Original Research ARTICLE
Manuka Honey and Zein Coatings Impart Bioactive Glass Bone Tissue Scaffolds Antibacterial Properties and Superior Mechanical Properties
- Department of Materials Science and Engineering, Institute of Biomaterials, University of Erlangen-Nuremberg, Erlangen, Germany
The combination of traditional herbal medicine (phytotherapeutic agents) with bioactive glasses is a promising strategy to generate advanced scaffolds for bone tissue engineering (BTE). An old remedy used for wound care since ancient times is honey. The antioxidant, antimicrobial and antibacterial properties of Manuka honey, in particular, make it an attractive substance for application in BTE scaffolds to prevent infections and biofilm formation. In this study 45S5 bioactive glass-based scaffolds produced via the foam replica technique were coated with corn protein zein and Manuka honey with two purposes: to improve the mechanical properties of the brittle scaffolds and to impart antibacterial properties. The morphology and chemical composition of the coated scaffolds were characterized with scanning electron microscopy and Fourier transform infrared spectroscopy, respectively, demonstrating the presence of Manuka honey in the coating. The release of the honey was quantified via ultraviolet-visible spectrophotometry; moreover, the antibacterial activity against Staphylococcus aureus was evaluated via colony-forming units counting, reduction of Alamar blue and turbidity measurements. Our findings suggest the effective combination of Manuka honey and bioactive glass, adding one more system to the novel family of bioactive glass scaffolds functionalized with phytotherapeutic agents.
One of the first approaches of humanity to heal wounds, tackle inflammation or other sources of pain was the use of natural remedies, more exactly herbal ingredients (Thakur et al., 2011). A wide range of knowledge on the healing effects of plants has been passed down through generations. Although today’s medical research is gaining renewed and increasing interest in the field of herbal medicine, the mechanisms of action of those so-called phytotherapeutics are still not completely elucidated. The multitude of different medical agents and therefore the wide range of biological effects of phytotherapeutics are making even more complicated to truly understand the detailed mechanism of healing (Schuhladen et al., 2019). However, research in the biomaterials field is increasing to exploit the advantages and the potential of herbal medicine, usually combining herbal or plant extracts with engineered biomaterials (Wang et al., 2018; Banerjee and Bose, 2019).
An interesting group of natural compounds under research are honeys. Honeys gain their antimicrobial properties to a large extent through conversion of ingredients in the pollen of the plant. Because of their antibacterial effect and ability to keep wounds moist and clean, to prevent them from becoming infected, honey has been used for wound care since ancient times (Mandal and Mandal, 2011). One specific type of honey, the Manuka honey (MH), is specifically interesting due to its wide range of antibacterial and anti-inflammatory effects (Speer et al., 2015; Almasaudi et al., 2016). The antibacterial effect makes this honey a promising natural remedy to prevent bacterial infection not only in wound care, but also on medical implants and in scaffolds for tissue regeneration. Infection is a major issue in orthopedics, since it can cause the integration of an implant to fail. Various strategies to prevent the colonization of bacteria on implant and scaffold surfaces are investigated, including coatings and incorporation of drugs for local release (Nooeaid et al., 2014; Cloutier et al., 2015; Mas-Moruno et al., 2019). The incorporation of herbal remedies like honey into medical implants and tissue scaffolds and the use of their interesting antibacterial abilities to help prevent infections, represent a promising and emerging field of research (Minden-Birkenmaier and Bowlin, 2018; Hixon et al., 2019; Schuhladen et al., 2020).
The monofloral MH, produced by bees in New Zealand and parts of Australia, derives from the flowers of certain Leptospermum species, commonly called manuka tree (Alvarez-Suarez et al., 2014; Carter et al., 2016). The antibacterial effect of most kinds of honey is related to hydrogen peroxide, phenolic components, low pH and high osmotic pressure. The increased antibacterial effect of MH results mainly from the existence of methylglyoxal. MH possesses a unique Manuka factor (UMF), which represents the level of methylglyoxal in the honey and has a documented direct effect on the honey antibacterial efficiency (Alvarez-Suarez et al., 2014).
