Extraction and antibacterial evaluation of marine AMPs against diabetic wound pathogens

Purchase of wound healing mesh materials and marine fish (Carangoides praeustus)

The present research work was carried out in the Department of Microbiology, Annamalai University, Chidambaram, Tamil Nadu, India. The work was done during the period of November 2019 to February 2020. C. malabaricus (paarai) fish was purchased from the local fish market at Chidambaram, Tamil Nadu, India. Nonadhering wound dressing material was used in the study. In Table 1, the sample material designation and the product description are mentioned. PVA used as carrier was purchased from chemical suppliers (Hi Media, India)

Extraction of AMPs from C. praeustus

Carangoides malabaricus fish procured from the fish market was processed for the extraction of AMPs using the procedure described by Nieto Lozano et al. (2012) (Fig. 1). The fishes were cut into pieces and the tissues were collected in a sterile container. About 100 g of tissues were mixed with 10% acetic acid and homogenized for 1 hour in a homogenizer. The homogenized tissue mixtures were centrifuged at 10,000 rpm for 20 minutes at 4°C. The supernatants were collected and equal volumes of acetone was mixed and centrifuged at 5,000 rpm for 10 minutes at 4°C. Supernatant containing AMPs were purified using standard ammonium sulfate precipitation and dialysis process. AMPs as protein precipitates were collected finally and stored at 4°C.

Antibacterial activity of AMPs

To determine the effective concentration of AMPs for coating the wound dressing mesh materials, antibacterial activity of four different concentrations (1X–10, 2X–20, 3X–30 and 4X–40 μg/ml) were tested against the test organisms (Escherichia coli, Klebsiella pneumoniae, Acinetobacter baumannii, S. aureus, and P. aeruginosa) (Sasmita et al., 2018).

Selection of AMP concentrations based on the antibacterial activity was carried out using modified Kirby–Bauer test method – Agar well diffusion method. Briefly, sterile Muller–Hinton agar plates were prepared. The plates were allowed to solidify for 5 minutes and 0.1-ml inoculum suspension of test bacteria were swabbed uniformly on the agar surface separately. After swabbing the cultures, four 6-mm wells were punctured on the agar surface using a sterile well borer for the addition of four different concentrations. All the plates after inoculation and addition of AMP concentrations were incubated at 37°C for 24 hours. The antibacterial activity of each concentration against the test bacteria was evaluated based on the inhibitory zones around the well. Experiments were carried out in triplicates and antibacterial activity was expressed in standard deviation values using the Statistical Package for Social Sciences (SPSS 9 for Windows 7.0) software.

Figure 1. Selection of C. malabaricus fish for extraction of AMP. [Click here to view]

Table 1. Details of wound dressing material. [Click here to view]

Coating wound dressing materials with AMPs + PVA

Antibacterial coating of wound healing mesh material using the AMPs was done by a standard two dip-coating technique (Gollwitzer et al., 2003). The technique started with the preparation of stable slurry with a specific amount (5 g) of AMPs in the molten polyethylene glycol (PEG). PEG (5 g) with a predefined molecular weight was mixed with AMPs (10 ml of purified fractions of AMPs) in a glass vial. The mixture was heated at the range of 60°C–70°C in a water bath to obtain homogeneous slurry. The resulting slurry was homogenized in a magnetic stirrer for 5–10 minutes. The wound healing mesh disk was cut (10 mm) using sterile devices and dip-coated twice with intermittent drying (suspension coating method).

The dip-coating procedure was carried out in sterile glass beakers on a shaker (120 rpm) for 30 minutes, with a drying period of about 15 minutes between the two coating procedures, followed by drying at room temperature. All the coating steps were carried out under strict aseptic conditions. After the coating procedure, the materials were stored at 4°C for up to 15 minutes. In order to increase antimicrobial drug loading and prevent excessive increase in material thickness, the coating process were repeated for replicates of each sample. Subsequently, in order to slow down the release rate of antimicrobial drug from PEG coating and mitigate the friction effect between material surfaces, a second coating layer was formed using PVA. PVA (drug carrier) was dissolved in DMSO to acquire a 10% (w/w) solution. PEG-coated materials were submerged into PVA solution three times for 1 minute each. The coated materials were left to dry on a clean bench for 24–48 hours at room temperature to remove residual DMSO, followed by determining the antimicrobial activity.

