V. García Fernández-Luna‡
a,
D. Mallinson‡a,
P. Alexioub,
I. Khadraa,
A. B. Mullena,
M. Pelecanoub,
M. Sagnou*b and
D. A. Lamprou*ac
aStrathclyde Institute of Pharmacy and Biomedical Sciences (SIPBS), University of Strathclyde, 161 Cathedral Street, Glasgow, G4 0RE, UK. E-mail: D.Lamprou@kent.ac.uk; Tel: +44 (0) 163 488 3927
bNCSR ‘Demokritos’, Institute of Biosciences and Applications, Athens, Greece. E-mail: sagnou@bio.demokritos.gr
cMedway School of Pharmacy, University of Kent, Medway Campus, Anson Building, Central Avenue, Chatham Maritime, Chatham, Kent ME4 4TB, UK
First published on 24th February 2017
Formation of ordered porous polymer films is one of the techniques currently under investigation for its potential for the manufacturing of coatings with biomedical applications. Aiming for films with improved characteristics against bacterial colonization, poly(methyl methacrylate) (PMMA) and polyurethane (PU) films were formed via the spin coating method on silica wafer (SW) substrates, in the absence or presence of four isatin thiosemicarbazone derivatives (ITSCs) in various concentrations. The resulting films exhibited high hydrophobicity based on contact angle goniometry measurements ranging from minimum water contact angle values of 84.0° ± 4.0 for PMMA and 85.0° ± 0.2 for PU, alone, to a maximum of 129.3° ± 2.6 and 102.1° ± 1.4, respectively, after the addition of an ITSC. Atomic force microscopy revealed rough polymer surfaces with honeycomb structures which are affected by ITSC type and concentration. PMMA films presented a higher density of pores with a smaller pore diameter (280 ± 20 nm) compared to PU films (647 ± 54 nm). A 24 h dissolution study showed a gradual release of ITSC from the PMMA film, in a pH dependent manner, reaching almost completion, while PU showed no detectable release. Overall, PMMA films blended with ITSCs present favourable characteristics for biomedical coating applications.
Bacterial infection is a serious complication of implanted biomaterials. In 2011, prosthetic infections occurred in 1.3–1.6% of all knee and hip joint replacement surgeries.16 With a view to eradicate the infections associated with film formation, some of the medical devices already in use incorporate a coated surface that is also able to release antimicrobial substances.17–19 Local release of the antimicrobial agent into a specific area has shown high effectiveness in the prevention of bacterial adhesion and the formation of microbial films. Therefore, there is an increasing interest in developing new biomedical coatings that can resist bacterial adhesion for tissue engineering.20 Moreover, there is growing focus on incorporating antibacterial drugs into biomedical coatings for targeted drug delivery.21
The heterocyclic compound 1H-indole-2,3-dione, commonly known as isatin is an outstanding building block in organic and medicinal chemistry approaches. Thiosemicarbazone derivatives of isatins (ITSCs) demonstrate a variety of biological activity, including antiviral, antibacterial, anticancer, anticonvulsant and antidepressant activity.22,23 N-Methylisatin-β-thiosemicarbazone (methisazone) has been studied extensively for their pox-viruses replication inhibition24 whereas isatin derivatives also have antifungal and anti-mycotoxin activities.25 Addition of ITSCs in poly(methyl methacrylate, PMMA) and polyurethane (PU) solutions was first attempted by our group26 in the effort to modify the polymer surface characteristics and alter its biological properties. It was shown that the addition of ITSC to PMMA dissolved in tetrahydrofuran solvent and spin-coated on to a silica wafer promoted the formation of films that displayed honeycomb structures that were highly hydrophobic; this was not observed for PU films. The present study aims to investigate further the influence of the presence of four different ITSCs (1–4, Fig. 1) on polymer film surface characteristics. ITSC 1 (K) has been shown to have significant antifungal activity,27 antiherpetic activity,28 antileishmanial activity,29 and antibacterial activity against antibiotic-resistant gram-positive bacterial strains.30 ITSC 2 (M) has been shown28 to have significant antiherpetic activity whereas isatin derivatives 3 (N) and 4 (NM) have not been studied in the literature previously.
