Ibuprofen-loaded poly(lactic-co-glycolic acid) films for controlled drug release.

Ibuprofen- (IBU) loaded biocompatible poly(lactic-co-glycolic acid) (PLGA) films were prepared by spreading polymer/ibuprofen solution on the nonsolvent surface. By controlling the weight ratio of drug and polymer, different drug loading polymer films can be obtained. The synthesized ibuprofen-loaded PLGA films were characterized with scanning electron microscopy, powder X-ray diffraction, and differential scanning calorimetry. The drug release behavior of the as-prepared IBU-loaded PLGA films was studied to reveal their potential application in drug delivery systems. The results show the feasibility of the as-obtained films for controlling drug release. Furthermore, the drug release rate of the film could be controlled by the drug loading content and the release medium. The development of a biodegradable ibuprofen system, based on films, should be of great interest in drug delivery systems.

Introduction

Nowadays, poly(lactic-co-glycolic acid) (PLGA) is widely applied in controlled drug delivery systems due to its biodegradability, toxicological safety, and good biocompatibility.1–5 Specifically, PLGA-based carriers have been used in long-term drug delivery systems because they have the potential to control drug release from a few days up to several months.6,7 In general, PLGA can degrade into water soluble, non-toxic products of normal metabolism through hydrolysis which is important for its practical application.8 Moreover, PLGA is one of the few synthetic polymers which have been approved for human clinical use. Several products such as Lupron Depot based on PLGA microparticles are available on the market.5,9 However, PLGA-based carriers are mostly solid particles including nanoparticles, microparticles, and microcapsules, which have the disadvantages of low drug loading capacity, easy aggregation, and polydispersable particle sizes.10 Therefore, it is necessary to prepare aspherical carriers instead of particles. Various biocompatible and biodegradable polymer films have been widely used for controlled drug release due to their excellent characteristics, such as high surface area, softness, absorbency, and ease of fabrication into many product forms.11–16 Until now, a number of methods have been developed for fabrication of polymer films, such as layer-by-layer (LBL) method17 and solvent evaporation technique.18 However, the reported methods usually involve some cumbersome processing steps and are time-consuming. Therefore developing a simple route to prepare drug-loaded fibers is still a great challenge.

Ibuprofen (IBU) is classified by the Biopharmaceutics Classification System (BCS) as a Class II active pharmaceutical ingredient as it presents low solubility and high permeability.19 Thus, increasing the solubility of IBU to enhance its bioavailability is the major obstacle.20,21 Previous studies indicate that the formulated IBU microspheres have a high initial burst resulting from the accumulation of drug crystals on the surface of microspheres.8,22 In some cases, the formulated IBU microspheres are unsuitable for well controlled release.

In this paper we present a very simple and general route to prepare drug-loaded films.23,24 The biocompatible PLGA and IBU are used as the model polymer and drug, respectively. Both PLGA and IBU are dissolved in tetrahydrofuran (THF), and then 50 μL of the solution is injected on the surface of the water. PLGA and IBU are indissoluble in water while THF and water are mixable. Thus, the IBU-loaded PLGA film is obtained on the surface of water. Films with different drug-loading contents could be prepared by controlling the ratios of IBU and PLGA. The aims of this study are to prepare IBU-loaded PLGA films with a simple route, and to characterize these films for their potential applications in drug delivery systems.

Materials and methods

Materials

L-lactic acid (LA) and glycolic acid (GA) were purchased from Sinopharm Chemical Reagent Co. Ltd (Shanghai, China). PLGA was synthesized according to the literature.25 The MW of PLGA (LA/GA = 75/25, MW = 80,000 g/mol) was determined by the inherent viscosity. IBU was bought from Aldrich. Double-distilled water was used in all the experiments. All chemicals were used as received.