Bone tissue engineering involves the use of porous scaffolds that can act as temporary templates in bone defects and are capable of supporting the regeneration of bone tissue (Porter et al., 2009; Amini et al., 2012). A promising material for biomedical applications is bioactive glass, discovered by Hench and coworkers in the late ’60 s (Hench et al., 1971). Bioactive glass (BG) of composition “45S5” (45 wt.% SiO2, 24.5 wt.% CaO, 24.5 wt.% Na2O, and 6.0 wt.% P2O5) has been continuously investigated in the last 50 years for applications as bone substituting material and, more recently, for bone tissue engineering (Chen et al., 2006; Jones, 2013). Today, many different compositions of bioactive glasses have been produced and tested successfully in vitro and in vivo (Jones, 2013; Balasubramanian et al., 2016; Kankare and Lindfors, 2016; Baino et al., 2018; Westhauser et al., 2019).
The great interest in bioactive glasses relates to their surface reactivity leading to their ability to support the formation of new tissue and regenerate defects, which has been documented not only in bone but also in soft tissues (e.g. wound healing) (Miguez-Pacheco et al., 2015). When aqueous solutions get in contact with bioactive glasses, a series of reactions occur on the surface of the material. The exchange of ions with the surrounding medium promotes the dissolution of the BG and the formation of calcium phosphate (or hydroxyapatite) precipitates on the surface, which allows a strong bond of the implants or scaffolds to the surrounding bone tissue by the stimulation of bone cell differentiation and proliferation thereby inducing the formation of new bone tissue (Filgueiras et al., 1993; Brauer, 2015; Boccaccini et al., 2016). Angiogenic effects of BGs have also been reported (Gorustovich et al., 2010), both in vitro and in vivo, which has confirmed the great potential of the material for tissue engineering.
Zein belongs to the family of prolamine proteins, a type of corn protein, which makes up to 50% of the whole protein amount in corn (Shukla and Cheryan, 2001). Due to its outstanding film-forming ability as well as biodegradability and biocompatibility, zein is currently used in food production and food packing as well as in the pharmaceutical field, e.g. as edible coating agent for medication, food supplements or sweets (Corradini et al., 2014). The biocompatibility and biodegradability of zein make it very interesting also for the biomedical field (Demir et al., 2017). Possible biomedical applications of zein include its use in tissue engineering, for example as electrospun nanofiber mats, coating of metallic implants, as well as a carrier system for drug delivery or encapsulation of micronutrients (Paliwal and Palakurthi, 2014; Meyer et al., 2018; Pedram Rad et al., 2018; Vogt et al., 2018; Mariotti et al., 2020).
To integrate drug delivery carriers and bone tissue engineering scaffolds, polymer coatings are a commonly utilized approach (Yao et al., 2013; Li et al., 2014; Philippart et al., 2014). In this study, 45S5 BG scaffolds were produced via the standard polymer foam replication technique (Chen et al., 2006). Manuka honey was used as an antibacterial agent incorporated in a biopolymer coating based on corn protein zein in order to investigate, for the first time, the combined effects of 45S5 BG and MH in a new scaffold type.