PMMA and PU films were produced via spin coating in the presence or absence of the four ITSCs and the surface morphology, surface energy and film hydrophobicity were investigated at various concentrations of isatin derivatives. Moreover, dissolution studies were performed to evaluate the drug-releasing ability of the PMMA–ITSC or PU–ITSC blended films.
Compound (4) was synthesised according to literature28 and used as positive control. Air sensitive chemical synthesis was performed in dry and inert conditions under a nitrogen atmosphere. All reactions were routinely checked by thin-layer chromatography (TLC) on silica gel Merck 60 F254 and compounds were purified by column chromatography on silica gel using the appropriate solvent systems or by preparative high-performance liquid chromatography (HPLC). The purity of the compounds tested biologically was determined by an analytical HPLC method and was found to be greater than or equal to 95%. The purity was determined automatically by the parameters of the MS analysis performed on a HPLC Shimadzu 2010EV (Column: Merck Purospher RP-C8, 250 × 4.6 mm, 5 μm particle size), equipped with a SPD-20A UV/Vis detector. Characterisation of target compounds was established by a combination of ESI-MS and NMR techniques. 1H and 13C NMR spectra were recorded on a Bruker Advance DRX 500 MHz spectrometer. Chemical shifts are presented in ppm (δ) with internal TMS standard. Original 1H and 13C NMR spectra are presented in the ESI section (Fig. S1–S4).† MS were obtained by the mass detector of the HPLC Shimadzu 2010EV.
AFM images were acquired using a Bruker Multimode 8 atomic force microscope with a Nanoscope V controller in ambient conditions. ScanAsyst Air probes (Bruker) with V-shaped silicon nitride cantilevers with spring constants in the range 0.25–0.4 N m−1 were used. Samples were studied using a peak force quantitative nanomechanical mapping (PF-QNM) mode in air at a resolution of 512 samples per line and a scan rate of 1.0 Hz. Roughness (Ra) was calculated using Nanoscope Analysis 1.6 software on five 5 × 5 μm images.
The analysis of these contact angles allowed the calculation of surface energies. The surface energy (γS) and surface energy components values for each sample were determined by the measurement of the advancing contact angles (θA) of three different solvents on the surfaces DW (18.2 MΩ cm, γL 72.8 mN m−1 at 20 °C), EG (γL 48.0 mN m−1 at 20 °C) and DIM (γL 50.8 mN m−1 at 20 °C) (surface tension γL values from Lamprou et al.31). The contact angles of the spin-coated surfaces were measured with a Krüss DSA30B contact angle goniometer, using the sessile drop method with the Krüss Advance software. Advancing contact angles (θA) were calculated from the left and right side of each drop 5–10 s after the placement of the drop on the surface. Finally, the surface energies (γs) were obtained by calculating the mean contact angles using the Good and Oss 3-liquid formula [eqn (1)] via an in-house Visual Basic program.31 The measurement was repeated for a minimum of three samples for each polymer film, measuring 3 to 4 drops per sample (n = 9–12).
(1) |
The release of compound 2 (500 μM) from a PMMA film was carried out at room temperature using a SiriusT3 instrument. To determine the best pH range for the release of the drug, a standard dissolution test was carried out by immersing the polymer film into 20 mL of phosphate buffer adjusted to a starting pH 2.0. The release of 2 was directly measured by multi-wavelength UV absorption spectroscopy using an in situ fibre-optic UV probe. The data were recorded for 24 h starting at pH 2.0 and increasing the pH every 6 h by the addition of KOH via a capillary to determine the optimum pH for the release. At the end of the study, the dissolution at different pH of 2.04, 3.85, 5.37 and 7.26 were recorded, showing the highest release profile in the pH range 5.37 to 7.26. Therefore, further analysis was performed by repeating the experiment using pH 6.46. Data was recorded for 24 h showing that at pH 6.46 ± 0.02 the drug was released in a continuous manner through time. During the experiment the solution was continuously stirred at a constant rate. Absorption data were converted to absolute sample weight (μg) and plotted against time (min).
