Preparation and Evaluation of Lipid-Based Liquid Crystalline Formulation of Fenofibrate
Moloud Kazemi, Jaleh Varshosaz, Majid Tabbakhian
Department of Pharmaceutics, Novel Drug Delivery Systems Research Center, Faculty of Pharmacy, Isfahan University of Medical Sciences, Isfahan, Iran
|Date of Web Publication||21-Sep-2018|
Dr. Jaleh Varshosaz
Department of Pharmaceutics, Novel Drug Delivery Systems Research Centre, Faculty of Pharmacy, Isfahan University of Medical Sciences, Po Box 81745-359, Isfahan
Source of Support: None, Conflict of Interest: None
Background: Many drugs have poor water solubility and so the oral delivery of such drugs is usually associated with limitation of low bioavailability and lack of dose proportionality. Lipid-based liquid crystal (LC) systems are excellent potential formulations for increasing dissolution and bioavailability of drugs. The aim of the present study was to formulate lipid-based LC containing fenofibrate (FFB) as a hydrophobic drug. Materials and Methods: The studied variables included lipid and stabilizer concentrations and the type of stabilizer. The LC formation was identified by the polarized optical microscopic method. The effects of variables on formulation characteristics such as particle size, drug release, and rheological behavior were evaluated. Results: The results showed that the prepared formulations had the particle size between 42 and 503 nm. The drug release profiles showed that FFB had the continuous release from the formulations and the highest dissolution efficiency was seen in formulation prepared by 1.5% of glyceryl monostearate and 0.5% of Pluronic F127 as the stabilizer. The change of stabilizer type from colloidal silica to Pluronic F127 increased the drug release, significantly. Conclusions: In the most formulations of FFB LCs, the DE% was more than the pure drug, and therefore, it seems that the liquid crystalline formulations can be effective for enhancing drug release. Furthermore, drug release rate depended on the stabilizer type so that the presence of colloidal silica caused slower drug release compared to Pluronic F127.
Keywords: Bioavailability, enhanced solubility, fenofibrate, liquid crystal
|How to cite this article:|
Kazemi M, Varshosaz J, Tabbakhian M. Preparation and Evaluation of Lipid-Based Liquid Crystalline Formulation of Fenofibrate. Adv Biomed Res 2018;7:126
|How to cite this URL:|
Kazemi M, Varshosaz J, Tabbakhian M. Preparation and Evaluation of Lipid-Based Liquid Crystalline Formulation of Fenofibrate. Adv Biomed Res [serial online] 2018 [cited 2019 Dec 6];7:126. Available from: http://www.advbiores.net/text.asp?2018/7/1/126/241834
| Introduction|| |
Designing novel formulations to enhance the oral bioavailability of poorly water-soluble drugs has long been a key driver of the pharmaceutical industries. The poor intrinsic solubility of Biopharmaceutical Classification Scheme (BCS) class II compounds has stifled the development of many emerging therapeutic compounds. Considering that 75% of drug development candidates display poor aqueous solubility, their limited bioavailability is still an unmet challenge for pharmaceutical drug development. The absorption of these poorly water-soluble drugs is limited by their poor solubility and resultant slow dissolution rate in gastrointestinal fluids. In addition, these drugs can commonly display variable bioavailability affected by foods, with poor solubility being a strong predictor of positive food effects. Ingested lipids interact with bile salts and phospholipids in the postprandial intestinal milieu to solubilize poorly water-soluble drugs. Although lipids can enhance absorption of these drugs, they may also lead to variable bioavailability during clinical use depending on the prandial state at the time of dose administration, potentially resulting in loss of efficacy.
