Tailoring of PEGylated bilosomes for promoting the transdermal delivery of olmesartan medoxomil: in-vitro characterization, ex-vivo permeation and in-vivo assessment

Abstract

Introduction

The intention of this work was to load olmesartan medoxomil (OLM), a sparsely water soluble antihypertensive bioactive with low oral bioavailability (26%), into PEGylated bilosomes (PBs) for augmenting its transdermal delivery. PBs contain PEGylated single chain edge activator besides the components of traditional bilosomes (Span 60, cholesterol and bile salts). The PEG gives further resilience to vesicle membrane and is speculated to augment both permeability and bioavailability of OLM.

Methods

A 2⁴ factorial experiment was constructed to inspect the impact of diverse variables on vesicles’ features and sort out the optimal formula adopting Design Expert^® software utilizing thin film hydration technique. Vesicles’ evaluation was done by finding out entrapment efficiency percent (EE%), particle size (PS), polydispersity index (PDI), zeta potential (ZP) and amount of drug released after 6 hrs (Q6h). The optimal formula was selected and characterized for further investigations.

Results

The optimal formula (PB15) showed spherical vesicles with EE% of 72.49±0.38%, PS of 559.30±10.70 nm, PDI of 0.57±0.15, ZP of −38.35±0.65 mV and Q6h of 59.60±0.24%. PB15 showed higher deformability index (28.39±5.71 g) compared to traditional bilosomes (5.88±0.90 g) and transethosomes (14.94±0.63 g). Further, PB15 showed superior skin permeation from rat’s skin relative to the drug suspension. Moreover, confocal laser scanning microscopy examination revealed efficient penetration of the fluoro-labeled PB15 through skin. Histopathological study ensured the safety of PB15. In addition, in-vivo skin deposition studies showed higher OLM deposition in rat’s skin from PB15 compared to transethosomes and OLM suspension. Furthermore, pharmacodynamic and pharmacokinetic studies performed using male Wistar rats and male Albino rabbits, respectively, showed the superiority of PB15 over oral tablets. PB15 was found to have significantly higher AUC_0–48 and AUC_0–∞ relative to the oral tablets. As well, the relative bioavailability of PB15 was found to be 235.04%.

Conclusion

Overall, the obtained results confirmed the creditable effect of PB15 for transdermal delivery.

Introduction

Hypertension seems to be a disorder that needs consideration for developing a transdermal drug delivery system (TDDS) because it requires long and continuing therapy.¹ For hypertension management, olmesartan medoxomil (OLM) is considered a promising antihypertensive drug classified as BCS class II with low bioavailability of 26% as a result of its inadequate solubility and first-pass effect after oral administration.² The first-pass metabolism of OLM and the considerations of hypertension disease could make transdermal delivery a recommended suggestion. TDDS could avoid hepatic first-pass effect and as a result the bioavailability is speculated to be boosted. Only small number of drugs exists as TDDS although the several merits of the skin as a drug delivery site which could be justified by the restriction of transdermal drug entry that is opposed by the stratum corneum (SC).³

Administering bioactive through a vesicular system is a successful mean for delivering drugs through transdermal route due to its deformable nature. Vesicles such as liposomes and niosomes are common carriers to encapsulate drugs. Unfortunately, they suffer from limited stability, encapsulation and scaling up problems which arouse the need for developing new vesicular systems.⁴ Bile salts (BS) enclosing vesicles or bilosomes have been produced as a modification for liposomes and niosomes which provide more stable vesicles by addition of BS to the lipid bilayers.⁵

Bilosomes have been fabricated for the orally administrated sparsely water soluble drugs and vaccines by the virtue of its high stability in opposition to pH, enzymes and BS existing in the gastro-intestinal tract.⁵ A recent study confirmed the tolerability of utilizing bilosomes in ocular drug delivery.⁶ Furthermore, bilosomes have been inspected for transdermal delivery. The studies proved the dominance of bilosomes over other vesicles as a TDDS as a result of the membrane destabilizing activity of the utilized BS.^3,7

In the present work, Brij^® was utilized as additional edge activator (EA) to prepare the PEGylated bilosomes (PBs). Brij^® consists of PEGylated single chain EA with various PEG chain lengths and acyl chain entities.⁸ The presence of the hydrophilic PEG moieties in EAs could increase the water uptake in SC which leads to SC swelling and it might also cause structural alterations in SC lipids and/or corneocytes which lead to broadening of the intercellular junctions in the barrier. Hence, the SC permeation is enhanced allowing sufficiently deformed PBs to pass the skin along with hydration gradient.⁹ Besides the improved transport of OLM loaded PBs across the skin, it might also be possible that PEG moieties facilitate their access to the lymph nodes. In this sense, it was reported that PEG improved the drainage of vesicles and enhanced their lymph node localization and subsequently resulted in augmentation of vesicles’ ability for circumvention of the first-pass effect.¹⁰ The work in this study was planned to assess the prospective of PBs to augment both transdermal permeability and bioavailability of OLM. To accomplish this aim, a 2⁴ full factorial experiment employing Design Expert^® software was used to obtain the optimal formula. Further, ex-vivo permeation studies using dorsal rat’s skin for the optimal formula in comparison with OLM suspension was performed to estimate OLM permeation from the vesicles. Confocal laser scanning microscopy was applied to track the intensity of penetration of the fluoro-labeled optimal PB through skin layers. To assess vesicles’ membrane elasticity and the role played by Brij^®, the deformability index of optimal PB was compared with transethosomes prepared in our previous work¹¹ and traditional bilosomes. Moreover, the safety of the prepared PBs was assured using histopathology. Furthermore, to determine the amount of OLM deposited in skin of male Wistar rats, the optimal PB was compared with transethosomes and OLM suspension. In addition, pharmacodynamic and pharmacokinetic studies for the optimal PB in comparison with the oral tablets were conducted in experimental animals.

Materials

OLM was obtained from FAP Pharmaceutical Co. (Cairo, Egypt). L-ɑ phosphotidylcholine (PC) from egg yolk, cholesterol, Span 60, sodium deoxycholate (SDC), sodium taurocholate (STC), cellulose membrane (12,000–14,000 molecular weight cutoff) and fluorescein diacetate (FDA) were obtained from Sigma Aldrich Chemical Co. (St. Louis, MO, USA). Brijo20 (polyoxyethylene (20) oleyl ether) and Brij52 (polyoxyethylene (2) cetyl ether) were provided by BASF Co. (New Jersy, NY, USA). Methylprednisolone acetate was obtained from Pfizer, Cairo, Egypt. Chloroform, methanol, ethanol 95%, acetonitrile, triethylamine, ethyl acetate and ammonium formate (each HPLC grade) were obtained from Merck (Darmstadt, Germany). Angiosartan^® 10 mg oral tablets were obtained from Chemipharm Co. (Cairo, Egypt) and expressed in the manuscript as the oral tablets.