Advancing contact angles (θA)/° | ||||
---|---|---|---|---|
Polymer | ITSC | DW | EG | DIM |
SW | None | 62.1 ± 6.7 | 44.8 ± 7.6 | 54.0 ± 3.4 |
PMMA | None | 83.9 ± 4.5 | 60.5 ± 4.7 | 40.2 ± 0.5 |
PU | None | 85.3 ± 0.2 | 61.9 ± 4.0 | 37.3 ± 4.8 |
PMMA | 1 | 93.4 ± 2.7 | 72.7 ± 3.2 | 39.7 ± 1.8 |
PMMA | 2 | 91.8 ± 1.9 | 68.9 ± 5.9 | 35.8 ± 1.8 |
PMMA | 3 | 90.5 ± 4.3 | 70.7 ± 2.2 | 38.6 ± 2.7 |
PMMA | 4 | 118.8 ± 0.7 | 96.5 ± 2.7 | 73.0 ± 5.4 |
PU | 1 | 88.8 ± 3.3 | 68.4 ± 0.7 | 31.6 ± 1.9 |
PU | 2 | 92.1 ± 1.8 | 71.4 ± 1.5 | 32.1 ± 1.7 |
PU | 3 | 84.4 ± 1.1 | 65.4 ± 2.4 | 30.6 ± 2.8 |
PU | 4 | 88.8 ± 1.8 | 63.9 ± 2.2 | 34.9 ± 1.6 |
Advancing contact angles (θA)/° | ||||
---|---|---|---|---|
Polymer | ITSC | DW | EG | DIM |
PMMA | 1 | 129.3 ± 2.6 | 100 ± 3.6 | 37.9 ± 3.6 |
PMMA | 2 | 123.5 ± 3.7 | 94.5 ± 6.3 | 41.2 ± 0.5 |
PMMA | 3 | 123.6 ± 2.7 | 100.0 ± 2.0 | 36.7 ± 0.9 |
PMMA | 4 | 119.6 ± 0.6 | 91.4 ± 5.8 | 41.7 ± 1.8 |
PU | 1 | 101.7 ± 0.5 | 72.8 ± 2.8 | 32.2 ± 0.1 |
PU | 2 | 100.6 ± 0.8 | 72.1 ± 0.2 | 32.0 ± 0.2 |
PU | 3 | 97.4 ± 3.2 | 72.9 ± 2.2 | 32.0 ± 0.3 |
PU | 4 | 101.5 ± 1.4 | 72.7 ± 3.9 | 32.5 ± 1.3 |
Advancing contact angles (θA)/° | ||||
---|---|---|---|---|
Polymer | ITSC | DW | EG | DIM |
PMMA | 1 | 123.6 ± 2.2 | 100.3 ± 1.2 | 39.6 ± 1.9 |
PMMA | 2 | 119.8 ± 5.0 | 92.6 ± 4.2 | 37.2 ± 2.8 |
PMMA | 3 | 121.9 ± 1.2 | 93.8 ± 6.6 | 33.6 ± 0.5 |
PMMA | 4 | 128.0 ± 1.3 | 100.5 ± 3.3 | 38.1 ± 0.6 |
PU | 1 | 102.1 ± 1.4 | 72.6 ± 1.7 | 30.2 ± 1.5 |
PU | 2 | 102.1 ± 1.8 | 72.2 ± 0.1 | 21.3 ± 1.5 |
PU | 3 | 101.1 ± 3.1 | 69.5 ± 5.1 | 30.2 ± 1.2 |
PU | 4 | 101.1 ± 1.9 | 73.4 ± 0.3 | 34.2 ± 0.4 |
It can be clearly seen from the Tables 1–3 that the effect of ITSCs on θA is concentration dependent. A statistically significant surface hydrophobicity increase (p < 0.05) was observed for concentrations of 100 and 500 μM compared to baseline, while no statistical significant change in θA was observed for the low ITSC concentration 10 μM. These results indicate the direct and active participation of ITSC in the BF phenomenon. The fact that the effect of the 100 μM and 500 μM concentration is within the same range suggests that the effect reaches a plateau. It is worth mentioning that this concentration-dependent behaviour resembles the effect on hydrophobicity observed during co-polymerisation processes, by either changing the concentration or the type of the film polymers,29,30 a fact that indicates the direct and active participation of ITSC in the BF phenomenon.