Fenofibrate (FFB), a prodrug of fenofibric acid, has been used to treat hypertriglyceridemia because it reduces low-density lipoprotein (LDL) and very-LDL while increasing the level of high-density lipoprotein., It belongs to BCS II which means that it is lipophilic (logP = 5.575) and practically insoluble in water, and its oral bioavailability is approximately 30% in humans., Orally administered agents possessing the aqueous solubility of 0.1 mg/ml usually demonstrate poor absorption due to impaired dissolution. Several techniques have been devised to amend solubility of drugs in the aqueous surroundings, thereby promoting their bioavailability. A number of solubilization methods have been engaged to significantly improve aqueous solubility and plasma titers of hydrophobic drugs. These approaches mostly involve particle-size diminution, incorporation of surface tension reducing substances, salt formation, pH modification, complexion, micronization, and development of solid dispersions., The Lipantil Micro is the capsule formulation of the micronized FFB which, displays food-dependent bioavailability, and therefore requires administration with food. A reformulated product, Lipantil Supra was developed using NanoCrystal technology, to overcome this limitation and allows food-independent administration and dose reduction.,, Furthermore, lipid-based formulations like self-emulsifying drug delivery systems can be more appropriate when the active substance is lipophilic. Lipid-based formulations have been widely investigated for their ability in enhancing solubilization within the gastrointestinal tract (GIT), generating supersaturation, and increasing drug absorption and have been shown to eliminate food effect in vivo. Solubilization of poorly water-soluble drugs within a lipid-based, liquid carrier allows delivery within a capsule which self-emulsifies on dispersion in GI fluids, maintaining drug solubilization. Coadministration of lipids as formulation excipients may promote the formation of mixed micelles enhancing solubilization and induce secretion of bile salts and phospholipids in vivo, mimicking the fed state environment.,,,,
Liquid crystals (LCs) are semisolids with crystalline structures combining the properties of both solid and liquid states. Commonly encountered phases in LCs include the lamellar, bicontinuous cubic, and inverse hexagonal phases. LCs are easily formed by various amphipathic lipids such as glyceryl monooleate (GMO) and phytantriol in excess amounts of water. Many studies reported that the oral administration of LCs enhanced the bioavailability of poorly water-soluble drugs. In the pharmaceutical arena, viscous lipid-based systems, such as bicontinuous cubic and hexagonal liquid crystalline phases offer considerable scope for application as drug delivery systems. They have the potential for control over release rates, low toxicity, and versatility in application across a range of administration regimes, including oral, transdermal, and parenteral delivery. Lipid-based liquid crystalline systems are also mucoadhesive. An important attribute of a limited number of lipid-based liquid crystalline systems is that they are thermodynamically stable in excess water, thereby providing a persistent matrix on exposure to liquids such as GI and interstitial fluids. This property also allows for the predispersion of liquid crystalline systems in aqueous vehicles in the form of submicron particles suitable for intravenous drug delivery.
Materials known to exhibit such phase behaviour include phospholipids, alkyl glycerides such as GMO, amphiphiles with phytanyl chains such as phytantriol  and glycolipids, and alkyl glycerates. The ability of drug delivery systems based on lipids such as GMO which enhances the bioavailability of FFB as a poorly water-soluble drug after oral administration, is well known, and is thought to reflect the ability of lipids and their digestion products to interact with endogenous bile-salt phospholipid micelles in the GIT, resulting in an increase in the solubilization capacity of the GI fluids. The aim of the present study was to improve the solubility of FFB by lipid-based LC formulation. Considering the advantages of this pharmaceutical technology that provides the large membrane surface area, LCs can increase the solubility of FFB, thereby improve its bioavailability.
| Materials And Methods|| |
FFB was provided by Faraby Pharmaceutical Company (Iran). Glyceryl monostearate (GMS), Pluronic F127, and Tween 20 were purchased from Merck Chemical Company (Germany), colloidal silica was from Sigma-Aldrich Company (USA). Dialysis bag was obtained from the Armaghane Kali Gavan Co (Iran). All chemicals and solvents were of analytical grade. Minitab Software (Version 16, USA) was used for experimental design and the evaluation of the effect of variables on responses.
The quantitative determination of FFB was performed by ultraviolet (UV) spectrophotometer (Biochrom WPA BioWave II, England) at λmax = 288 nm in 0.1 N of hydrochloric acid containing 1% of Tween 20. The validity of the assay method involving linearity, repeatability, accuracy, and limit of quantification were calculated.