Methods

Formulation of OLM PBs

PBs were assembled by applying thin film hydration method by altering both type and amount of BS and EA (Table 1). Firstly, OLM (25 mg), Span 60 (50 mg), cholesterol (25 mg), BS and EA were completely dissolved in 10 mL chloroform: methanol mixture (2:1) (v/v) in 250 mL round bottom flask and the organic phase was then removed by the aid of rotary-evaporator (Rotavapor, Heidolph VV 2000, Burladingen, Germany) in a 60°C water bath under vacuum.³ The film was hydrated with 10 mL ultra-pure water and stirred for 45 mins. To augment the yield of the obtained vesicles, glass spheres were utilized throughout the hydration stage. After that, the vesicles were sonicated using bath sonicator (Ultra Sonicator, Model LC 60/H Elma, Germany) for 10 mins for further particle size (PS) reduction. For comparative appraisal, OLM loaded traditional bilosomes and OLM loaded transethosomes were prepared by thin film hydration technique. For preparing traditional bilosomes, Span 60 (50 mg), cholesterol (25 mg) and STC (15 mg) were added in 10 mL chloroform: methanol mixture (2:1) (v/v) in 250 mL round bottom flask and the organic phase was then removed and the film was hydrated by 10 mL distilled water and then bilosomes were sonicated for 10 mins. In addition, transethosomes composed of SDC (15 mg) and phospholipid (85 mg) were developed also by thin film hydration technique and the film was hydrated using 10 mL distilled water containing 4% v/v ethanol and the preparation was continued as mentioned in our previous work.¹¹

Table 1.

The levels of independent variables and the model summary statistics of 2⁴ full factorial design used for optimization of OLM loaded PBs

Factors (independent variables)	Levels of variables
X1: BS type				SDC				STC
X2: EA type				Brijo20				Brij52
X3: BS amount (mg)				5				15
X4: EA amount (mg)				15				25
Responses (dependent variables)	R2	Adjusted R2	Predicted R2	Constraints	p-value	F value	Adequate precision	Significant factors
Y1: EE%	0.97	0.96	0.95	Maximize	<0.0001	101.00	33.92	x1, x2, x3, x4
Y2: PS (nm)	0.74	0.62	0.41	Minimize	0.0002	6.20	9.11	x1, x2, x3, x4
Y3: PDI	0.27	−0.06	−0.67	Minimize	0.62	0.81	3.45	-
Y4: ZP (mV)	0.75	0.64	0.43	Maximize (as absolute value)	0.0002	6.55	9.21	x1, x2, x4
Y5: Q6h (%)	0.99	0.98	0.97	Maximize	<0.0001	223.74	48.49	x1, x2, x3, x4

Abbreviations: BS, bile salt; EA, edge activator; EE%, entrapment efficiency percent; PBs, PEGylated bilosomes; PS, particle size; PDI, polydispersity index; SDC, sodium deoxycholate; STC, sodium taurocholate; ZP, zeta potential; Q6h, amount of drug released after 6 hrs.

In-vitro characterization and optimization of OLM PBs

Drug entrapment efficiency percent (EE%) analysis

The EE% of OLM from the produced formulae was determined by applying the direct method.¹² The dispersions were centrifuged at 20,000 rpm for 1 hr at 4°C using a cooling centrifuge and the sediment was lysed using methanol and analyzed using UV-Vis spectrophotometer. EE% was calculated using^:11

$$\mathrm{E}\mathrm{E}\mathrm{\%}=\left(\frac{\mathrm{E}\mathrm{D}}{\mathrm{T}\mathrm{D}}\right)\times 100$$ (1)

where EE% is the entrapment efficiency percentage, ED is the concentration of entrapped drug and TD is the total drug concentration. The experiments were performed three times and shown as mean±SD.

PS, polydispersity index (PDI) and zeta potential (ZP) analysis

Mean PS, PDI and ZP of the produced formulae were obtained through dynamic light scattering technique utilizing Zetasizer (Malvern Instruments Ltd., UK) after appropriate dilution of the samples.³ The ZP determination was evaluated by studying the electrophoretic mobility of the charged vesicles. All assessments were accomplished in triplicate±SD.

Determination of amount of drug released after 6 hrs (Q6h)

Two milliliters of PBs dispersions were added in plastic cylindrical tubes with a specific permeation area that have one end tightly enclosed with a cellulose membrane and the other connected to the shaft of the USP dissolution apparatus replacing baskets’ position for 6 hrs at 37°C.¹³ Formulations containing 5 mg of OLM were put in 50 mL PBS pH 7.4 and ethanol mixture (3:2, v/v) to keep sink situation. Aliquots were removed at 1, 2, 3, 4, 5 and 6 hrs. Samples were scanned by UV spectrophotometer at λ_max 257 nm. Experiments were assessed in triplicates and represented as mean±SD.

Experimental design construction

A 2⁴ factorial experiment was used to assess the impact of various factors in formulating PBs utilizing Design Expert^® software version 7 (Stat Ease, Inc., Minneapolis, MN, USA). The design required performing 16 runs. Four factors were studied: BS type (X₁), EA type (X₂), BS amount (X₃) and EA amount (X₄) that were the independent variables, whereas EE% (Y₁), PS (Y₂), PDI (Y₃), ZP (Y₄) and Q6h (Y₅) were chosen as dependent variables (Table 1).

Selection and validation of the optimal OLM loaded PB

The sorting out of optimal formula depended on the desirability function which permitted investigation of each and every response concurrently. The optimization step was decided to obtain a suggestion with the least PS and PDI and the highest EE%, ZP as absolute value and Q6h. Suggestion of highest desirability was chosen. For approving the model performance, optimal formula was prepared, characterized and correlated to the predicted responses through calculation of the bias percent by using the following equation:¹⁴

$$\mathrm{B}\mathrm{i}\mathrm{a}\mathrm{s}\mathrm{p}\mathrm{e}\mathrm{r}\mathrm{c}\mathrm{e}\mathrm{n}\mathrm{t}=\frac{\left|\mathrm{P}\mathrm{r}\mathrm{e}\mathrm{d}\mathrm{i}\mathrm{c}\mathrm{t}\mathrm{e}\mathrm{d}\mathrm{v}\mathrm{a}\mathrm{l}\mathrm{u}\mathrm{e}-\mathrm{o}\mathrm{b}\mathrm{s}\mathrm{e}\mathrm{r}\mathrm{v}\mathrm{e}\mathrm{d}\mathrm{v}\mathrm{a}\mathrm{l}\mathrm{u}\mathrm{e}\right|}{\mathrm{o}\mathrm{b}\mathrm{s}\mathrm{e}\mathrm{r}\mathrm{v}\mathrm{e}\mathrm{d}\mathrm{v}\mathrm{a}\mathrm{l}\mathrm{u}\mathrm{e}}\times 100$$ (2)

Transmission electron microscopy (TEM)

The optimal PB was morphologically identified by TEM (Joel JEM 1230, Tokyo, Japan). Stained vesicles’ dispersion was put on a carbon grid with copper coat and kept to dry to get a thin film. The sheet of copper was entered into the TEM.¹²

Differential scanning calorimetry (DSC)

Thermal investigation of 5 mg from each sample of OLM, cholesterol, Span 60, STC, Brij52, physical mixture of OLM with PBs constituents and the optimal PB was fulfilled by the assistance of DSC (DSC-60, Shimadzu Corp., Kyoto, Japan) in a temperature range of 10–250°C at a scanning rate of 5°C/min under inert nitrogen flow (25 mL/min) standardized with purified indium.³

Stability study

The optimal formula was retained at 4°C and 25°C for 90 days. Samples from each formulation were taken at 0, 45 and 90 days. Stability was estimated through evaluating the first measurements relative to the results observed following storing.¹⁵ The EE%, PS, PDI, ZP and Q6h of the PBs were determined as mentioned earlier. Statistical significance was analyzed by Student’s t-test using SPSS^® software 22.0 (SPSS, Chicago, IL, USA). The change at p≤0.05 was regarded as significant.