Preparation of drug-loaded PLGA films

For a typical synthesis, appropriate amounts of PLGA and IBU were dissolved in tetrahydrofuran (THF). The weight ratio of THF/PLGA/IBU in the solution was WTHF/WPLGA/WIBU = 85/12.5/2.5. A pipette was used to take 50 μL of the solution and then the solution was injected on the surface of distilled water in a beaker (the distance between the water surface and the drop source was 1 cm). The solution spread quickly on the surface of water and solidified into a film within 3 seconds then the film was taken out at once and washed with distilled water and dried in air at 40°C. For the samples synthesized with different weight ratios, such as WTHF/WPLGA/WIBU = 85/11.25/3.75 and WTHF/WPLGA/WIBU = 85/10/5, the synthetic procedures were similar to the above.

Drug loading and encapsulation efficiency

A certain amount of dried film was dissolved in 10 mL of THF. The UV absorbance of the solution was measured using a UV spectrophotometer at wavelength 264 nm which was a typical absorbance of IBU in THF. Pure THF was used for a blank experiment before the UV measurement. Drug loading content (DLC) and encapsulation efficiency (EE) were determined using the following equations.

In vitro release studies

Three kinds of release mediums (phosphate buffered solution, PBS, pH = 6.8; phosphate buffered solution, PBS, pH = 7.4; and HCl aqueous solution, pH = 1.2) were used to study the in vitro release. In drug release studies, PBS was the typical medium to mimic intestinal fluid. The release of samples with different ratios (WTHF/WPLGA/WIBU = 85/12.5/2.5, WTHF/WPLGA/WIBU = 85/11.25/3.75, and WTHF/WPLGA/WIBU = 85/10/5) were performed in 50 mL PBS (pH 6.8). The influence of the release medium on the sample (WTHF/WPLGA/WIBU = 85/12.5/2.5) was performed in 50 mL HCl solution (pH 1.2) and PBS (pH 7.4), respectively. The in vitro experiments were carried out in a heated bath at 37°C in triplicate. The sample was sealed in a dialysis bag (from Solarbio, Beijing, China), which was suspended in 50 mL release medium in a sealed beaker under continuous stirring at a rate of 100 rpm.26,27 At predetermined time intervals, 1.5 mL of the resultant release medium was sampled for analysis, then 1.5 mL of fresh release medium was immediately added to maintain the original volume. Based on the standard curve, the IBU concentration in the sampled release medium was obtained through UV experiment (λ = 222 nm).

The cumulative amount of IBU released from the samples was calculated using the equation:

Mt was the amount of IBU released from the PLGA films at time t and Mtotal was the total amount of IBU loaded in the PLGA films.

Drug release kinetics

The kinetics of IBU release from the films were determined by fitting different curves to distinct models. The models included Zero order, First order, Higuchi release model, Ritger-Peppas, and Biexponential model. The linear form of each function was evaluated using R regression analysis.

SEM

Scanning electron microscopy (SEM) was done using a Hitachi SU-70 FESEM scanning electron microscope operated at 3 kV. Samples were sputtered with Au prior to imaging (the thickness of Au was 5 nm).

X-ray diffraction (XRD) measurements

XRD measurements were obtained on a Rigaku Dmax-rc X-ray diffractometer with Ni filtered Cu Kα radiation. The angular range was from 10° to 60°.

DSC measurements

Differential scanning calorimetry (DSC) measurements were performed using CDR-4P (Shanghai Precision and Scientific Instrument Co., Ltd. China). Weighed samples of 5 mg were placed in aluminum pans and the samples were scanned from 40°C to 200°C using a heating rate of 10°C/min.