Preparation of fenofibrate liquid crystal formulations
For the preparation of FFB LC formulations, FFB was dissolved in GMS (as the lipid phase), then aqueous solution of stabilizer (Pluronic F127 or colloidal silica) was added to the lipid phase. The final mixture was heated at 50°C with sonication in a bath sonicator (POWER-SONIC 505, Korea) at power of 500 W. Independent variables in this study included; concentration of the lipid (1, 1.5, 2 w/w%), concentration of the stabilizer (0.5, 5, and 10 w/w%), and the type of stabilizer (Pluronic F127 or colloidal silica). The concentration of the drug in all formulations was kept constant at 1 w/w%. The composition of different formulations is illustrated in [Table 1].
|Table 1: The compositions, particle size, polydispersity index, and drug loading percentage of the different liquid crystal formulations of fenofibrate|
Click here to view
Recognition of anisotropy of liquid crystals by polarized microscopy
Polarized microscopy method was used as a quick and easy inspection method to show the birefringence behavior of the LCs. The texture of the samples was observed by the polarizing microscope (HUND, Germany). A small quantity of the sample was placed on a clean glass slide. The existence of birefringence was verified by observation under crossed polarizer employing magnification of ×20. The observations were carried out at room temperature.
Ternary diagram determination
Eighteen prepared formulations containing 1 w/w% of the drug, 1–2 w/w% of lipid, and 0.5–10 w/w% of the stabilizers including; Pluronic F127 or colloidal silica, were stored at room temperature for 1 week to reach the equilibration. Phase equilibria were determined by visual observation of the samples in normal light and also by cross-polarizing microscope for anisotropy. Formation points of LCs were recorded and the ternary diagram of variables was plotted to represent the limitation of the area formation of liquid crystalline phases.
Particle size measurement
Determination of particle size of nanoparticles was done by dynamic light scattering method using Zetasizer Nano ZS (Malvern Instruments Gmb H, Malvern, UK). The LC formulations were diluted 50-fold with purified water before all measurements.
Drug loading efficiency in liquid crystals
The specified amount of LC formulation was centrifuged (Sigma, US) at 8000 rpm for 20 min. Then, the clear supernatant liquid was decanted. The dissolved FFB in the liquid phase was measured using spectrophotometer (UV-mini-1240 CE-Shimadzu, Japan) at λmax = 228 nm. Then, the percent of the drug loaded into LCs was calculated according to the initial drug payload.
Rheological measurements were performed using a Brookfield (DV-III ultra rheometer, USA). After selecting an appropriate spindle, the specified volume of LCs formulation was placed in the beaker of the device and the spindle was plunged in the sample. Then, the different increasing rates of shear (rpm) were applied to the sample and different shear stresses arising from the rate of shear were recorded (in constant temperature at 25°C). The changes of the rate of shear versus shearing stress were plotted for each sample.
Drug release studied from liquid crystal formulations
In vitro, drug release studies were performed using the dialysis technique. The cellulose acetate membrane (cutoff –8000 Da) was soaked in the distilled water at 25°C for 24 h. Then, 6 cm2 of the dialysis bag was loaded with 2 mg of the formulation and the bag was placed in a beaker filled with a mixture of 1% of Tween 20 in HCl 0.1 N. The solution of the beaker was constantly stirred by the externally driven magnetic bar at 200 rpm throughout the experiment. At specified time intervals of 0.5, 1, 2, 3, 4, 5, 6, 7, and 8 h, 400 μl samples were taken from the beaker and the drug was determined spectrophotometrically at 288 nm. The withdrawn samples were immediately replaced with an equal volume of fresh solution.
The dissolution efficiency (DE%) of different formulations was calculated according to the following equation:
Where y is the percentage of dissolved drug at time t.
| Results|| |
The validity of drug measurement
The correlation coefficient for the concentration–absorbance curve was R2 = 0.996, which means that 99.6% of the absorbance values are estimated by the concentration. Regression analysis showed a significant relationship between concentration and the light absorbance (P = 0.001). The lack-of-fit in this study was not statistically significant (P = 0.115), which appears in the estimated absorbance changes. The accuracy of measurement indicated that the concentrations were close to the actual values. The results showed the desirable repeatability of the measurements were achieved within and between days.