Furthermore, it is notable that even though PMMA and PU are hydrophilic polymers with an intrinsic contact angle lower than 90°, the films obtained in the presence of 100 and 500 μM of ITSCs exhibit angles around or above 100°, with the PMMA films reaching up to 129° in the presence of ITSC 1. Changes in the wettability of the surfaces have been presented in the literature associated with different mechanisms of preparation, the influence of air plasma on the surfaces, or ultraviolet ozone treatment of the surfaces.32–36 In our case, the observed change from hydrophilic to hydrophobic can only be due to the presence of the extended aromatic system of the ITSCs and the way it interacts with the polymer or even self-assembles during the film-preparation process. This is the first to our knowledge case in the literature where a change in the wettability of the surface occurs by the simple addition of a small organic molecule in the THF–polymer system.
The surface energy calculations showed high similarity between the PMMA and PU films. Overall, the surface energy in PMMA films was slightly lower than PU, which is in agreement with the values obtained for the water contact angles. This correlation is more clearly revealed at lower ITSC concentrations (Tables 4–6). This behaviour is consistent with the roughness values calculated for each film by AFM (Tables 4–6) as high roughness on polymer surfaces can lead to an increase of water contact angles due to the ‘lotus effect’.32 The “lotus effect”, initially studied by Cassie and Baxter,33 takes place when air pockets rest under the drop causing super-hydrophobicity by affecting the apparent contact angle at the boundary between the liquid and the solid surface.
Surface | Surface energy/mJ m−2 | Roughness (Ra) by AFM/nm | ||||
---|---|---|---|---|---|---|
Polymer | ITSC | γS− | γS+ | γLWS | γS | |
SW | None | 22.77 | 0.33 | 32.00 | 37.49 | 1.09 ± 0.10 |
PMMA | None | 5.54 | 0.04 | 39.50 | 40.43 | 20.33 ± 5.51 |
PU | None | 4.88 | 0.10 | 40.94 | 42.36 | 17.77 ± 2.68 |
PMMA | 1 | 2.87 | 0.57 | 39.78 | 42.33 | 31.73 ± 4.03 |
PMMA | 2 | 2.74 | 0.41 | 41.65 | 43.78 | 17.68 ± 7.89 |
PMMA | 3 | 4.06 | 0.54 | 40.30 | 43.27 | 26.25 ± 4.71 |
PMMA | 4 | 0.00 | 0.26 | 21.21 | 21.22 | 23.37 ± 0.99 |
PU | 1 | 4.30 | 0.66 | 43.54 | 46.92 | 30.77 ± 5.45 |
PU | 2 | 3.13 | 0.82 | 43.32 | 46.53 | 27.35 ± 3.65 |
PU | 3 | 6.48 | 0.59 | 43.98 | 47.90 | 29.45 ± 5.23 |
PU | 4 | 3.15 | 0.17 | 42.07 | 43.54 | 21.15 ± 1.91 |
