% drug was observed over 24 h. The slower release when compared with TREs dispersion and free drug hydrogel probably related to drug diffusion through the TRE lipid bilayer vesicles and followed throughout the matrix network of the aqueous hydrogel.57 The previous results proved that the TRE hydrogel system offered a sustained release pattern of GE when administered transdermally.
Figure 5 Cumulative in vitro release profiles of GE from TRES3 dispersion, HPMC hydrogel (F3), and HPMC-TRE3 hydrogel (F6) in phosphate buffer (pH 7.4 for 24 h at 37°C). Data presented as means ± SD (n=3).
To investigate the mechanisms regulating drug release from the different formulations, the results of the release study were analyzed using three kinetic models (zero-order, first-order, and Higuchi diffusion kinetic models) based on correlation coefficients (R2) and release-rate constants (K) for different mathematical models. The results revealed that GE release from all investigated formulation was best fitted to Higuchi diffusion because of the higher values of correlation coefficients (0.922±0.015, 0.873±0.014, 0.845±0.021, 0.904±0.038, 0.915±0.017, and 0.910±0.014 for F1, F2, F3, F4, F5 and F6, respectively) compared to those obtained from zero (0.823±0.011, 0.747±0.021, 0.722±0.034, 0.801±0.024, 0.807±0.028 and 0.785±0.014 for F1, F2, F3, F4, F5, and F6, respectively) and first-order kinetics (0.877±0.014, 0.809±0.012, 0.843±0.027, 0.835±0.021, 0.859±0.031, 0.843±0.013, and 0.840±0.020 for F1, F2, F3, F4, F5, and F6, respectively). In addition, the release data were fitted to the Korsmeyer–Peppas model and the value of (n) calculated. All the GE hydrogel preparations displayed (n) values of 0.5 < n < 1.0, (0.545±0.014, 0.727±0.009, 0.646±0.012, 0.503±0.054, 0.695±0.074, and 0.762±0.039 for F1, F2, F3, F4, F5, F5, and F6, respectively) that corresponded to anomalous (non-Fickian) diffusion, meaning that the release of drug from the prepared formulations may be controlled by diffusion mechanism from the hydrogel network and partitioning through the lipid bilayer of TRE vesicles.52 These findings are in accordance with previous research that found similar release profiles for TRE vesicles.52,56,58
Ex Vivo Skin-Permeability and -Deposition Studies
The study of permeability of GE across the skin from the optimum transethosomal HPMC hydrogel (F6) in comparison with free GE HPMC hydrogel (F3) and GE solution was carried out for 24 h at 37°C. The results of the permeability profiles are presented in Figure 6A. The observed results revealed that TRE hydrogel formulation (F6) exhibited a significantly (P<0.0001) higher amount of GE permeated (436.55±19.79 μg.cm2) after 24 h compared to 377.80±10.06 μg.cm2 and 179.28±14.16 obtained from nontransethosomal HMPC hydrogel (F3) and free GE solution, respectively. Moreover, transethosomal hydrogel displayed a significantly (P<0.0001) higher value of flux than those obtained from free drug hydrogel and free drug solution. The significantly highest (P<0.0001) mean apparent permeability coefficient (Papp) of GE was obtained with the TRE3 HPMC hydrogel formulation (F6) (2.43±0.008×10−6 cm/sec). The results showed that steady-state flux (Jss) from F6 was 3.35- and 2.1-fold higher than free drug solution and free drug hydrogel, respectively.
Higher GE skin deposition and permeation are probably due to the structure and nature of the nanosized TRE vesicles.59 They can squeeze themselves into the stratum corneum and tiny pores in the skin. The enhanced skin delivery of this nanoplatform may also be explained by the presence of ethanol and edge activator as permeation enhancer. Moreover, the phospholipid bilayer vesicles containing ethanol might have the potential to boost vesicle flexibility, enabling them to alter the structure of stratum corneum, penetrate the skin layer deeply and feasibly improve drug permeation.58,60 Additionally, the nanosized TREs offered a higher area for drug penetration through the skin, resulting in a high level of drug concentration at the site of application (inflamed area). These findings indicate the promise of these TRE nanovesicles to facilitate drug penetration to deep layers of rat skin compared to the free drug.11
Figure 6B displays higher skin deposition of 20.87% of HPMC-TRE3 (F6) hydrogel compared to 10.25% and 5.81% of free GE HPMC hydrogel (F3) and GE solution, respectively. This outcome may be because of the synergetic impact of ethanol and edge activator association. The higher deposition revealed that GE-TRE hydrogel accumulated for an extended period in the skin, acting as a reservoir and enabling a prolonged performance of GE at the adjacent tissue of the deep layers of the skin during intervals between administrations.59,61 Based on previous experimental results, it was concluded that the presence of an edge activator, ethanol, and phospholipid in the TRE nanosystem markedly improved GE permeation and skin deposition when compared to that of both drug solution and GE plain hydrogel.