Ternary diagram and polarized microscopy
The ternary phase diagram of lipid/stabilizer/water system is constructed and presented in [Figure 1]. The region marked in points shows the limits of LCs formation region. Eight samples marked in the phase diagram were selected to study. The contents of each component are listed in [Table 1]. LCs were formed in 1%–2% of the lipid and 0.5%–10% of the stabilizer with both types of the stabilizers (Pluronic F127 and colloidal silica).
|Figure 1: The ternary phase diagram of lipid/stabilizer/water system used for the production of fenofibrate liquid crystals|
Click here to view
[Figure 2] shows the polarized microscopy micrograph that demonstrates birefringence behavior of the LCs.
|Figure 2: The birefringent behavior of the prepared formulations of fenofibrate liquid crystals|
Click here to view
Particle size distribution
Particle size and poly dispersity index (PDI) of different LC formulations are demonstrated in [Table 1]. The results of this table indicate that the particle size of formulations was between 42 and 503 nm with PDI was <0.7. The minimum and maximum values of particle size relate to formulations P0.5G1.5 and P5G2, respectively. The effects of the studied independent variables were also studied on the mean particle size of LC formulations. The following equation demonstrates the regression between the independent variables and the particle size:
Particle size = 57.303 (X1) +0.172 (X2) +188.011 (X3)–56.157 (eq. 1)
Where X1 is the type of stabilizer, X2 is the percentage of stabilizer, and X3 is the percentage of lipid. Regression analysis showed there was a significant relationship between the mean particle size and the percentage of the stabilizer and the lipid (P < 0.05). Thus, the particle size was affected by formulation parameters and considering the positive sign of all variables in eq. 1.
[Table 1] shows the drug loading efficiency in different LC formulations of FFB. Based on the results, the drug loading efficiency was more than 95% in all of the formulations. The minimum and maximum drug loading efficiency was seen in formulations P0.5G1 and P0.5G1.5, respectively. The following equation demonstrates the regression between the studied independent variables and the drug loading efficiency (LE%):
LE% = 0.553 (X1) +0.177 (X2) +1.321 (X3) +95.544 eq. 2
Regression analysis showed that there was a significant relationship between LE% and the percent of stabilizer (X2) and lipid (X3). So that, with increasing in lipid percent from 1 to 2, and increasing in stabilizer percent from 0.5to–5 and 0.5 to 10, the LE% increased and all of the this variables had a positive effect on the LE%.
Rheological properties of the liquid crystal formulations
The stable flow behavior curves of the LC phases are shown in [Figure 3]. All of the samples behaved as shear thinning fluids. The only significant parameter affecting on the shearing stress of formulations was the stabilizer type, in which by changing the stabilizer type from Pluronic F127 to colloidal silica the shearing stress increased significantly (P < 0.05). The other studied variables had no significant effect on the shearing stress of the formulations (P > 0.05).
|Figure 3: Rheograms of the liquid crystalline formulations of fenofibrate|
Click here to view
The dissolution efficiency (DE%) of different formulations varied between 16.58% and 35.83%. The minimum and maximum of DE belonged to formulations C5G2 and P0.5G1.5, respectively [Figure 4]. All formulations except two (C0.5G1.5 and C5G2) showed more DE% than pure drug [Figure 4]. In formulations P0.5G1.5,P5G2, and P10G1, this difference was statistically significant (P < 0.05). The following equation demonstrates the regression between independent studied variables and DE%:
|Figure 4: Dissolution efficiency percent of fenofibrate in the different studied formulation of liquid crystals (n = 3)|
Click here to view
DE% = −8.12 (X1)−0.13 (X2)−3.53(X3) +43.1 eq. 3
The only significant effective parameter on the DE% was the stabilizer type. So that, by changing in stabilizer from colloidal silica to Pluronic F127, DE% was increased.