Surface | Surface energy/mJ m−2 | Roughness (Ra) by AFM/nm | ||||
---|---|---|---|---|---|---|
Polymer | ITSC | γS− | γS+ | γLWS | γS | |
PMMA | 1 | 2.03 | 3.32 | 40.64 | 45.84 | 46.04 ± 2.15 |
PMMA | 2 | 1.16 | 2.14 | 39.01 | 42.17 | 31.47 ± 2.08 |
PMMA | 3 | 0.50 | 4.02 | 41.23 | 44.07 | 40.50 ± 3.47 |
PMMA | 4 | 0.62 | 1.72 | 38.73 | 40.80 | 31.76 ± 1.47 |
PU | 1 | 0.14 | 0.5 | 43.28 | 43.82 | 40.26 ± 4.04 |
PU | 2 | 0.24 | 0.48 | 43.38 | 44.06 | 37.53 ± 4.91 |
PU | 3 | 1.09 | 0.73 | 43.36 | 45.13 | 37.85 ± 2.47 |
PU | 4 | 0.26 | 0.32 | 42.73 | 43.30 | 35.74 ± 3.98 |
Surface | Surface energy/mJ m−2 | Roughness (Ra) by AFM/nm | ||||
---|---|---|---|---|---|---|
Polymer | ITSC | γS− | γS+ | γLWS | γS | |
PMMA | 1 | 0.45 | 3.78 | 39.79 | 42.41 | 43.97 ± 1.07 |
PMMA | 2 | 0.58 | 2.35 | 40.98 | 43.32 | 37.30 ± 7.05 |
PMMA | 3 | 0.93 | 2.78 | 42.65 | 45.87 | 35.23 ± 1.92 |
PMMA | 4 | 1.49 | 3.58 | 40.53 | 45.15 | 30.45 ± 0.49 |
PU | 1 | 0.08 | 0.53 | 44.13 | 44.54 | 38.23 ± 3.30 |
PU | 2 | 0.05 | 0.78 | 47.40 | 47.79 | 45.33 ± 2.30 |
PU | 3 | 0.05 | 0.29 | 44.15 | 44.39 | 40.55 ± 2.05 |
PU | 4 | 0.27 | 0.52 | 42.43 | 43.18 | 44.35 ± 0.78 |
The statistical test one-way and two-way ANOVAs, showed a significant effect of the added ITSCs on the surface roughness. Within the same polymer, the roughness increased when concentration increased from 10 μM to 100 μM with a less pronounced increase from the 100 μM to the 500 μM concentration. In the case of PMMA surfaces there is a distinct variability of surface roughness depending on the type of ITSC added while the PU surface roughness seems to be less drastically affected by the nature of the ITSC added. The roughness results agree with the high contact angle measurements obtained and the surface energies calculated providing additional evidence for the effect of the added ITSCs on the polymer film characteristics.
Fig. 2 AFM height images with 3D effect of PMMA and PU with ITSCs 1, 2, 3 and 4 at 10 μM. Images are 5 × 5 μm. |
Fig. 3 AFM height images with 3D effect of PMMA and PU with ITSCs 1, 2, 3 and 4 at 100 μM. Images are 5 × 5 μm. |
Fig. 4 AFM height images with 3D effect of PMMA and PU with ITSCs 1, 2, 3 and 4 at 500 μM. Images are 5 × 5 μm. |
The mean values and standard deviation of pore density for each surface at 10, 100 and 500 μM of each ITSC are shown in Fig. 5. These results agree with the high hydrophobicity of the films, as they show unequal surfaces providing space for air pockets.