Results and discussion

The results of drug loading and encapsulation efficiencies with different WTHF/WPLGA/WIBU ratios are shown in Table 1. The drug loading contents for the samples of WTHF/WPLGA/WIBU = 85/12.5/2.5, WTHF/WPLGA/WIBU = 85/11.25/3.75, and WTHF/WPLGA/WIBU = 85/10/5 are 14.7% ± 0.2%, 22% ± 1.6% and 29.7% ± 0.4%, respectively. The values are a little smaller than the corresponding ones in theory (16.7%, 25%, and 33.3%, respectively). As for the encapsulation efficiency, the samples exhibit high percentages (more than 88%) and there are no remarkable differences among the different samples. These results reveal that our method is a simple and efficient way to prepare films with high drug loading and encapsulation efficiency. The high drug loading and encapsulation efficiency can be explained by the solubility of IBU and PLGA in THF, but their insolubility in water. THF, however, is intersoluble with water. When the mixed solution spreads on the water surface, the THF molecules immediately diffuse into the water phase, leaving the PLGA and IBU molecules to quickly solidify due to their indissolubility in water. Thus, high drug loading and encapsulation efficiency are obtained.

Table 1.

Drug loading and encapsulation efficiency (%) at various IBU/PLGA weight ratios (± SD, n = 3)

Ratio of WTHF/WPLGA/WIBU	85/12.5/2.5	85/11.25/3.75	85/10/5
Drug loading (%)	14.7 ± 0.2	22.0 ± 1.6	29.7 ± 0.4
Theoretical loading (%)	16.7	25	33.3
Encapsulation efficiency (%)	88.2 ± 1.2	88.0 ± 6.6	89.1 ± 1.3

Abbreviations: IBU, ibuprofen; PLGA, poly(lactic-co-glycolic acid).

Electron microscopy

Figure 1 shows SEM images of the IBU-loaded PLGA film with the ratio of WTHF/WPLGA/WIBU = 85/12.5/2.5.

Figure 1.

SEM images of IBU-loaded PLGA films WTHF/WPLGA/WIBU = 85/12.5/2.5), the surface (A), and the thickness (B).

Abbreviations: IBU, ibuprofen; PLGA, poly(lactic-co-glycolic acid); SEM, scanning electron microscopy.

Figure 1A exhibits the top surface of the film, which has a convex pattern. The diameter of each convex shape is 1.52 ± 0.45 μm. Figure 1B shows a cross-section image of the film, which has a smooth surface, indicating the absence of a void in the film.

Figure 2 shows the SEM images of films with different ratios of WTHF/WPLGA/WIBU. Figure 2A shows the film with a ratio of WTHF/WPLGA/WIBU = 85/11.25/3.75. It shows that the film has a convex pattern on the top surface. The diameter of each convex shape is 0.87 ± 0.11 μm. The insert in Figure 2A shows the rough cross-section surface which indicates the presence of voids in the film. Figure 2B shows the film with a ratio of WTHF/WPLGA/WIBU = 85/10/5. The top surface is relatively smooth and has no convex pattern. Furthermore, the cross-section of the film is rough, which indicates that there are voids in the film.

Figure 2.

SEM images of IBU-loaded PLGA films, WTHF/WPLGA/WIBU = 85/11.25/3.75 (A) and WTHF/WPLGA/WIBU = 85/10/5 (B).

Abbreviations: IBU, ibuprofen; PLGA, poly(lactic-co-glycolic acid); SEM, scanning electron microscopy.

The SEM images in Figure 1 and Figure 2 show that there are voids in the film formed with higher drug concentration (WTHF/WPLGA/WIBU = 85/11.25/3.75 and WTHF/WPLGA/WIBU = 85/10/5) while there are no obvious voids in the film formed at lower drug concentration (WTHF/WPLGA/WIBU = 85/12.5/2.5). There is a convex pattern in the samples of WTHF/WPLGA/WIBU = 85/12.5/2.5 and WTHF/WPLGA/WIBU = 85/11.25/3.75. However, there is no convex pattern for the sample of WTHF/WPLGA/WIBU = 85/10/5. The convex-patterned surface may result from the surface tension when the phase separation proceeds at the top surface of the polymer solution, ie, the air/solution interface.24 The films have a dimension of about 33 cm2, which is as large as the Baker’s dimension. The thickness of all the films with different weight ratios is in the range of 2 to 5 μm. In short, the ratio of WTHF/WPLGA/WIBU has a large influence on the surface morphology and structure of the films. For the formation of IBU-loaded PLGA film, the THF solvent diffuses quickly into water which leaves the undissolved IBU and PLGA solidified. In this case, the IBU and PLGA form a thin film on the surface of water. It is known that IBU and PLGA can dissolve well in THF as molecular state, and therefore the drug is distributed homogenously in the formed films.