Materials and Methods
Three-dimensional BG-based scaffolds were produced by means of the well-known foam replica technique (Chen et al., 2006). To prepare the slurry, melt-derived 45S5 BG powder with a particle size of <4 µm (Vitryxx® Schott, Mainz, Germany), polyvinyl alcohol (PVA, fully hydrolyzed, Mw ∼ 30000 Merck Millipore, Darmstadt, Germany) as a binder and deionized water were used. Initially PVA was dissolved in deionized water at 80°C in a ratio of 0.01 mol/L, followed by 1 h magnetic stirring. The solution was left to cool down to room temperature. 45S5 BG powder was slowly added up to a concentration of 40 wt.% and the suspension was magnetically stirred for 1 h. The chosen sacrificial template was polyurethane (PU) foam of 45 ppi (Eurofoam Deutschland GmbH). The foams were initially cut with a cylindrical puncher and cleaned with acetone, afterwards they were coated twice by dipping them in the BG slurry and magnetically stirred for 1 min, finally the excess slurry was manually squeezed out and the specimens were left to dry overnight in a drying furnace at 60°C. Subsequently, the samples underwent a heat treatment in which the sacrificial template and organic components of the slurry were burned out and the sintering of the 45S5 BG structure occurred (Hum and Boccaccini, 2018). Initially the temperature was increased to 400°C and held for 1 h to burn out the PU foam. Afterwards, to complete the sintering process and the densification of the glass structure, the temperature was increased to 1050°C at 2°C/min and held for 2 h followed by natural cooling down in the furnace.
Coating with Biopolymer
10 wt% zein (Sigma Aldrich, Munich, Germany) was slowly added into an 80 vol% ethanol-solution under stirring conditions at room temperature for 30–60 min to allow the zein to dissolve, afterwards 10 and 20 wt.% Manuka honey (TranzAlpineHoney® NZ) with a methylglyoxal (MGO) content of >400 mg/kg was added and the solution was further magnetically stirred for at least 5 h until a homogeneous solution was obtained. The coating of the BG scaffold was performed by dipping each scaffold for 3 min in the zein-MH solution, followed by the removal of the excess of solution by gently rolling and tapping the samples over tissue paper and final drying at room temperature.
Scanning Electron Microscopy (SEM)
A scanning electron microscope (Auriga, Carl-Zeiss, Jena, Germany) was used to evaluate the microstructure of the scaffolds and the quality of the coatings at an accelerating voltage of 1.5 kV and a working distance of ∼6 mm. Before SEM observation, samples were fixed with conductive silver paint and sputtered with gold (Quorum Q150T Turbo-Pumped Sputter Coater, Darmstadt, Germany).
The morphology of the scaffold, in particular the pore structure, was evaluated with a light microscope Stemi 508 (Carl Zeiss, Jena).
Calculation of Porosity
The porosity of the coated samples was calculated and compared to the porosity of the uncoated scaffolds. The porosity (P) was calculated by the gravimetric method using the bulk and apparent densities, as shown in Eqs 1, 2 (Chen and Boccaccini, 2006):
The compressive strength of cylindrical scaffolds of 8 mm height and 7 mm diameter (nominal dimensions) was evaluated by uniaxial compression strength tests using an electromechanical universal testing machine (Instron 3300 Floor Model, Instron® GmbH, Germany). Five replicas of each sample were compressed at a speed of 1 mm/min and a maximum applied force of 100 N.
Evaluation of Bioactivity
The in vitro acellular bioactivity of the scaffolds was evaluated by immersion in simulated body fluid (SBF) using the well-known protocol of Kokubo et al. (Kokubo and Takadama, 2006). Samples were placed in scratch-free polypropylene containers, with 50 ml of SBF in an orbital shaker at 90 rpm and 37°C. After different time points samples were removed, washed with ultrapure water and left to dry at room temperature. The formation of hydroxycarbonate apatite on the surface of the scaffolds was evaluated with SEM and Fourier transform infrared spectroscopy (FTIR), (IRAffinity-1S, Shimadzu Europa GmbH).
Manuka Honey Release Behavior
The concentration of MH released from the scaffolds was measured with a UV-Vis spectrophotometer (Specord® 40, Analytic Jena, Germany). The measurements were carried out at the characteristic absorbance peak of MH at 268 nm. Initially, a calibration curve with different concentrations of MH in phosphate-buffered saline (PBS) was obtained (1.25, 2.5, 5, 7.5, 10 mg/ml, 15 mg/ml and 20 mg/ml). Scaffolds were immersed in 2 ml of PBS and placed in an orbital shaker at 90 rpm and 37°C, 1 ml the solution was measured after different time points. The measurements were carried out in triplicate.