| Discussion|| |
Particle size distribution
According to the results, the particle size was affected by formulation parameters and considering the positive sign of all variables in eq. 1, it may be concluded that all of them had an increasing or synergistic effect on the particle size of the LCs. This has been suggested to be the result of stabilizer incorporated into the GMS bilayer, causing swelling and ultimately a transformation of nanostructure resulting to increase in particle size. When the stabilizer content was kept constant and the concentration of GMS used in dispersion was increased, the particle size of the LCs increased. The increase in GMS was expected to manifest proportionally increase in surface area while stabilizer content was held constant. Considering the surface area of the system has increased, but equal amounts of stabilizer associated per unit surface area was constant, it may be concluded that the stabilizer was changing its conformation at the interface, thereby allowing the polymer to occupy the greater surface area at the same concentration. These results are in accordance with the results obtained in previous studies.,,
According to the results of [Table 1], increasing in lipid content caused to increase of LE%. This may be related to hydrophobic properties of the encapsulated drug in LCs. Increasing in lipid content makes the LCs more lipophilic and more capable to entrap and solubilize the lipophilic drugs. Furthermore, increasing in stabilizer percentage makes the LCs be more stable and help to solubilize more drug.
Rheological properties of the liquid crystal formulations
Based on regression analysis, the only significant parameter affecting on the shearing stress of formulations was the stabilizer type, in which by changing the stabilizer type from Pluronic F127 to colloidal silica the shearing stress increased. The micellar phase or hexagonal phase (H1) could be found in a less hydrophilic surfactant system on the solubilization of the oil. Since the Pluronic is not a very hydrophilic surfactant, it appears in the micellar phase up to a certain concentration. Beyond this concentration, the hexagonal phase (H1) appears. In contrast, colloidal silica is not amphiphilic; therefore, it appears in the cubic phase. The cubic phases are even more viscous than the hexagonal phases. Some reports are available on the rheological behavior of different phases of LCs which are related to this phenomenon.
According to the results, the only significant effective parameter on the DE% was the stabilizer type. So that, by changing in stabilizer from colloidal silica to Pluronic F127, DE% was increased. This may be related to the viscosity of LCs formulation. According to the results of section 3.5, LCs formulations which contained colloidal silica as a stabilizer showed more viscosity than formulation prepared with Pluronic. The reason may be related to the increase in LCs matrix viscosity, which caused slower diffusion of the aqueous release media to the matrix, and consequently, decrease in drug release rate. Furthermore, previous studies showed that addition of Pluronic to LCs formulation accelerated drug release. According to the results, LC formulations have been successful to improving solubility and bioavailability of FFB, which is consistent with the results of previous studies. In addition, this study has addressed the disadvantages and problems of previous studies including the method of preparing LCs. Despite previous studies in this study, LC formulations are easily made at a lower temperature without any need for high pressure, which makes it possible to industrial scale-up.
| Conclusions|| |
Dissolution property of FFB, a poorly soluble drug, was improved by preparing LC formulations using rapid and simple method with two different stabilizers, Pluronic F127 and colloidal silica. LCs could increase the solubility and in vitro releasing of this poorly soluble drug, thus expecting to improve its bioavailability. Drug release profiles showed that in the most formulations of FFB LCs, the DE% was more than the pure FFB, and therefore, it seems that the liquid crystalline formulations would be effective for enhancing drug release. Furthermore, drug release rate depended on the stabilizer type, so that the presence of colloidal silica caused slower drug release compared to Pluronic F127.
Increasing in lipid content caused increasing in LE%. On the other hands, lipid component in LC formulations had a critical role in hydrophobic drug encapsulation. Particle size distribution was affected by the percentage of the stabilizer and the lipid. Considering that GMS formed the bilayer structure in LCs, increasing of stabilizer content led to swelling and increasing in particle size. Altogether, LC formulations, especially formulations containing Pluronic F127 as a stabilizer, are suitable for increasing the dissolution rate of FFB.
Financial support and sponsorship
Financial support of this work by Research Vice Chancellor of Isfahan University of Medical Sciences is acknowledged.
Conflicts of interest
There are no conflicts of interest.
| References|| |
Di L, Fish PV, Mano T. Bridging solubility between drug discovery and development. Drug Discov Today 2012;17:486-95.
Bergström CA, Holm R, Jørgensen SA, Andersson SB, Artursson P, Beato S, et al.
Early pharmaceutical profiling to predict oral drug absorption: Current status and unmet needs. Eur J Pharm Sci 2014;57:173-99.
Custodio JM, Wu CY, Benet LZ. Predicting drug disposition, absorption/elimination/transporter interplay and the role of food on drug absorption. Adv Drug Deliv Rev 2008;60:717-33.