Assessment of vesicles’ elasticity

Extrusion method was utilized for comparing the bilayer elasticity of the optimal PB with traditional bilosomes and transethosomes adopting the method reported by Aziz et al³ and deformability index (DI) was calculated. Statistical analysis was evaluated by one-way ANOVA adopting SPSS^® software 22.0. Post-hoc test was conducted using Tukey’s HSD test.

Ex-vivo studies

Ex-vivo permeation studies

The permeation capability of OLM suspension and optimal PB via rat’s skin was evaluated. Removal of rat’s skin was done following sacrifice of animals. The setting of the study was the same as that in the in-vitro release but with putting the dorsal skin with the SC confronting the donor compartment instead of cellulose membrane. Aliquots were taken at 2, 4, 8, 10 and 12 hrs time intervals and analyzed using validated HPLC method.¹⁶ Permeation flux (J_max) at last time point and the enhancement ratio were estimated.³ Experiments were assessed in triplicates. Statistical significance was determined by Student’s t-test using SPSS^® software 22.0.

Ex-vivo tracking using confocal laser scanning microscopy study (CLSM)

To track the movement of optimal PB through deep skin tissues, the fluoro-labeled PB was formulated by thin film hydration technique. Firstly, FDA (100 mg), cholesterol (25 mg), Span 60 (50 mg), STC (15 mg) and Brij52 (15 mg) were added in 10 mL chloroform: methanol mixture (2:1) (v/v) in 250 mL round bottom flask and the organic phase was removed by the aid of rotary-evaporator in a 60°C water bath under vacuum. The film was then hydrated with 10 mL ultra-pure water and stirred for 45 mins and then sonicated for 10 mins. Dorsal rat’s skin was set with the SC confronting the donor compartment with the previously mentioned arrangement as the permeation study. FDA-packed PB was put on dorsal skin surface and remained for 6 hrs. For comparative evaluation, 1% FDA solution (control) was prepared, added on the rat’s skin and treated as mentioned for FDA-packed PB formulation. Longitudinal sections that were exposed to fluoro-labeled optimal PB and 1% FDA solution were stored in paraffin-wax and sliced using a microtome (Leica MicrosystemsSM2400, Cambridge, UK) and were examined for the existence of fluorescence in skin layers. The sample slides were inspected by invert microscope (LSM 710; Carl Zeiss, Oberkochen, Germany).¹¹

In-vivo studies

A total of 105 male Wistar rats were enrolled in the in-vivo studies, namely histopathological, skin deposition and pharmacodynamic studies. In addition, six male Albino rabbits were involved in the pharmacokinetic study. The study design was authorized by the ethical board of the Faculty of Pharmacy, Cairo University (PI 1867). The utilization and handling of animals in all studies obeyed the EU directive 2010/63/EU. The animals were kept in cages with wide mesh wire bottoms to avoid coprophagy at a temperature of 25°C and humidity of 55%. The animals were put in a dark:light cycle of 12 hrs each and were provided with standard diet and had free access to water. Animals were kept for 7 days for adaptation before experiments.¹¹ For in-vivo studies, lab-made containers containing drug suspension and optimal PB were used to serve as drug-pools. The containers were settled on the previously shaved dorsal animal skin. In addition, the application was performed non-occlusively into the drug-pools.^3,7,11 At the end of the previously stated studies, animals were sacrificed by decapitation method following anesthesia.

In-vivo histopathological study

A total of nine rats were classified into three groups of three rats for each group and treatment duration was 1 day. Group I acted as control and group II and group III were treated with drug suspension and optimal PB, respectively. Autopsy from skin samples was fixed in 10% formol saline for 24 hrs, followed by washing and dehydration using alcohol. Specimens were cleared in xylene and fixed in paraffin wax blocks and then sectioned at 4 mm by sledge microtome (Leica MicrosystemsSM2400, Cambridge, UK). The specimens were deparaffinized, stained and histopathologically examined using light microscopy (Axiostar plus, ZEISS, Oberkochen, Germany).¹¹

In-vivo skin deposition study

Seventy-two rats were classified into four groups of 18 rats each, where group I was control and animals in group II, group III and group IV were treated with drug suspension, transethosomes and optimal PB, respectively. A known volume (0.5 mL) of drug suspension, transethosomes and optimal PB was added non-occlusively to dorsal rat’s skin on a specific area that was shaved earlier. After various time intervals of treatment (1, 2, 4, 6, 8 and 10 hrs), three rats per group were killed and the dorsal rat’s skin was cut and analyzed.^3,7,11 AUC_0–10 values were calculated and compared between treatments. Statistical significance was studied using one-way ANOVA adopting SPSS^® software 22.0. Post-hoc test was conducted using Tukey’s HSD test.

In-vivo pharmacodynamic study

Pharmacodynamic study was done by employing a non-invasive blood pressure arrangement (NIBP 200 A; Biopac System, Inc., Goleta, CA, USA) depending on cuff tail method. Twenty-four male Wistar rats were distributed equally into four groups (1–4). Group 1 served as normal control. Hypertension was made in the other groups (2, 3 and 4) by administration of methylprednisolone acetate for 2 weeks subcutaneously. Group 2 acted as hypertensive control. Group 3 received oral tablets (10 mg OLM) (Angiosartan^® 10 mg oral tablets) that were mashed and administered by the aid of oral gavage syringe. Group 4 received topical treatment of optimal PB (10 mg OLM). The PBs dispersion was put to a shaved dorsal area of rat’s skin (4.91 cm²). The blood pressure (BP) from the tail was then taken at planned time points.¹ Statistical analysis was done by one-way ANOVA using SPSS^® software 22.0. Post-hoc test was performed using Tukey’s HSD test. Percent of decrease in BP from hypertensive control was determined.¹¹

In-vivo pharmacokinetic study

Animal study protocol

Six male Albino rabbits were used in the in-vivo pharmacokinetic assessment. Animals were classified into two groups with the same number. A randomized crossover design was done on two stages separated by 1 week as washout period. Hair on the dorsal part of the first group was shaved and the optimal PB (10 mg OLM) was put on a determined area of 10 cm×5 cm. Further, oral OLM tablets equivalent to 10 mg (Angiosartan^® 10 mg oral tablets) were orally given to the second group by utilizing oral gavage. Following the washout period, reverse randomization occurred. Blood samples (2 mL) were withdrawn by retro-orbital plexus puncture in heparin-coated eppendorf tubes after 0, 1, 2, 3, 4, 6, 8, 10, 12, 24 and 48 hrs of administration. Centrifugation of plasma was done at 5000 rpm for 15 mins and put at −20°C until analyzed.