Qualitative antibacterial activity of AMPs + PVA-coated materials

AMP-coated wound dressing materials were subjected to evaluate the qualitative antibacterial activity against the test organisms individually (El-Rehewy et al., 2009). The standard disk diffusion method was used in the research to evaluate the antibacterial activity. Briefly, Mueller–Hinton agar (MHA) plates were prepared by pouring 15 ml of media into sterile Petri dishes. The plates were allowed to solidify for 5 minutes and 0.1-ml inoculum was swabbed uniformly and allowed to dry for 60 seconds. Premeasured disk-shaped (20 mm in diameter) AMP-coated wound dressing materials were placed on the MHA plates (seeded with bacterial inoculum). The disk was gently pressed to attach on the agar surface using sterile conditions. A plain mesh without AMPs was also kept in the plate as control. All the plates were incubated at 37ºC for 24–48 hours. At the end of incubation, the zone of inhibition formed around each material was measured in millimeter. Experiments were carried out in triplicates and antibacterial activity was expressed in standard deviation values using SPSS 9 (for Windows 7.0) software.

Determining the release concentration of AMPs from coated materials

The release of AMPs from the coated wound dress materials was studied using a standard in vitro drug release analysis (modified method of Mashru and Saikumar, 2010). The sample material was coated using the method described in previous section (Gollwitzer et al., 2003). Drug release was studied in 100-ml phosphate buffer (pH 6.8). The apparatus setup was made using a 250-ml glass beaker placed on a magnetic stirrer. A magnetic bead washed well was used for the experiment. The stirring condition was kept constant at 150 rpm. The release profiles were evaluated spectrophotometrically using UV-VIS spectrophotometer. Absorbance was measured for 4 ml of the sample solution at 450-nm wave length against phosphate-buffered saline as a blank. A fresh medium of the same volume was replaced each time after measuring absorbance. The drug release profile of coated wound dressing material was studied during the time period (0.5, 1, 2, 4, 8, 12, 24, 48, 72, 96, and 120 hours) using a standard calibration curve.

Assessing the biocompatibility of AMPs + PVA-coated materials

3-(4,5-Dimethylthiazol-2-yl)-2,5-diphenyltetrazolium bromide (MTT) assay was used to assess the biocompatibility of AMPs + PVA-coated wound dressing materials (Budman et al., 2012). L₉₂₉ fibroblast cell lines were cultivated in 12-well microtitre plates to reach a confluent cell growth. The samples were applied directly to the developed fibroblast monolayer. Before cell seeding, the specimens were pre-wetted in 70% aqueous ethanol solution for 48 hours; rinsed twice with ultrapure water, and immersed in 1-ml DMEM fibroblast medium in 24-well plates for 2 hours in an incubator at 37°C. The specimens were then seeded with L₉₂₉ fibroblast cell line at 10,000 cells per well according to the routine cell-culture methods. The plates were incubated at 37°C and 5% CO₂ for 15 days. The effect of AMPs on fibroblast viability was evaluated using the photometric MTT assay. At each time point, samples were taken from the 24-well plates and transferred into new plates for the MTT study. About 1 ml of MTT solution was added to each well and the plates were incubated for 3 hours. All the wells were rinsed and desorbed in 100 μl of 70% isopropanol for the formation of purple crystals. The plates were agitated rapidly at 400 rpm for 40 minutes and the purple crystal dyed solution was transferred to a 96-well microtitre plate and read at 550 nm. The viability is expressed as a percentage of the control sample (100%).