Sauron R, Wilkins M, Jessent V, Dubois A, Maillot C, Weil A, et al.
Absence of a food effect with a 145 mg nanoparticle fenofibrate tablet formulation. Int J Clin Pharmacol Ther 2006;44:64-70.
Sanganwar GP, Gupta RB. Dissolution-rate enhancement of fenofibrate by adsorption onto silica using supercritical carbon dioxide. Int J Pharm 2008;360:213-8.
Wishart DS, Knox C, Guo AC, Shrivastava S, Hassanali M, Stothard P, et al.
DrugBank: A comprehensive resource for in silico
drug discovery and exploration. Nucleic Acids Res 2006;34:D668-72.
Ming-Thau S, Ching-Min Y, Sokoloski TD. Characterization and dissolution of fenofibrate solid dispersion systems. Int J Pharm 1994;103:137-46.
Löbenberg R, Amidon GL. Modern bioavailability, bioequivalence and biopharmaceutics classification system. New scientific approaches to international regulatory standards. Eur J Pharm Biopharm 2000;50:3-12.
Guay DR. Micronized fenofibrate: A new fibric acid hypolipidemic agent. Ann Pharmacother 1999;33:1083-103.
Granero GE, Ramachandran C, Amidon GL. Dissolution and solubility behavior of fenofibrate in sodium lauryl sulfate solutions. Drug Dev Ind Pharm 2005;31:917-22.
Badens E, Majerik V, Horváth G, Szokonya L, Bosc N, Teillaud E, et al.
Comparison of solid dispersions produced by supercritical antisolvent and spray-freezing technologies. Int J Pharm 2009;377:25-34.
Leuner C, Dressman J. Improving drug solubility for oral delivery using solid dispersions. Eur J Pharm Biopharm 2000;50:47-60.
Perrut M, Jung J, Leboeuf F. Enhancement of dissolution rate of poorly-soluble active ingredients by supercritical fluid processes. Part I: Micronization of neat particles. Int J Pharm 2005;288:3-10.
Junghanns JU, Müller RH. Nanocrystal technology, drug delivery and clinical applications. Int J Nanomedicine 2008;3:295-309.
Williams HD, Trevaskis NL, Yeap YY, Anby MU, Pouton CW, Porter CJ, et al.
Lipid-based formulations and drug supersaturation: Harnessing the unique benefits of the lipid digestion/absorption pathway. Pharm Res 2013;30:2976-92.
O'Reilly JR, Corrigan OI, O'Driscoll CM. The effect of mixed micellar systems, bile acid/fatty acids, on the solubility and intestinal absorption of clofazimine (B663) in the anaesthetized rat. Int J Pharm 1994;109:147-54.
Srinarong P, Faber JH, Visser MR, Hinrichs WL, Frijlink HW. Strongly enhanced dissolution rate of fenofibrate solid dispersion tablets by incorporation of superdisintegrants. Eur J Pharm Biopharm 2009;73:154-61.
Patel AR, Vavia PR. Effect of hydrophilic polymer on solubilization of fenofibrate by cyclodextrin complexation. J Incl Pheno Macrocycl Chem 2006;56:247-51.
Wei LL, Peixin, W Chandra N, Say Chye JL. Gastric-floating microcapsules provide controlled and sustained release of multiple cardiovascular drugs, J Mater Chem 2013;1:1090-5.
Bhargava P, Bhargava S, Daharwal SJ. Self emulsifying drug delivery system: An approach to improve the solubility of poorly water soluble drug. Adv Res Pharm Biol 2011;1:1-9.
Yamada K, Yamashita J, Todo H, Miyamoto K, Hashimoto S, Tokudome Y, et al.
Preparation and evaluation of liquid-crystal formulations with skin-permeation-enhancing abilities for entrapped drugs. J Oleo Sci 2011;60:31-40.
Clogston J, Rathman J, Tomasko D, Walker H, Caffrey M. Phase behavior of a monoacylglycerol: (myverol 18-99K)/water system. Chem Phys Lipids 2000;107:191-220.
Lian R, Lu Y, Qi J, Tan Y, Niu M, Guan P, et al.