XRD measurements

X-ray diffraction (XRD) patterns were established on the pure IBU, pure PLGA, and the IBU-loaded PLGA films, in order to study the physical state of these systems. Generally, when the patterns of two crystal forms are identical in terms of peak positions, they have the same internal crystal structure, whereas if the patterns differ, the crystals have a different internal structure and are recognized as polymorphs.28 The XRD pattern of pure PLGA shown in Figure 3a has no evident brand, which denotes an amorphous polymeric compound. Figure 3b shows the XRD patterns of pure IBU, which yields typical peaks at 16°, 20°, and 22°, showing the crystalline substance. In the curves of IBU-loaded PLGA films shown in Figure 3c, d, and e, peaks at 16°, 20°, and 22° were detected in the three samples, which demonstrates that IBU had a crystalline state in the film. The difference in the relative intensity of the peaks is due either to the variation of the crystal habit, because the relative abundance of the planes exposed to X-ray source is altered, or to differences in the size of the crystals.28

Figure 3.

XRD patterns of: a) pure IBU, b) PLGA, and IBU-loaded PLGA films: c) WTHF/WPLGA/WIBU = 85/12.5/2.5; d) WTHF/WPLGA/WIBU = 85/11.25/3.75 and e) WTHF/WPLGA/WIBU = 85/10/5.

Abbreviations: IBU, ibuprofen; PLGA, poly(lactic-co-glycolic acid); XRD, X-ray diffraction.

In order to further study the drug–polymer interaction, the DSC thermal characteristics of IBU-loaded PLGA films (c, d, and e) are compared with pure PLGA (a) and pure IBU (b) in Figure 4. The endothermic peak of PLGA (curve a) is observed at 56°C, which can be attributed to the glass-transition temperature of PLGA. The curve in Figure 4 shows a sharp endothermic peak at 78°C, which indicates that the melting peak of pure IBU is 78°C. The curves c, d, and e in Figure 4 show the peaks of different drug-loading films. Comparing with pure IBU, the melting points are 65, 75, and 73 for the samples of WTHF/WPLGA/WIBU = 85/12.5/2.5, WTHF/WPLGA/WIBU = 85/11.25/3.75 and WTHF/WPLGA/WIBU = 85/10/5, respectively. The shift of the melting point indicates a decrease of drug crystallinity. These results are consistent with the XRD analysis, which reveals that IBU is crystalline while PLGA is amorphous in the drug-loaded film.

Figure 4.

DSC curves of PLGA (a), pure IBU (b), and IBU-loaded films: c) WTHF/WPLGA/WIBU = 85/12.5/2.5; d) WTHF/WPLGA/WIBU = 85/11.25/3.75 and (e) WTHF/WPLGA/WIBU = 85/10/5.

Abbreviations: DSC, differential scanning calorimetry; IBU, ibuprofen; PLGA, poly(lactic-co-glycolic acid).