Pharmacokinetic assessment

Olmesartan; the active-form of OLM was determined in the samples of plasma employing a sensitive, precise and selective liquid chromatography mass spectrometry (LC/MS/MS). The concentration of olmesartan was plotted against time and analyzed by Kinetica^® 5 software (Thermo Fisher scientific Inc., Waltham, MA, USA) using non-compartmental models. The C_max and T_max were determined. In addition, AUC_0–48 and AUC_0–∞ were calculated. C_max, AUC_0–48 and AUC_0–∞ were compared between the treatments employing ANOVA test using SPSS^® software version 22. The nonparametric Signed Rank Test (Mann–Whitney’s U test) was used to compare the medians of T_max for the treatments. The relative bioavailability of optimal PB was calculated and compared to the oral tablets employing the following equation:

$$\mathrm{R}\mathrm{e}\mathrm{l}\mathrm{a}\mathrm{t}\mathrm{i}\mathrm{v}\mathrm{e}\mathrm{b}\mathrm{i}\mathrm{o}\mathrm{a}\mathrm{v}\mathrm{a}\mathrm{i}\mathrm{l}\mathrm{a}\mathrm{b}\mathrm{i}\mathrm{l}\mathrm{i}\mathrm{t}\mathrm{y}=\left(\frac{\mathrm{A}\mathrm{U}\mathrm{C}\mathrm{P}\mathrm{B}\mathrm{s}}{\mathrm{A}\mathrm{U}\mathrm{C}\mathrm{o}\mathrm{r}\mathrm{a}\mathrm{l}\mathrm{t}\mathrm{a}\mathrm{b}\mathrm{l}\mathrm{e}\mathrm{t}\mathrm{s}}\right)\times 100$$ (3)

Results and discussion

Analysis of factorial design

Quality by design is an impressive statistical means where it confirms the efficacy of the procedure in term of mathematical relationships. Desirability function is an effective tool for defining the optimal levels of the variables. The model chosen was two-factor interaction. Adequate precision is used to affirm that the model might be used to navigate the design space.¹⁷ A ratio superior than four is preferred which was noticed for all dependent variables (except PDI) as illustrated in Table 1. The predicted R² values were in a good harmony with the adjusted R² in all dependent variables (Table 1). The negative predicted R² value of PDI proves that the overall mean is a better interpreter of the response.¹⁸

Effect of variables on the EE%

The capability of PBs to enclose a considerable quantity of OLM is important for its potential application as a TDDS. Both cholesterol and Span 60 in PBs bilayers offered high drug entrapment; cholesterol presence provided rigidity to the bilayers¹⁹ while Span 60 with high transition temperature (Tc) offered a better adequacy to maintain a more organized gel structure and well-defined vesicles.²⁰ EE% ranged from 40.19±0.12 to 81.21±0.44% (Table 2). ANOVA results proved that BS type (X₁), EA type (X₂), BS amount (X₃) and EA amount (X₄) significantly affected EE% (p<0.0001), which is graphically presented in 3-D surface plots (Figure 1A–C).

Table 2.

A) Experimental runs, independent variables and measured responses of the 2⁴ full factorial experimental design of OLM PBs and B) the observed, predicted values and bias percent of the optimum PB15

A) Formulations	X1	X2	X3	X4	Y1 (%)	Y2 (nm)	Y3	Y4 (mV)	Y5 (%)
PB1	SDC	Brijo20	5	15	56.65±0.83	496.65±51.45	0.69±0.11	−32.90±1.60	91.98±0.45
PB2	SDC	Brijo20	5	25	53.14±0.45	420.90±16.30	0.46±0.04	−30.57±0.25	87.36±4.11
PB3	SDC	Brijo20	15	15	45.86±0.85	438.00±49.00	0.48±0.18	−33.60±0.40	91.93±1.44
PB4	SDC	Brijo20	15	25	40.19±0.12	387.35±48.45	0.52±0.08	−27.40±0.20	97.56±0.66
PB5	SDC	Brij52	5	15	72.65±0.43	562.10±7.90	0.37±0.07	−28.10±0.50	60.62±0.51
PB6	SDC	Brij52	5	25	59.73±0.24	543.15±23.15	0.61±0.11	−31.75±0.65	66.03±1.59
PB7	SDC	Brij52	15	15	47.87±0.13	545.30±5.30	0.52±0.03	−29.25±0.65	68.72±3.75
PB8	SDC	Brij52	15	25	43.82±0.18	440.80±69.20	0.63±0.04	−31.60±0.40	71.90±1.03
PB9	STC	Brijo20	5	15	76.90±0.38	616.15±37.75	0.55±0.15	−29.70±0.45	51.90±1.89
PB10	STC	Brijo20	5	25	70.82±0.16	464.65±23.25	0.50±0.12	−26.15±0.45	55.66±1.11
PB11	STC	Brijo20	15	15	68.00±1.38	561.40±1.20	0.49±0.09	−30.35±0.45	58.97±1.87
PB12	STC	Brijo20	15	25	60.68±0.30	440.30±24.30	0.60±0.03	−30.55±1.80	66.41±1.84
PB13	STC	Brij52	5	15	81.21±0.44	804.20±41.30	0.61±0.11	−44.50±0.25	47.18±1.62
PB14	STC	Brij52	5	25	78.11±0.20	646.75±24.25	0.63±0.04	−35.65±0.35	51.76±7.56
PB15	STC	Brij52	15	15	72.49±0.38	559.30±10.70	0.57±0.15	−38.35±0.65	59.60±0.24
PB16	STC	Brij52	15	25	69.47±0.12	492.30±54.30	0.50±0.14	−33.35±0.85	63.79±1.66
B)
Observed values of PB15					72.49	559.30	0.57	−38.35	59.60
Predicted values of PB15					72.33	606.26	0.56	−38.65	58.33
Bias %					0.22	8.39	1.75	0.78	2.17

Note: Data represented as mean±SD (n=3).

Abbreviations: X₁, BS type; X₂, EA type; X₃, BS amount; X₄, EA amount; Y₁ (EE%), entrapment efficiency percent (%); Y₂ (PS), particle size (nm); Y₃ (PDI), polydispersity index; Y₄ (ZP), zeta potential (mV); Y₅ (Q6h), amount of drug released after 6 hrs (%); PBs, PEGylated bilosome.

Figure 1.

Response 3-D plots for the effect of BS type (X₁), EA type (X₂), BS amount (X₃) and EA amount (X₄) on EE%, PS and PDI of OLM loaded PBs.