The antibacterial activity of the scaffolds was evaluated against Gram-positive bacteria S. aureus. The scaffolds were sterilized with UV light irradiation for 2 h. Bacteria colonies were incubated in 10 ml of Luria/Miller medium (LB medium; Carl Roth, Germany) for 24 h at 37°C. 106-107 bacteria in 2 ml medium were added in each well-plate and incubated with the scaffolds for up to 8 h at 120 rpm and 37°C. To evaluate the metabolic activity of bacteria, Alamar blue (Invitrogen, United States) was added after 8 h and incubated according to the manufacture’s protocol, subsequently absorbance measurements at 570 and 600 nm were performed and the reduction of Alamar blue was calculated. Additionally, the viability of incubated bacteria in contact with the samples was assessed at different time points using solid agar plates (LB Agar; Carl Roth, Germany). After each incubation time, 100 μl of supernatant was plated onto the agar plate and the growth of bacteria was observed after 24 h incubation at 37°C. Turbidity measurements were carried out measuring the optical density at 600 nm using a photometer (Thermo Scientific GENESYS 30, Germany). Samples of bacteria without scaffolds were used as control. The experiments were carried out in triplicate.
Production of Scaffolds and Coating
The microstructure of the scaffolds was studied by both SEM and optical microscopy. Highly porous BG scaffolds were obtained. Figures 1A,B shows the typical interconnected porous structure of the scaffolds at two magnifications, showing a structure similar to cancellous bone, typical of scaffolds obtained by the replica method (Chen et al., 2006).
Figure 2 depicts different coatings on BG scaffolds. Initially, a coating consisting only of zein was obtained, as can be observed in Figures 2A,B, the coating covered well the surface of the scaffold, and only a few pores were seen to be blocked with zein. Additional cracks and nanopores were also observed. When MH is incorporated into the coating solution, it can be detected in the scaffold as the black or dark gray spots and lines shown in the SEM pictures (Figures 2C–F). Two concentrations of MH were tested by incorporating 10 wt% and 20 wt% MH into the zein coating solutions. Even though the coating solution with MH was thicker compared to the zein solution, in terms of coating quality and blockage of pores, no significant difference was observed with increasing amount of MH.
FIGURE 2. SEM images of coated scaffolds: (A,B) zein coated scaffolds, (C–E) zein +10 wt.% MH scaffolds, (F) zein +20 wt.% MH scaffolds. MH can be identified in the coating as the black/dark areas.
The FTIR spectra of BG powder (sintered following the same procedure used for making the scaffolds), zein and MH are depicted in Figure 3. The absorbance spectra show peaks according to the vibrational bands of the materials. Sintered 45S5 BG shows prominent broad peaks in the regions 1150–960 cm−1 as well as 960–850 cm−1, which can be assigned to the vibrational bands of Si-O-Si asymmetric stretching vibration. Furthermore, a prominent peak at around 445 cm−1 can be attributed to the rocking Si-O-Si vibration (Aguiar et al., 2009). Smaller peaks at 730 and 696 cm−1 can be identified as symmetric stretching vibration of a Si-O-Si crystalline phase, indicating that the scaffold partly crystallizes during the sintering process, which is well-known from previous work (Chen et al., 2006). Peaks at around 620 and 524 cm−1 indicate the presence of crystalline phosphate since they can be assigned to bending vibrations of a crystalline phosphate phase (Filho et al., 1996), whereas the peak at 575 cm−1 can be identified as a vibrational band of amorphous P-O bending (Filho et al., 1996; Lefebvre et al., 2007; Chen et al., 2010; Adams et al., 2013). The FTIR spectrum of zein (Figure 3B) shows the characteristic vibrational bands for proteins, including a broad peak at 3290 cm−1 with a shoulder at about 3320 cm−1. This peak can be identified as the Amide A peak and is assigned to O-H and N-H stretching vibrations of amino acids. The spectrum also exhibits peaks at 3060 and 2930 cm−1 due to aromatic and aliphatic C-H stretching, respectively. The prominent peak at 1645 cm−1 represents the Amide I peak and can be attributed primarily to C=O (carbonyl) stretching vibrations (Forato et al., 1998). The Amide II peak at 1523 cm−1 contributes to N-H bending of the peptide backbone of the protein. Another small peak at 1238 cm−1 can be assigned to axial deformation of C-N bonds (Magoshi et al., 1992; Forato et al., 1998; Corradini et al., 2014). The spectrum of MH (Figure 3C) shows the characteristic peaks for carbohydrates since it mainly consists of hydrated glucose and fructose as well as some smaller amounts of more complex carbohydrates like saccharides. The peak at 3260 cm−1 corresponds to O-H stretching (H-bonded), the peak at 2930 cm−1 can be assigned to stretching of C-H groups (Corradini et al., 2014). Both peaks can also be seen in the zein spectrum. Furthermore, a peak at 1645 cm−1 can be attributed to O-H water bending. More peaks between 1,500 and 700 cm−1 correspond to characteristic vibration bands of carbohydrates (Svečnjak et al., 2011; Arslan et al., 2014; Head et al., 2015; Sabri and See, 2016).