We examined the drug release behaviors of the as-prepared IBU-loaded PLGA films, in order to reveal their potential use in drug delivery systems. Figure 5 shows the release profiles of pure IBU and different ratios of WTHF/WPLGA/WIBU films in phosphate buffered solution (PBS, pH 6.8). Curve (a) shows that the pure IBU releases rapidly into the release medium with a release mount of nearly 100% in 12 hours. In contrast, in the sample with a ratio of WTHF/WPLGA/WIBU = 85/12.5/2.5, the release reached 12.7% ± 1.5% within 24 hours, and reached 32.4% ± 7.8% in 120 hours. In the sample with a ratio of WTHF/WPLGA/WIBU = 85/11.25/3.75, the release rate reached 27.5% ± 6.4% in 24 hours and 60% ± 5.5% in 120 hours. However, the release reached 46.6% ± 9.5% in 24 hours and 65.3% ± 1.6% in 120 hours in the sample with a ratio of WTHF/WPLGA/WIBU = 85/10/5. The different release percentages over the same time, show that the release rate decreases as the drug loading decreases. This can be due to the fewer drug molecules diffusing through the polymer network with the decrease of the drug loading. The polymer network becomes more porous as the drug concentration decreases, so that the soluble IBU molecules have to travel a longer distance from the pores to the release medium. The burst effect is not observed in the release, which can be explained as follows. On the one hand, the IBU is distributed homogeneously in the polymer without much surface segregation. On the other hand, rinsing the film decreases the amount of drug associated on the surface. These results show that a more controlled release can be obtained when changing the weight ratio of the drug, which indicates the potential application of the as-prepared drug-loaded PLGA products in a drug controlled delivery system.

Figure 5.

Cumulative release of different samples in pH 6.8 phosphate buffered solution, films with ratios of WTHF/WPLGA/WIBU = 85/12.5/2.5 (-▪-), WTHF/WPLGA/WIBU = 85/11.25/3.75 (-•-), WTHF/WPLGA/WIBU = 85/10/5 (-▴-) and pure IBU (-▾-).

Abbreviation: IBU, ibuprofen.

In order to better understand the importance of the release mediums on the drug release kinetics from PLGA-based films, the other two release mediums were chosen to mimic the in vitro release. Figure 6 shows the release profiles of the sample with WTHF/WPLGA/WIBU = 85/12.5/2.5 from the release mediums, HCl aqueous solution (pH 1.2) and PBS (pH 7.4). The time to reach 30% of drug release in PBS was 135 hours compared with 238 hours in HCl aqueous solution, which reveals that the drug release kinetic is faster at high pH than at low pH. The decreased release rate of IBU in acidic media (pH 1.2) may have been due to the decreased solubility of IBU. The pKa of IBU is known to be 4.42 and thus it has low aqueous solubility when the pH of the medium is below or close to 4.42. What is more, matrix erosion which is affected by medium pH is also expected to affect the drug release. It is known that PLGA hydrolysis is equilibrium-limited in acidic environments, while it is not limited by equilibrium in basic conditions. Thus the erosion of the matrix increases when the pH of the release medium increases.

Figure 6.

Cumulative release of the sample with WTHF/WPLGA/WIBU = 85/12.5/2.5 in different release mediums, pH 7.4 phosphate buffered solution (-▪-) and pH 1.2 HCl aqueous solution (-•-).

The kinetics of IBU release from the films are determined by fitting the curves to distinct models, Zero order, First order, Higuchi release model, Ritger-Peppas, and Biexponential model. The equations for the different models and the regression coefficient (R) are given in Table 2 and the best-fit model is selected on the basis of R.

Table 2.

The equations for the different models and the regression coefficient (R) of IBU-loaded PLGA films in vitro