Abbreviations: BS, bile salt; EA, edge activator; EE%, entrapment efficiency percent; PS, particle size; PDI, polydispersity index; OLM, olmesartan medoxomil; PBs, PEGylated bilosomes.

Taking into consideration BS type (X₁), relatively high drug entrapment was obtained in formulae consisting of STC compared to SDC formulae. It is worthy to mention that the hydrophobicity of STC is higher than SDC⁵ which could justify that the higher EE% values observed in PBs containing STC might be related to a widely preferable hydrophobic area for the lipophilic OLM in vesicles’ bilayers.²¹ Regarding EA type (X₂), EE% values were found to be higher in formulae containing Brij52 compared to Brijo20 which might be linked to the HLB values of both Brij52 (HLB=5.3) and Brijo20 (HLB=15.3).^8,22 As previously declared, the lower HLB value of EA resulted in elevated drug EE%.²³ Furthermore, Brij^® consists of acyl chain with different lengths with a saturated or unsaturated carbon chain and PEG repeating units. Brijo20 contains acyl chain of C₁₈, unsaturated double-bond and 20 PEG repeating units while Brij52 contains acyl chain of C₁₆ and two PEG repeating units. Tagami et al⁸ reported that Brijo20, with an unsaturated acyl chain, did not result in formulations with good drug entrapment compared to Brij52 which contains no double-bond in its structure. Existence of the unsaturated double-bond in the chain of carbon might cause it to twist which leads to the vesicle bilayer being leakier as the packing of the molecules might not be firm.²⁴ In addition, the lipid-phase transition temperature (Tc) of the EA could be critical factor in demonstrating EA effect on EE%. The Tc of Brij52 and Brijo20 are 36–38°C and 25–30°C, respectively.⁸ It was recorded that the higher the Tc of the EA, the better its capability to make a defined structure and a more ordered bilayer that might result in higher EE% values.²⁴

ANOVA results revealed that by raising BS amount (X₃) from 5 to 15 mg, a significant negative impact on EE% occurred. Hofmann and Mysels²⁵ illustrated that BS form helical mixed micelles in the vesicles’ bilayers. This explains that at a higher BS amount (15 mg), the solubility of OLM in the aqueous phase increased due to potential presence of mixed micelles which compromised the EE% of OLM. Regarding the impact of EA amount (X₄) on EE%, it was noted that increasing the EA amount from 15 to 25 mg resulted in a consequent reduction of EE%. This might be related to the formation of pores in vesicle bilayers, when the EA amount increased which decreased EE% values.²⁶

Effect of variables on PS

PS of the vesicles has a leading impact on their in-vivo metabolism. Decreasing the PS could significantly abolish their detection by the complements in the blood and increase their circulation time which enhances the therapeutic efficiency of entrapped drugs.²⁷ The PS of PBs was in the range of 387.40±48.45 to 804.20±41.30 nm as illustrated in Table 2. The impact of BS type (X₁), EA type (X₂), BS amount (X₃) and EA amount (X₄), on the PS of PBs is graphically represented in 3-D surface plots (Figure 1D–F).

BS type (X₁) showed a significant impact on PS (p=0.0009). Smaller PS was obtained for vesicles prepared with SDC compared to those containing STC. The difference in PS might be related to the difference in the structure of the used BS.⁶ Aburahma⁵ illustrated the difference in molecular weight for both SDC (414.6 gm/mol) and STC (537.68 gm/mol). Therefore, the bulkier STC might have produced larger PS of STC-PBs in comparison with SDC-PBs. Furthermore, increase in the molecular weight leads to increased viscosity of the nanodispersion and might result in aggregations and augmentation of the PS.²⁸ Moreover, the obtained results asserted that EA type (X₂) showed a significant effect on the PS of the vesicles (p=0.0007). The PS of the formulae containing Brij52 was higher compared to Brijo20 formulae. This could be associated with that the EA of higher HLB value (Brijo20) resulted in augmentation of the surface energy and thus decreased the PS. In addition, as previously mentioned, Brijo20 and Brij52 contain 20 and 2 PEG units, respectively. It is reported that the increase in PEG content might slow down the rate of vesicles’ precipitation and hence hinders vesicles’ agglomeration.²⁹

BS amount (X₃) showed a significant influence on the PS of PBs (p=0.0021). Raising BS amount from 5 to 15 mg decreased PS because of the reduction in surface tension of the vesicles.⁵ Another speculated theory is that BS at higher amount tend to form mixed micelles which are lesser than the original size of vesicles.³⁰ ANOVA results confirmed that increasing the EA amount (X₄) significantly decreased the PS (p=0.0010). The possible reason might be due to that EA at smaller amount (15 mg) was not satisfactory enough to effectively cover the lipids and reduce the surface tension. Hence, the PS of vesicles was higher and larger vesicles were formed. Moreover, the decrease in PS could be explained by the augmentation of the curvature of PBs at greater EA amount.¹⁵

Effect of variables on PDI

Concerning PDI, zero value demonstrates monodisperse dispersion. On the contrary, a value of 1 indicates polydisperse dispersion.⁷ All inspected factors; BS type (X₁), EA type (X₂), BS amount (X₃) and EA amount (X₄) revealed no significant effect with p-values of 0.37, 0.36, 0.80 and 0.33, respectively, which is graphically represented in 3-D surface plots (Figure 1G–I). PDI of the measured formulae ranged from 0.37±0.07 to 0.69±0.11 as illustrated in Table 2. This showed that the prepared PBs were polydisperse but with appropriate values.³¹

Effect of variables on ZP

ZP is frequently employed to assess the nanoparticle’s charge which represents a good indicator about the stability of nanoparticles.³² ZP ranged from −26.15±0.45 to −44.50±0.25 mV (Table 2). All factors were significant except BS amount (X₃) (p=0.5009). The influence of BS type (X₁), EA type (X₂), BS amount (X₃) and EA amount (X₄) on the ZP of PBs is graphically depicted in 3-D surface plots (Figure 2A–C).

Figure 2.

Response 3-D plots for the effect of BS type (X₁), EA type (X₂), BS amount (X₃) and EA amount (X₄) on ZP and Q6h of OLM loaded PBs.

Abbreviations: BS, bile salt; EA, edge activator; ZP, zeta potential; Q6h, amount of drug released after 6 hrs; OLM, olmesartan medoxomil; PBs, PEGylated bilosomes.