FIGURE 3. FTIR spectra with characteristic vibrational bands of (A) sintered 45S5 BG powder, (B) zein, (C) MH and (D) coated scaffolds. (The relevant peaks are discussed in the text).
FTIR spectra of the coated scaffolds were analyzed to confirm the presence of MH in the coating. In Figure 3D The spectrum of zein coated BG scaffold shows characteristic zein peaks at 3290, 2930, 1645, and 1523 cm−1. Because zein and MH exhibit some common vibrational bands, the peaks overlap and cannot be specifically assigned. Nevertheless, the presence of MH in the coating can be identified in the larger and wider peak at 3260 cm−1 (O-H stretching), compared to the zein coated BG scaffold. Additionally, an increased peak at wavenumber 1026 cm−1 in the coated scaffold is attributed to MH, this absorption band is characteristic of carbohydrates (Svečnjak et al., 2011).
High porosity is particularly important for BTE applications since pores are needed not only for vascularization of the scaffold but also for cell attachment, differentiation and proliferation (Karageorgiou and Kaplan, 2005). Osteoblasts need to be able to penetrate the scaffold’s porosity and to attach on its surface. High porosity is also crucial for a suitable degradation of the scaffold, since a higher porosity results in a higher surface in contact with body fluids. Although scaffolds with lower porosities have successfully been used for bone tissue engineering, for highly porous scaffolds like the ones prepared by the foam replica method the desired porosity is over 90%, which is beneficial for bone regeneration (Chen et al., 2006). This very high porosity, on the other hand, leads to very low compression strength of the scaffolds (Philippart et al., 2014).
As can be seen in Table 1, uncoated BG scaffolds developed in this study showed a very high porosity of 95.6%. This porosity lays in a suitable range for bone tissue engineering scaffolds (Bose et al., 2012). The zein coating decreases the porosity of the scaffold in around 5%. The addition of 10 wt.% MH to the coating led to a decrease of porosity of around 8% when compared to the zein coated scaffolds. Similarly, for the 20 wt.% MH scaffolds the decrease of porosity was ∼5%. This reduction could be a consequence of the higher viscosity of the coating solution. The high content of MH makes the consistency of the coating gluier, making more difficult for the excessive coating solution to flow out of the scaffold, even with the help of compressed air.