Stability of Selected Ginger-Extract Transethosomal Hydrogel Formulation
The stability study for the selected TRE hydrogel formulation (F6) was conducted at 4°±1°C and 25°±1°C) for 1 month to investigate the storage stability of the formulation (Table 5). After 30 days, no significant changes were detected in surface pH, viscosity, drug content, homogeneity, or spreadability between the two storage temperatures. The selected TRE hydrogel formulation was found to be stable when stored at room temperature or in a refrigerator. This finding confirms the potentiality of the TRE nanovesicles to enable physical and chemical stability of GE hydrogel preparation.
Table 5 Physicochemical evaluation of ginger extract transethosome hydrogel (HPMC-TRE3 gel; F6) during the stability study (means ± SD, n=3)
In Vivo Animal Studies
The study of skin irritation was carried out to confirm the safety and compatibility of the GE hydrogel formulations when applied to the skin of rats without any visible irritation. The results revealed that GE transethosomal (F6) and nontransethosomal hydrogel (F3) formulations exhibited zero scores (null irritation) when compared with highly irritated skin that received formalin solution as standard irritant. This finding indicate that the prepared GE hydrogel formulations (F3 and F6) are nonirritant and safe on rat skin.
Anti-Inflammatory Performance in Induced Paw-Edema Rat Model
In this study, the anti-inflammatory effect of a novel GE transethosomal hydrogel was investigated against paw edema in adult rats induced by carrageenan compared to free GE hydrogel and reference ketoprofen gel (1%). The pharmacodynamic performance of GE hydrogel formulations in terms of anti-inflammatory efficacy on edema in hind paws of the rats is illustrated in Figure 7A and B, showing the edema swelling for up to 8 h and edema-inhibition percentages exhibited by the groups receiving free GE-HPMC (F3), GE-HPMC-TREs (F6) and marketed ketoprofen hydrogel formulations. Generally, a significant reduction in percentage of induced edema swelling was presented with the treated groups compared with the untreated group (Figure 7A). The group treated by hydrogel formulation F6 of GE TREs (TRE3, contains sodium deoxycholate) exhibited significantly (P<0.05) higher percentage of edema inhibition (Figure 7B) compared with free GE HPMC hydrogel (F3) and reference ketoprofen gel. After 2 h, F6 showed 66.11%±1.23% edema inhibition compared to 40.50%±1.72% from F3. After 5 h, F6 displayed significant (P<0.05) inhibition (86.34%±1.72%) of the induced edema compared to both F3 and ketoprofen gel 1%. The previous observations revealed superior anti-inflammatory activity of F6 compared to F3. This result matches the GE permeation study that demonstrated association between the higher percentages of GE transport across the skin and superior in vivo anti-inflammatory performance. These findings proved that transethosomal gel offered sustained and higher anti-inflammatory efficacy for a prolonged time when compared with free drug hydrogel. The prolonged anti-inflammatory effect exhibited by TRE hydrogel over free GE hydrogel is probably due to the nature of TRE nanovesicles, which act as a penetration enhancer. Also, they act as a nanosized drug vehicle that improves drug penetration, resulting in improved anti-inflammatory activity for prolonged time.
These findings are in accordance with those obtained by Salem et al, who investigated the anti-inflammatory effects of dapoxetine HCl transethosomal hydrogel transdermal delivery.52 Previous reports investigated the in vivo anti-inflammatory performance of pure GE extracts when administered orally or parenterally.62,63 Topical administration of GE was studied by Priprem et al,4 who found that ginger-loaded niosomal gel achieved enhanced skin permeation and anti-inflammatory activity against ear edema induced by croton oil in mice. In our investigation, a novel nanoplatform, TRE hydrogel, was successfully developed as a transdermal delivery system presenting sustained and improved anti-inflammatory effects of GE. It is known that upon carrageenan injection, levels of TNFα, PGE2, and reactive oxygen species (ROS) are elevated in inflammatory conditions. Therefore, the levels of these inflammatory mediators were estimated in the animal groups that were treated with GE-HPMC-TRE3 gel and commercial ketoprofen gel compared with untreated and normal control animal groups.