It was observed that by changing BS type (X₁), ZP significantly changed (p=0.0054). STC increased ZP of vesicles compared to SDC. This difference might be due to extra OH group in STC which contains three OH groups, compared to SDC that contains two OH groups.^5,33 Further, taurine BS are more acidic than unconjugated BS³ due to the presence of highly charged taurine amino-acid which increases the negative value of ZP.³⁴ Moreover, higher molecular weight BS like STC usually have thick and malleable interfacial layers and are more reluctant to stress relative to lower molecular weight BS as SDC that are predispose to coalescence when they are present in close contact.³⁵ It is worth mentioning that vesicles produced by using STC were significantly larger than those produced using SDC which might also be related to the greater ZP-values of the PBs containing STC. Vesicles of greater ZP-values revealed high repulsion energy among the charged vesicular bilayers with subsequent increased spaces between them resulting in production of bigger vesicles.³

Regarding EA type (X₂), results displayed that it had a significant impact on ZP (p=0.0004). Higher ZP-values were obtained upon incorporation of Brij52 in vesicles in comparison to Brijo20. It was recorded that the EA with higher Tc (Brij52), as mentioned earlier, might be important in preparing more ordered stable vesicles.²⁴ On the contrary, Brijo20 with 20 PEG repeated units had lower ZP. This could be related to the higher amount of hydrophilic PEG steric shield that slightly screened the surface charge of carboxyl groups at the surface of the vesicles and led to lower ZP-values.³⁶ Additionally, increasing EA amount (X₄) significantly decreased the ZP (p=0.0205). This could be because of the tendency of the investigated EAs to reside on the surface of the vesicular bilayers related to their hydrophilic character which might have resulted in obscuring the negative charge of the PBs.³³

Effect of variables on Q6h

Amount of OLM released after 6 hrs ranged from 47.18±1.62 to 97.56±0.66% (Table 2). ANOVA results showed that BS type (X₁), EA type (X₂), BS amount (X₃) and EA amount (X₄) had a significant impact on Q6h (p<0.0001), which is graphically depicted in 3-D surface plots in Figure 2D–F. In addition, Figure 3A–B illustrates the release profiles of OLM from the prepared PBs at different time intervals.

Figure 3.

The release profiles of OLM from the prepared 16 PB formulations compared to OLM suspension (A) release profiles of OLM and PB1:PB8 and (B) release profiles of OLM and PB9:PB16. Data represented as mean±SD (n=3).

Abbreviations: OLM, olmesartan medoxomil; PB, PEGylated bilosome.

Regarding BS type (X₁), it was found that PBs containing SDC produced a significantly greater amount of OLM released relative to STC containing PBs. As previously mentioned, the hydrophobicity is higher in case of STC compared to SDC while critical micelle concentration correlates inversely with hydrophobicity. The large number of methylene groups in the side chain of the BS during conjugation with taurine results in decreased critical micelle concentration values which could attribute for the decrease of OLM release from STC containing PBs.³⁷ For EA type (X₂), PBs containing Brij52 showed significantly lower amount of OLM released than the corresponding formulae containing Brijo20. Based on PEG content and HLB values, Brijo20 was found to be more hydrophilic than Brij52, as previously stated. As the hydrophilicity increases, the membrane microviscosity decreases and the rate of flip-flop and membrane penetration increase.³⁸ In addition, it was reported that by increasing the bulk of hydrophilic portions of the EA (PEG), the flippase activity increases which could attribute to the augmentation of the amount of OLM released.³⁹

Increase in BS amount (X₃) resulted in increasing the amount of OLM released which could be related to that the incorporation of BS through the bilayer resulted in discharge of the lipophilic drug integrated. Further, BS might associate with the vesicles’ bilayers and convert them into mixed micelles which results in boosting the solubility of OLM and augmenting OLM release.⁵ Moreover, increasing EA amount (X₄) from 15 to 25 mg resulted in an increase in the amount of OLM released. Lower OLM release at smaller EA amount might be explained because of the existence of the lipid membranes in firm and less leaky form which hinders drug release from PBs, while increasing EA amount to 25 mg resulted in pore formation in PBs bilayers which augmented OLM release.⁴⁰

Selection and validation of the optimal PB

The optimal formula from experimental design was PB15 which met the criteria determined before. High correlation was noticed among the observed and predicted values of PB15 (Table 2). In addition, the average bias percent values for all the obtained responses were smaller than 10% revealing the high model’s predictability capacity.¹⁴ Subsequently, PB15 was chosen as the optimal formula for extra studies.

Transmission electron microscopy (TEM)

TEM configuration as observed in Figure 4 confirmed that vesicles were spherical with narrow size distribution and no vesicles with irregular shape were visible. The PS of the vesicles determined by Zetasizer was in a perfect harmony with that observed using TEM. In addition, TEM images demonstrated that the vesicles had a smooth surface with the presence of PEG (lighter colored peripheries) around the vesicles.⁴¹

Figure 4.

Morphology of the selected vesicle (PB15).

Abbreviation: PB, PEGylated bilosome.

Differential scanning calorimetry (DSC)

Figure 5 illustrates the thermograms of OLM, cholesterol, Span 60, STC, Brij52, physical mixture of OLM along with PBs constituents and PB15. The DSC of OLM demonstrated a melting endothermic peak at 183.86°C.² Thermogram of cholesterol showed a sharp melting endotherm at 146.81°C.³ Span 60 revealed a narrow melting endotherm at 55.01°C revealing its crystalline state which is attributed to its melting point.³ Furthermore, Brij52 demonstrated a Tc of 36–38°C.⁸ The DSC thermogram of STC showed a very wide endotherm that included the 50–120°C temperature range followed by exothermic crystallization peak at 238.30°C.^3,42 The DSC of the physical mixture of OLM with PBs constituents disclosed that the OLM particular peak was existent supporting its presence in crystalline state. For PB15, the distinctive peak of OLM completely vanished which might be related to that OLM was entrapped inside the vesicles.⁴³ These findings might also suggest a major interaction between the drug and the constituents of the bilayer structure which might be the reason for the high EE% of OLM. These interactions could account for the good vesicle shape, structure and excellent stability.⁴⁴

Figure 5.

DSC thermograms of (A) OLM, (B) cholesterol, (C) Span 60, (D) Brij52, (E) STC, (F) physical mixture of PB15 components and (G) PB15.

Abbreviations: STC, sodium taurocholate; OLM, olmesartan medoxomil; PB, PEGylated bilosome.

Stability study

After 45 and 90 days in both 4°C and 25°C, stored vesicles showed no recognized aggregation or transformation in their shape. No significant change in EE%, PS, PDI, ZP and Q6h of the stored vesicles relative to the freshly prepared PBs was observed as shown in Table 3. Basically, charged vesicles are more stable against aggregation than un-charged vesicles. The prepared PBs were negatively charged because of STC that increased the ZP and prohibited the coalescence of the vesicles. Moreover, it was reported that Span 60 containing formulae were generally very stable and drug leakage from vesicles prepared using Span 60 was small and this might be related to its high Tc and its capability to form more ordered bilayers.²⁰ In addition, the high stability of the PBs was related to the presence of the PEG in Brij52 structure which stabilized vesicle membrane by steric hindrance.³⁶

Table 3.