Antibacterial activity of AMPs

To determine the effective AMP concentration for coating the wound dressing mesh materials, antibacterial activity of four different concentrations were tested against the test organisms. During the analysis, the higher concentrations (4X strength–40 μg/ml) expressed more inhibitory zones against all test organisms than the other lower concentrations. 1X concentration did not inhibit any of the test organisms during the analysis. In Figure 2, the difference in size of inhibitory zones among all the concentrations was clearly presented. In Table 2, the inhibitory zones measured in millimeter also supported the above results in the images. Among the test organisms, E. coli and K. pneumoniae exhibited inhibitory zones of 12.6 ± 1.08, 16.2 ± 1.08, and 22.6 ± 1.04 mm and 10.2 ± 0.57, 12.6 ± 1.04, and 18.3 ± 0.86 mm for 2X, 3X, and 4X concentrates, respectively. Enterobacter sp. and S. aureus exhibited inhibitory zones of 11.1 ± 1.04, 12.5 ± 0.86, and 19.2 ± 0.76 mm and 10.1 ± 1.25, 11.6 ± 0.29, and 20.1 ± 1.6 mm against their respective 2X, 3X, and 4X concentrates. S. epidermidis showed 11.6 ± 1.04, 16.2 ± 0.57, and 18.5 ± 0.5 mm of inhibitory zones against the respective concentrates.

Figure 2. Antibacterial activity of AMPs. 1X−10 μg/ml, 2X−20 μg/ml, 3X−30 μg/ml, and 4X−40 μg/ml. [Click here to view]

Table 2. Selection of AMP concentration based on the antibacterial activity of AMPs. < [Click here to view]

Table 3. Qualitative antibacterial activity of AMPs + PVA-coated materials [Click here to view]

Figure 3. Qualitative antibacterial activity of the AMPs + PVA-coated wound dressing mesh samples. UC = Uncoated (bare wound dressing mesh without PVA and AMPs); C = AMPs + PVA-coated wound dressing mesh. [Click here to view]

Qualitative antibacterial activity of AMPs + PVA-coated materials

AMPs and their concentrations selected earlier were coated onto wound dressing meshes and its antibacterial potential was evaluated under in vitro conditions. Antibacterial activity was determined using the diffusing ability of the coated wound dressing samples and control samples on MHA plates. During the analysis, the zone of inhibition measured in millimeters for coated and uncoated mesh (bare material without PVA and AMPs) was calculated to obtain the mean value (tested in triplicates). In Table 3 and Figure 3, the difference in size of inhibitory zones for coated mesh and control was presented.

The most significant test organisms E. coli and S. aureus were observed to be highly susceptible to the AMPs + PVA combination. E. coli and S. aureus exhibited inhibitory zones of 33.1 ± 2.31 mm and 32.3 ± 1.04 mm for the coated mesh samples, respectively. K. pneumoniae and P. aeruginosa exhibited the inhibitory zones of 27.6 ± 1.04 mm and 30.1 ± 2.51 mm against their respective coated samples. A. baumannii showed significantly 31.1 ± 1.73 mm of inhibitory zones for the test samples.

From the obtained results it was noted that AMPs + PVA-coated wound dressing mesh samples exhibited significant antibacterial activity against all the test organisms. It was mainly due to the antibacterial potential of the carrier (PVA) natively. The obtained results revealed that the carriers increase the therapeutic effect of AMPs resulting in greater inhibitory zones against the test organisms. The mode of action of PVA on the bacterial cell wall that emphasizes its antibacterial activity was reported. PVA has the ability to penetrate the surface of the bacterial pyramidal wall so that they can disassemble and prevent bacteria from forming a biofilm consequently (Salman et al., 2014). Santiago-Morales et al. (2016) also explained the mode of action of PVA. The antibacterial activity of PVA was attributed to the chelation of the divalent cations and destabilization of the peptidoglycan layer of bacteria.