Samples	Model	Equation	R
WTHF/WPLGA/WIBU = 85/12.5/2.5, pH = 1.2	Zero-order kinetics	Q = 0.1201 t + 3.0237	0.9972
	First-order kinetics	ln(100- Q) = −0.0014 t + 4.5786	0.9970
	Higuchi	Q = 1.6027 t1/2 −1.3078	0.9085
	Ritger-Peppas	ln Q = 0.4062 lnt + 0.6594	0.9528
	Biexponential	100- Q = 97.839e−0.1052t + 104e−0.139t	Rα = 0.9340Rβ = 0.9690
WTHF/WPLGA/WIBU = 85/12.5/2.5, pH = 7.4	Zero-order kinetics	Q = 0.2057 t + 4.2613	0.9956
	First-order kinetics	ln(100- Q) = −0.003 t + 4.5832	0.9830
	Higuchi	Q = 3.2695 t1/2 − 3.0312	0.9654
	Ritger-Peppas	ln Q = 0.5008 lnt + 0.9880	0.9894
	Biexponential	100- Q = 98.283e−1.0574t +94.796e−0.2002t	Rα = 0.9834Rβ = 0.9957
WTHF/WPLGA/WIBU = 85/12.5/2.5, pH =6.8	Zero-order kinetics	Q = 0.2281 t + 6.3468	0.9920
	First-order kinetics	ln(100- Q) = −0.0028 t + 4.5497	0.9953
	Higuchi	Q = 2.8396 t1/2 + 0.1087	0.9948
	Ritger-Peppas	ln Q = 0.4659 lnt + 1.1722	0.9955
	Biexponential	100- Q = 96.181e−0.5508t + 91.87e−0.2075t	Rα = 0.9857Rβ = 0.9945
WTHF/WPLGA/WIBU = 85/11.25/3.75, pH =6.8	Zero-order kinetics	Q = 0.4216 t + 12.675	0.9736
	First-order kinetics	ln(100- Q) = −0.0067 t + 4.4868	0.9896
	Higuchi equation	Q = 5.3614 t1/2 + 0.5101	0.9953
	Ritger-Peppas	ln Q = 0.4993 lnt + 1.6995	0.9973
	Biexponential	100- Q = 93.85e−1.0107t + 80.762e−0.3462t	Rα = 0.9933Rβ = 0.9862
WTHF/WPLGA/WIBU = 85/10/5, pH = 6.8	Zero-order kinetic	Q = 0.235 t + 28.738	0.9369
	First-order kinetics	ln(100- Q) = −0.0052 t + 4.2746	0.9761
	Higuchi equation	Q = 4.4906 t1/2 + 13.555	0.9801
	Ritger-Peppas	ln Q = 0.4194 lnt + 2.1991	0.9826
	Biexponential	100- Q = 90.346e−1.52t + 50.022e−0.1150t	Rα = 0.9968Rβ = 0.9945
Pure IBU, pH = 6.8	Zero-order kinetics	Q = 6.4129 t + 35.624	0.7701
	First-order kinetics	ln(100- Q) = −0.2586 t + 4.1051	0.9510

Note: Where Q is the fraction of drug release, t is the time, R is the regression coefficient.

For the sample WTHF/WPLGA/WIBU = 85/12.5/2.5 in pH 7.4 PBS and WTHF/WPLGA/WIBU = 85/10/5 in pH 6.8 PBS, we observe that R value is larger when fitted to a biexponential equation compared with other equations, which indicates a biexponentia release from the PLGA-based films. The R value is higher when the samples (WTHF/WPLGA/WIBU = 85/12.5/2.5 and WTHF/WPLGA/WIBU = 85/11.25/3.75) are fitted to the Ritger-Peppas kinetics equation in the pH 6.8 release medium, which indicates a Ritger-Peppas release from the PLGA matrix. When the sample (WTHF/WPLGA/WIBU = 85/12.5/2.5) is released from pH 1.2 release medium, it fits to Zero-order kinetics. As for the release of pure IBU, the R value is larger when fitting to First-order kinetics than Zero-order kinetics. Drug release from matrices is usually complex and though some processes may be clearly classified as either diffusion or erosion controlled, drug release is mostly governed by both mechanisms. However, the above results may provide a better understanding of the drug controlled release from the drug-loaded films.

Conclusion

In summary, a very simple, basic method was developed to fabricate drug-loaded biocompatible polymeric films by directly spreading polymer/drug solution on the nonsolvent surface. PLGA and IBU were used as the model polymer and drug, respectively. By controlling the weight ratio of IBU and PLGA, different drug loading percentage films can be prepared. The drug release behaviors of the as-prepared products show their potential applications in a drug controlled delivery system. The release rate of IBU from these films into phosphate buffered solutions appeared to depend on a number of factors including drug loading content and the pH of the release mediums. This method can easily be scaled up and potentially extended to the fabrication of other drug-loaded composites for the application in drug delivery systems.