Effect of storage on the physical properties of PB15

Parameter	PB15 fresh	PB15 after 45 days at 4°C	PB15 after 45 days at 25°C	PB15 after 90 days at 4°C	PB15 after 90 days at 25°C
EE%	72.49±0.38	72.04±0.95	70.52±3.91	68.33±3.44	67.93±5.75
PS (nm)	559.30±10.70	563.15±4.60	560.30±9.20	561.86±6.40	562.75±7.90
PDI	0.42±0.15	0.47±0.05	0.48±0.08	0.44±0.15	0.45±0.05
ZP (mV)	−38.35±0.65	−38.10±9.82	−36.35±8.52	−35.90±9.17	−34.40±6.89
Q6h (%)	59.60±0.34	61.60±1.00	63.36±1.88	62.48±3.93	63.12±3.02

Note: Data presented as mean±SD (n=3).

Abbreviations: EE%, entrapment efficiency percent; PS, particle size; PDI, polydispersity index; ZP, zeta potential; Q6h, amount of drug released after 6 hrs; PB, PEGylated bilosome.

Elasticity measurement

BS are able of destabilizing vesicles’ bilayers and hence increase their deformable properties. The deformability index values of PB15, traditional bilosomes and transethosomes were 28.39±5.71 g, 5.88±0.90 g and 14.94±0.63 g, respectively. The significant (p<0.05) dominance of PB15 over traditional bilosomes and transethosomes could be attributed to the presence of extra PEGylated EA in PBs bilayers. In addition, the higher DI of transethosomes compared to traditional bilosomes could be justified by the presence of both BS and ethanol rather than BS alone in traditional bilosomes.¹¹ The previous results verified the advantage of PB15 over traditional bilosomes and transethosomes in squeezing through skin with superior elasticity while preserving PS.

Ex-vivo studies

Ex-vivo permeation studies

Numerous animal models have been recommended as an alternative for human skin and have been utilized to measure percutaneous permeation of drugs. These included porcine, primates, mouse, rat, snake and guinea pig models.^11,45 Rat’s skin was recognized to mimic human SC in thickness, composition and transport resistance and it consists of SC, epidermis and dermis.⁴⁶ From Figure 6, it could be declared that the amount of OLM permeated from PB15 was significantly greater than that permeated from OLM suspension. The ER exceeded six folds for PB15 relative to drug suspension as presented in Table 4. The significant lower permeability of OLM suspension compared to PB15 might be due to the properties of OLM. It is suggested that the log partition coefficient value of 5.6 could be the reason of the low permeation of OLM.² A parabolic relationship between the skin permeation ability and lipophilic character of several drugs has been formerly recorded with the highest permeability at log P of about three to four.⁴⁷ For highly deformable vesicles as PBs, the condition is dissimilar as they could permeate intact through the SC and hence the permeability of the vesicle basically controls the movement of the drug.⁴⁸

Figure 6.

Cumulative amount of OLM permeated per unit area from PB15 relative to OLM suspension. Data represented as mean±SD (n=3).

Abbreviations: OLM, olmesartan medoxomil; PB, PEGylated bilosome.

Table 4.

Skin permeability parameters of OLM after topical application of OLM suspension and PB15

Skin permeability parameters	OLM suspension	PB15
Total amount of OLM permeated per unit area after 12 h (μg/cm2)	123.78±14.02	811.31±146.67
Jmax (μg/cm2/h)	10.31±1.16	67.61±12.22
ER	1	6.56

Note: Data presented as mean±SD (n=3).

Abbreviations: J_max, permeation flux; ER, enhancement ratio; PB, PEGylated bilosome.

Ex-vivo tracking using CLSM

CLSM investigation was done to evaluate the capability of penetration and fluorescence intensity following transdermal delivery of fluoro-labeled PB15. Images obtained with CLSM (Figure 7A–B) depicted that the dye loaded PB15 exhibited accumulation of fluorescence in different skin tissues. Images were captured from longitudinal section (perpendicular to the skin surface) which provided details about the allocation in the SC and skin tissues. The vesicles demonstrated symmetric distribution on the skin surface and maximum penetration of fluoro-labeled PB15 relative to control solution which might be related to the elasticity provided by the EAs present in fluoro-labeled PB15. High intensity of fluoro-labeled PB15 was noticed near the hair-follicles. This observation agrees with the former investigations supporting that the hair-follicles serve as a depot for the transdermally applied carriers from which the liberation of the entrapped drug might happen. It is worthy to mention that the hair-follicles are surrounded by blood capillaries and thus the substances penetrating through the hair-follicles could reach the tissues surrounding the follicle and get to the blood circulation.¹⁴

Figure 7.

A tile scan confocal laser microscope photomicrographs of longitudinal section in rat’s skin treated with (A) FDA control solution (B) fluoro-labeled PB15. (I) fluorescence light, (II) transmitted light and (III) merge between fluorescence light and transmitted light.

Abbreviations: FDA, fluorescein diacetate; E, epidermis; D, dermis; HF, hair follicles; PB, PEGylated bilosome.

In-vivo studies

In-vivo histopathological study

Histopathological scanning (Figure 8) of group II (OLM suspension) and group III (PB15) displayed no alterations in the histopathology of different skin layers compared to untreated skin sections of group I (control). The treated skin samples showed perfect normal skin features. These findings asserted that the prepared PBs had good safety toward skin.

Figure 8.

Photomicrographs showing histopathological sections (hematoxylin and eosin stained) of normal untreated rat’s skin (group I), rat’s skin treated with OLM suspension (group II) and rat’s skin treated with PB15 (group III) with magnification power of 16x and 40x, respectively.

Abbreviations: E, epidermis; D, dermis; HF, hair follicles; OLM, olmesartan medoxomil; PB, PEGylated bilosome.

In-vivo skin deposition

In-vivo skin deposition results of OLM from transethosomes and PB15 relative to OLM suspension are depicted in Figure 9. Statistical evaluation displayed that there was a significant difference (p<0.05) among the AUC_0-10 of OLM suspension, transethosomes and PB15 topically treated groups. The AUC_0-10 calculated for OLM loaded PBs (1115.64±110.70 μgh/cm²) and for OLM loaded transethosomes (680.46±17.99 μgh/cm²) were about 5.68 and 3.47 folds higher than that of OLM suspension (196.30±99.66 μgh/cm²), respectively. Further, multiple comparison demonstrated the superiority of PB15 over transethosomes and OLM suspension. The significantly higher skin deposition capacity of OLM from PB15 was related to the capability of PBs as highly deformable vesicles, based on elasticity results, to partition themselves via SC layers enclosing the entrapped OLM to deeper tissues. It is worth stating that adequate material transfer across the skin is not only a result of the modified skin features but rather counts on the movement of the intact and highly deformed vesicles through the SC.⁴⁸ In addition, SC is constructed of proteins and fats. BS are known to solubilize membrane proteins and phospholipids effectively which could result in enhanced vesicles’ penetration.³ Moreover, the results declared that the amount of OLM deposited decreased by increasing time. This could be attributed to that the cellular uptake of skin became saturated and hence the amount of OLM transferred into the blood from the skin exceeded the quantity of drug penetrating the skin with resultant reduction of the skin deposition.⁴⁹

Figure 9.

In-vivo skin deposition profiles of OLM versus time from PB15, transethosomes and OLM suspension after topical application. Data represented as mean±SD (n=3).