The antibacterial activity aided by PVA, with antibacterial drugs surveyed from the literature, was found to be supportive with the results of the present research. Salman et al. (2014) studied the antibacterial and anti-adhesive effect of PVA and PVA/Biosufactant mixture against pathogenic bacteria. The study revealed that there is high overlap between PVA and biosurfactant molecules which improve antibacterial activity than each one separately. In another study, Santiago-Morales et al. (2016) studied the antimicrobial activity of poly(vinyl alcohol) and poly(acrylic acid) electrospun nanofibers. The antimicrobial effect was assessed using strains of E. coli and S. aureus. Membranes containing >35 wt% PVA displayed significant antibacterial activity, which was particularly high for the gram-positive S. aureus.

Figure 4. Determining the release concentration of AMPs from coated materials. Graph output software: ORIGIN PRO 8.6 version. [Click here to view]

Table 4. Biocompatibility of the coated materials – cell viability test. [Click here to view]

Determining the release concentration of AMPs from coated materials

An in-vitro release study was conducted on developed AMPS + PVA-coated wound dressing mesh samples. The release concentration of AMPs in PBS at a specific temperature was determined. The release study was conducted for 120 hours in PBS at 37°C. Mesh materials coated with AMPs when released from crystalline AMPS + PVA mixture indicated that the rate of drug release was exponentially related to the release time (Fig. 4). The lag phase exhibited initial burst effect from 0.5 to 4 hours (35, 35, 35, and 45 μg). Followed this lag phase, an increase in drug concentration was observed from 8 to 24 hours (70, 80, and 85 μg). In PBS at pH 7.0, the hydrophilic polymer, PVA undergoes degradation during the log phase. Due to the rate of polymer degradation, the release of drugs was facilitated at higher rate than the initial burst level concentration. During this phase, the release concentration of AMPs remained almost constant (100, 100, 110, and 120 μg) from 48 to 120 hours, indicating the sustained rate of drugs from the coated mesh samples.

The rate of degradation of the PVA in PBS will influence the wound healing process at the critical wound site. PVA is a hydrophilic polymer and its solubility in water increases greatly as the degree of the acetate group hydrolysis increases. The use of PVA as a polymer in the present research offers the possibility to place hydrophilic drugs on the surfaces of hydrophobic wound dressing materials. This slow-release drug delivery system containing AMP + PVA mixtures from mesh surface could be a promising process for vascular wound healing in the later stages (Puranik et al., 2013). Hence, PVA can be used for releasing the drugs from biological and medical materials in a controlled way (Kenawy et al., 2007).

Assessing the biocompatibility of AMPs + PVA-coated materials

The biocompatibility of the wound dressing mesh is to be ensured for the patients’ safety before being used at the targeted wound site. Therefore, the biocompatibility of AMPs + PVA-coated mesh samples was evaluated by cytotoxicity assay (MTT assay). This method has an advantage over in vivo animal studies and other in vitro cell line studies. This method is very sensitive and accurate to prove the biocompatibility of any surface modified medical products. AMPs + PVA-coated mesh samples did not reduce the cell viability and cell count of fibroblast cells during the study period of up to 24 hours. The cell morphology, viability, and numbers were compared with control samples simultaneously. The results are described in Table 4 separately for each selected concentration of AMPs + PVA with the support of table values and graphical representations attributing for cell cytotoxicity and cell viability.

The mesh coated with selected concentrations (5, 15, and 25 μg/ml) of metabolites did not express any cytotoxic effects (Fig. 5). In support of this, an increase in cell viability with no significant difference in the morphology of the L₉₂₉ fibroblast cells was evident after 24 hours of cell culturing in the cell culture media when compared to control. The results revealed that the selected concentrations did not inhibit the growth of cells; thus indicating the biocompatibility of the AMP + PVA-coated wound dressing materials.

Figure 5. Biocompatibility of AMPs + PVA-coated wound dressing mesh. (Phase contrast microscopic analysis of L929 fibroblast cell line morphology.) [Click here to view]