TNFα and Prostaglandin E2 Levels
TNFα is a cytokine that has a crucial role in both acute and chronic inflammatory disorders. In this study, it was found that the serum TNFα level was markedly increased in carrageenan-induced paw edema (untreated rat group) when compared to the normal control rats. The group that was treated with either GE-HPMC-TRE3 or ketoprofen commercial gel showed significantly (P<0.05) attenuated levels of TNFα (Figure 8A). The level of PGE2 was estimated for animal groups and the results are presented in Figure 8B. There was a significant increase in serum PGE2 in the untreated group (carrageenan-induced paw edema) compared to the normal control rats. However, the treatment of rats with either HPMC-TRE3 or ketoprofen gel significantly (P<0.05) inhibited these changes (Figure 8B). This may be attributed to the inhibitory effect of GE on the release of different inflammatory mediators during inflammation reaction. GE consists of a variety of flavonoid active constituents that exert anti-inflammatory effects by inhibition of cyclooxygenase, as reported previously. These findings revealed the improved anti-inflammatory efficacy of GE when loaded into a nanosized TRE hydrogel formulation.
Oxidative Stress Parameters
Elevation of ROS at the inflammation area is considered the main cause of tissue damage in many inflammatory disorders. The free radicals produced can stimulate inflammatory reactions, resulting in the increase of proinflammatory cytokines, which might lead to tissue damage. In this work, the paw edema induced via carrageenan in rats showed a marked increase (P<0.05) in ROS production compared to the control. Rats that were treated with either GE-HPMC-TRE3 or ketoprofen exhibited reduction in the levels of ROS (Figure 9A). Untreated rats, which received only carrageenan, exhibited a significant increase (P<0.05) in pancreatic MDA, while treatment with GE-HPMC-TRE3 hydrogel or ketoprofen gel inhibited this effect (Figure 9B).
Figure 10 I and II illustrate the histological examination of paw skin in the rat model of carrageenan-induced paw edema using H&E staining. (I) shows thin skin photomicrographs and (II) shows thick skin photomicrographs. IA and IIA represent normal control sections with normal histological structure in both thin and thick skin. IB and IIB represent sections obtained from positive control (carrageenan-induced edema without treatment) with detachment of epidermal layer (arrow), severe vacuolation and edematous reaction in thin and thick skin (star), and severe inflammatory reaction in the dermal tissue of thin skin (double-head arrow), as well as severe inflammatory reaction in dermal and muscular layers in thick skin (double-head arrow). IC and IIC sections obtained from animal pretreated with (GE-HPMC-TRE3 hydrogel) showed moderate dermal edematous and inflammatory reaction (star). ID and IID sections obtained from animal pretreated with (ketoprofen gel) showed mild dermal edematous and inflammatory reaction (star).
In the current study, for the first-time GE was loaded into a new nanosystem called TREs to improve transdermal permeation and anti-inflammation effect. They were successfully fabricated using cold injection method and thoroughly characterized in terms of different parameters. The selected GE transethosomal dispersion containing sodium deoxycholate demonstrated high EE, acceptable DL, nanosized particles, and sustained drug release. The optimum transethosomal formulation was incorporated into an HPMC hydrogel system. GE transethosomal hydrogel was found to be appropriate for skin application and showed improved skin permeability as well as superior anti-inflammatory activity in the induced rat-paw edema model. In summary, TRE nanovesicles can be considered a very promising advanced nanovehicle able to be applied in the transdermal delivery of GE for the treatment of inflammation conditions. Nevertheless, stability studies for long-term storage are required in future work to evaluate and achieve pharmaceutical acceptability.
GE, ginger extract; TREs, transethosomes; HPMC, hydroxypropyl methylcellulose; CS, chitosan; ROS, reactive oxygen species.
Experiments were conducted in accordance with the international ethical guidelines for animal care of the United States Naval Medical Research Centre, Unit 3, Abbaseya, Cairo, Egypt, accredited by the Association for Assessment and Accreditation of Laboratory Animal Care International. The procedures were in accordance with the Principles of Laboratory Animal Care (NIH publication 85-23, revised 1985). The study protocol was adopted by the Research Ethics Committee and the head of the Pharmacology and Toxicology Department, Faculty of Pharmacy, South Valley University, Egypt (PSVU 126/22).
Many thanks to Professor Adel Baker (Department of Histology, Faculty of Veterinary Medicine, Cairo University) for help with histopathological examination.
All authors made a significant contribution to the work reported, whether in conception, study design, execution, acquisition of data, analysis, and interpretation, or all these areas, took part in drafting, revising, or critically reviewing the article, gave final approval to the version to be published, have agreed on the journal to which the article has been submitted, and agree to be accountable for all aspects of the work.
The authors report no conflicts of interest in this work.
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