Abbreviations: OLM, olmesartan medoxomil; PB, PEGylated bilosome.

In-vivo pharmacodynamic study

The antihypertensive effect of transdermally applied PB15 was studied by measuring the lowering effect of BP upon applying the optimal formula to the skin of hypertensive rats. Both oral tablets and PB15 treated groups showed similar antihypertensive activity and there was no significant difference between both groups and normal control group at (1, 2, 4 and 6 hrs) after treatment. However, the BP of oral tablets treated group was maintained at normal levels up to 6 hrs only posttreatment and oral tablets were unable to revert BP to normal level at 8, 24 and 26 hrs posttreatment (Table 5). On the contrary, transdermally applied PB15 reduced the BP to normal values with the highest percent reduction of 35.00±5.00% at 24 hrs time point and BP was maintained at normal range for up to 26 hrs. Although the BP values of PB15 treated group at 28 and 48 hrs were not at normal values likewise oral tablets but there was a significant difference (p<0.05) between PB15 treated group and oral tablets treated group with superior percent reduction in BP values of 20.00±6.00% and 13.00±4.00% compared to 1.00±0.00% and 3.00±1.00% for PB15 and oral tablets treated group at 28 and 48 hrs, respectively (Table 5). Furthermore, post-hoc test showed that there was no significant change (p>0.05) between the normal control group and PB15 treated group while there was a significant difference (p<0.05) between oral tablets treated group and normal control group at 8, 24 and 26 hrs posttreatment. The obtained results could be related to the presence of PEG moieties in PBs which could inhibit effectively the in-vivo clearance of OLM by mononuclear phagocyte.⁵⁰ These results asserted that the PBs were efficient in maintaining the rat’s BP for prolonged period compared to oral tablets.

Table 5.

Influence of oral tablets and PB15 on mean BP in methylprednisolone acetate-induced hypertensive rats

Time (hours)	Normal control (mmHg)	Hypertensive control (mmHg)	Oral tablets (mmHg)	PB15 (mmHg)	Percent reduction in BP of oral tablets	Percent reduction in BP of PB15
0	109.50±3.50	171.00±4.00	177.00±3.26	169.00±11.70	4.00±2.00%	6.00±4.00%
1	126.20±1.20	187.50±2.50	138.00±0.81	121.50±10.10	26.00±0.00%	34.00±2.00%
2	129.00±1.00	166.50±6.50	127.20±1.83	120.00±2.50	24.00±1.00%	28.00±2.00%
4	126.70±2.70	168.00±8.00	128.90±0.83	115.70±11.30	23.00±1.00%	31.00±7.00%
6	117.70±4.20	166.00±4.00	126.50±6.94	124.70±4.40	24.00±4.00%	25.00±3.00%
8	114.70±1.70	169.50±2.50	140.10±6.40	123.20±13.30	17.00±4.00%	27.00±8.00%
24	117.70±0.70	185.50±5.50	165.00±8.16	123.30±4.02	11.00±4.00%	35.00±5.00%
26	117.00±1.00	186.50±8.50	166.80±11.27	127.30±3.20	6.00±2.00%	24.00±2.00%
28	111.00±3.00	170.00±8.00	169.00±0.81	135.60±10.00	1.00±0.00%	20.00±6.00%
48	128.50±1.50	175.50±2.50	173.60±5.73	152.60±7.70	3.00±1.00%	13.00±4.00%

Note: Data presented as mean±SD (n=6).

Abbreviations: BP, Blood pressure; PB, PEGylated bilosome.

In-vivo pharmacokinetic study

OLM is ester prodrug of olmesartan.² Subsequently in assessing the transdermal bioavailability of OLM from PB15, it is speculated to be converted in blood circulation to olmesartan due to the presence of esterase enzymes.⁵¹ Hence, olmesartan was used as indicator for determination of the in-vivo pharmacokinetic behavior of OLM. The mean concentration time plots in male Albino rabbits after 48 hrs posttreatment are shown in Figure 10 and the main pharmacokinetic parameters are tabulated in Table 6. There was a significant difference (p<0.05) between PB15 and oral tablets in AUC_0–48 and AUC_0–∞ while there was no significant difference between PB15 and oral tablets in C_max and T_max with p-values of 0.96 and 0.10, respectively. The AUC_0–48 and AUC_0–∞ values of PB15 treated group were about 2.35 times higher than those of oral tablets treated group. In addition, the T_max value of PB15 was numerically but not significantly higher compared to oral tablets. The high relative bioavailability of PB15 (235.04%) confirmed what was hypothesized at the beginning of the work and clearly defined the superiority of PB15 over oral tablets which could be associated with bypassing the liver first-pass metabolism in case of transdermal PB15 which consequently enhanced OLM bioavailability. Moreover, based on PB15 composition, the presence of PEG might have provided higher stability levels in the bloodstream preventing interactions with plasma opsonins which could have led to longer circulation time in the blood and thus prolonged the systemic efficacy. In addition, PEG moieties might have facilitated the access of PBs to the lymph nodes and subsequently resulted in augmentation of vesicles’ ability for bypassing the first-pass effect, as previously mentioned.¹⁰ Concisely, the findings verified that PB15 could act as effective transdermal delivery approach for OLM by avoiding its oral problems.

Figure 10.

Pharmacokinetic profiles of olmesartan versus time from oral tablets and topically applied PB15. Data represented as mean±SD (n=6).

Abbreviation: PB, PEGylated bilosome.

Table 6.

Pharmacokinetic parameters of olmesartan after administration of oral tablets and PB15

Pharmacokinetic parameters	Oral tablets	PB15
Cmax (ng/mL)a	270.08±79.51	296.52±177.47
Tmax (h)b	1	7
AUC0→48 (ngh/mL)a	1542.43±713.33	3625.61±948.02
AUC0→∞ (ngh/mL)a	1583.41±676.84	3721.67±878.73
Relative bioavailability (%)	-	235.04

Notes: ^aData represented as mean±SD (n=6); ^bData represented as median (n=6).

Abbreviations: AUC, area under the curve; PB, PEGylated bilosome.

Conclusion

In the present study, PBs were developed for transdermal delivery of OLM. A complete 2⁴ full factorial experiment assisted in formulating the optimal formula (PB15) that showed spherical shape, high drug EE% and small PS. In addition, ex-vivo studies showed superior permeation from PB15 over OLM suspension. CLSM verified that the PBs could penetrate the deep skin layers. In addition, histopathological study confirmed the tolerability of PB15. In-vivo skin deposition study confirmed higher retention tendency of OLM in rat’s skin from PB15 compared to transethosomes and drug suspension. Further, PB15 showed a controlled effect on hypertensive rats that lasted for prolonged time. Pharmacokinetic study proved the capability of PB15 to augment the bioavailability of OLM compared to oral tablets. In the consequence, the findings proved that PB15 could be a potential TDDS for OLM by abolishing its extensive first-pass metabolism and its oral problems.

Disclosure

The authors affirm that they do not have conflicts of interest to disclose in this work.