Silymarin glyceryl monooleate/poloxamer 407 liquid crystalline matrices: Physical characterization and enhanced oral bioavailability. AAPS PharmSciTech 2011;12:1234-40.
Drummond CJ, Fong C. Surfactant self-assembly objects as novel drug delivery vehicles. Curr Opin Colloid Interf Sci 1999;4:449-56.
Chung H, Kim J, Um JY, Kwon IC, Jeong SY. Self-assembled “nanocubicle” as a carrier for peroral insulin delivery. Diabetologia 2002;45:448-51.
Lopes LB, Lopes JL, Oliveira DC, Thomazini JA, Garcia MT, Fantini MC, et al.
Liquid crystalline phases of monoolein and water for topical delivery of cyclosporin A: Characterization and study of in vitro
and in vivo
delivery. Eur J Pharm Biopharm 2006;63:146-55.
Boyd BJ, Whittaker DV, Khoo SM, Davey G. Lyotropic liquid crystalline phases formed from glycerate surfactants as sustained release drug delivery systems. Int J Pharm 2006;309:218-26.
Norling T, Lading P, Engström S, Larsson K, Krog N, Nissen SS, et al.
Formulation of a drug delivery system based on a mixture of monoglycerides and triglycerides for use in the treatment of periodontal disease. J Clin Periodontol 1992;19:687-92.
Gustafsson J, Ljusberg-Wahren H, Almgren M, Larsson K. Submicron particles of reversed lipid phases in water stabilized by a nonionic amphiphilic polymer. Langmuir 1997;13:6964-71.
Briggs J, Caffrey M. The temperature-composition phase diagram and mesophase structure characterization of monopentadecenoin in water. Biophys J 1994;67:1594-602.
Barauskas J, Landh T. Phase behaviour of the phytantriol/water system, Langmuir. 2003;19:9562-5.
Hato M, Minamikawa H. The effects of oligosaccharide stereochemistry on the physical properties of aqueous synthetic glycolipids. Langmuir 1996;12:1658-65.
Charman WN, Rogge MC, Boddy AW, Berger BM. Effect of food and a monoglyceride emulsion formulation on danazol bioavailability. J Clin Pharmacol 1993;33:381-6.
Ermer J. Performance parameters, calculation and tests. In: Ermer J, Miller J, editors. Method validation in Pharmaceutical Analysis. New York: Wiley-VCH, Verlag GMBH; 2005. p. 21-119.
Nesseem DI. Formulation and evaluation of itraconazole via liquid crystal for topical delivery system. J Pharm Biomed Anal 2001;26:387-99.
Ghosh PK, Majithiya RJ, Umrethia ML, Murthy RS. Design and development of microemulsion drug delivery system of acyclovir for improvement of oral bioavailability. AAPS PharmSciTech 2006;7:77.
Tilley AJ, Drummond CJ, Boyd BJ. Disposition and association of the steric stabilizer pluronic® F127 in lyotropic liquid crystalline nanostructured particle dispersions. J Colloid Interface Sci 2013;392:288-96.
Chong JY, Mulet X, Waddington LJ, Boyd BJ, Drummond CJ. Steric stabilisation of self-assembled cubic lyotropic liquid crystalline nanoparticles: High throughput evaluation of triblock polyethene oxide-polypropylene oxide-polyethene oxide copolymers, Soft Matter 2011;7:4768.
Dong YD, Larson I, Hanley T, Boyd BJ. Bulk and dispersed aqueous phase behavior of phytantriol: Effect of Vitamin E acetate and F127 polymer on liquid crystal nanostructure. Langmuir 2006;22:9512-8.
Alam MM, Sugiyama Y, Watanabe K, Aramaki K. Phase behavior and rheology of oil-swollen micellar cubic phase and gel emulsions in nonionic surfactant systems. J Colloid Interface Sci 2010;341:267-72.
Milak S, Zimmer A. Glycerol monooleate liquid crystalline phases used in drug delivery systems. Int J Pharm 2015;478:569-87.
Wei S, Ren J, Li N, Huo W, Gao C. Preparation and pharmacokinetic study of fenofibrate cubic liquid crystalline. Asian J Pharm Sci 2017;17:30193-9.
[Figure 1], [Figure 2], [Figure 3], [Figure 4]