Fig. 5 Pore density calculated for surfaces prepared of PMMA (a) or PU (b), and doped with ITSCs at 10, 100 and 500 μM. A control with no isatin derivatives was also used. |
As evidenced by the differences found in the surface film characteristics, the behaviour of the surface is affected to some extent by the presence of different isatin derivatives and the variety of concentrations used. The data obtained was subjected to statistical analysis that confirmed an interaction between the polymer nature and the isatin which directly affects the physical properties of the films. From the pore density values in Fig. 5 it is obvious that PMMA produce films of higher porosity. In both films increasing concentrations of ITSCs cause an upward trend in porosity confirming the catalytic effect of ITSCs on pore formation. Apparently, during the BF process, hydrophobic or π–π stacking interactions cause these molecules to self-assemble enhancing patterned honeycomb structure formation. The results of our previous work indicated that the presence of the amide –NH group is important in enhancing the BF phenomenon. It appears plausible that the –OCH3 or –NO2 substituent in position 5 of ITSCs 2, 3, and 4 may participate in intermolecular hydrogen bonding with the amide –NH group further enhancing and stabilizing the molecular networking. Even though, as showed by Bunz,34 the parameters which affect the final honeycomb structure are very diverse and the formation of breath figure arrays presents intricate thermodynamic, kinetic and entropic characteristic not completely understood, it is clearly shown in this work that the presence of the ITSCs is a determining factor for honeycomb structure formation.
Fig. 6 shows a great dependence of drug release on pH and the dissolution profiles present a discontinuous release as different process over all the pH areas of analysis in this studies. The average of dissolved drug per sections and the total amount released with their standard deviations can be found in Table 7. ITSCs are Schiff bases and pH alterations are anticipated to affect the degree of protonation/deprotonation of the molecules. At the low pH values of the study, it has been suggested that protonation takes place at the oxo group of the isatin five-membered ring.36 The basic character of ITSC 2 may be affected by the methoxy group mesomeric electron-donation effect which can be transferred through conjugation to the imine nitrogen of the five-membered indole ring. Since the increasing pH sectors seem to accumulate a correspondent increasing amount of ITSCs, the acidic properties of the molecule seem to dominate.
Fig. 6 Amount of ITSC 2 released from 2% w/v PMMA film over four specific pH sectors (6 h each) at room temperature. The initial concentration of ITSC 2 was 500 μM. |
pH range | Mass of dissolved ITSC 2/μg |
---|---|
End of sector 1 (pH 2.04) | 0.00 ± 0.00 |
End of sector 2 (pH 3.85) | 0.22 ± 0.86 |
End of sector 3 (pH 5.37) | 2.82 ± 1.72 |
End of sector 4 (pH 7.26) | 3.14 ± 0.98 |
Peak concentration (time) | 4.47 ± 0.97 (1428 min) |
An additional in vitro dissolution study was performed at pH 6.46 to confirm the release profile of ITSC 2. Fig. 7 presents the continuous release of drug, with a maximum dissolved mass of ∼6 μg, 10 h after the initiation of the experiment.
Fig. 7 Amount of ITSC 2 released from 2% w/v PMMA film over 24 h at room temperature. The initial concentration of ITSC 2 was 500 μM. |
The in vitro release studies demonstrate that the ITSC investigated does not remain in the polymer for a prolonged period of time, which could promote antibiotic resistance. Similar polymeric systems with extended release of antibiotics have been found to be problematic as lingering around at low (sub-minimum inhibitory concentration (MIC)) values, which can be a major issue in terms of promoting antibiotic resistance.
The same study was repeated with PU film though in this case the results did not show any release. Based on this data and the images from the AFM, it may also be suggested that due to the great difference in the pore diameter and pore density, the PU films did not have the optimum features needed such as high density of pores and smaller pore size to increase the surface available for the release of drug, to enable the drug to be released from the surface. Little work has been done in this area, however, the study carried out by Ponnusamy et al., gave some insight of the surface behaviour.37 They have determined that films formed by the BF method appeared to have a higher release profile than non-BF films. In addition, the drug dissolution was completed after 5 days, followed by the degradation of the surface.
Footnotes |
† Electronic supplementary information (ESI) available. See DOI: 10.1039/c6ra28163j |
‡ Equal contribution. |
This journal is © The Royal Society of Chemistry 2017 |