Compressive strength tests were carried out to evaluate the potential use of the coated scaffolds in bone tissue engineering applications in terms of their robustness and structural integrity under loads. Figure 4 shows representative stress-strain curves for uncoated and coated BG scaffolds which can be divided into three different areas. In stage I, the overall stress increases up to a maximum value at which the thick and strong struts of the scaffold start to break. This leads to a decrease in compressive stress in area II. Eventually, in stage III, the stress rises again as the crushed scaffold gets compacted (Chen et al., 2006). The coating with zein and MH leads to an increase of the compressive strength of the scaffold in comparison to the uncoated one. Both curves are typical stress-strain curves for the compression of porous bioactive glass based structures (Philippart et al., 2014; Hum and Boccaccini, 2018). The jagged course of the curves originates from the porous structure and cracked surface of the thin struts. When the stress rises, struts start to break, leading to a temporary decrease of stress resulting in a characteristic jagged curve and a low compressive strength of 0.04 ± 0.01 MPa, value which is comparable to results reported in the literature for similar scaffold types (Li et al., 2015; Hum and Boccaccini, 2018). For the coated scaffold with MH and zein, the average maximum compressive strength notably increased to 0.14 ± 0.05 MPa. In the present investigation, the maximum compressive strength was estimated as the maximum stress applied before the densification of the scaffold took place, a concept that has been employed previously (Chen et al., 2006; Hum and Boccaccini, 2018).
The enhanced compressive strength of the coated scaffolds might be associated with the well-known reinforcement effect of the polymer infiltration into the cracks and open hollow struts of BG scaffolds (Philippart et al., 2014). Additionally, the properties of zein and MH can provide mechanical stability since zein has an extraordinary film-forming ability and can, therefore, form a smooth coating on the struts of the BG scaffold, closing microcracks and strengthening the brittle structure. As a possible disadvantage, when zein dries it can be hard and brittle. Consequently, plasticizers are used as an alternative to overcome the problem (Zhang et al., 2015). MH could act as a plasticizer for zein. Sugars like glucose and fructose, which make up the major component of honey, have been shown to reduce the stiffness and brittleness of zein films (Ghanbarzadeh et al., 2006; Ghanbarzadeh et al., 2007). Similarly, phenolic compounds in honey could act as plasticizers, as studies have shown (Arcan and Yemenicioglu, 2011), demonstrating that phenolic acids, gallic acid, p-hydroxybenzoic acid and ferulic acid, which are also present in MH, can improve the flexibility of zein films. Indeed, the work of fracture of the coated scaffolds is notably higher than that of the uncoated scaffolds, as can be inferred in a first qualitative approximation by the extension of the area under the stress-strain curve.
However, when comparing the present results to the compressive strength of human cancellous bone, there is still room for improvement. The mechanical strength of the coated BG scaffolds is located only at the lower limit of the compressive strength of cancellous bone which ranges from 0.1 - 16 MPa (Gerhardt and Boccaccini, 2010).
Evaluation of bioactivity
The formation of hydroxycarbonate apatite (HCA) on the surface of the scaffolds was investigated through SEM observations and FTIR analysis after immersion of the samples in SBF for different incubation times. Figure 5 depicts the surface changes of the coated scaffolds. After one day incubation, the coating already starts to degrade and flakes off in some areas of the scaffold, whereas some patches of coating remain on struts. Additionally, no dark dots of MH can be seen in the coating after one day of immersion. After three days in SBF, the coating is degraded further and eventually, the growth of apatite like structures on the surface increases significantly after seven days of immersion. Part of the coating is still visible and partially covered by calcium phosphate precipitates, which are qualitatively recognized by the cauliflower-like shape, as observed in Figure 5 (14 d SBF). As has been reported in the literature (Metze et al., 2013; Hum and Boccaccini, 2018), uncoated 45S5 BG scaffolds show the formation of apatite like structures already after just 1-day of immersion in SBF. Therefore the bioactive behavior of the scaffolds is slightly delayed by the zein coating.
FIGURE 5. SEM images at different magnifications of zein+MH coated BG scaffolds after immersion in SBF for 1, 3, 7, and 14 days.
HCA formation was confirmed using FTIR spectroscopy (Figure 6). After one day in SBF, the characteristic MH peak at 3620 cm−1 was not detected, therefore, wavenumbers in the range 2000–500 cm−1 are chosen for comparison since all important vibrational bands and peak changes are present in this range. After 7 days incubation, a peak at 575 cm−1 assigned to amorphous P-O bending is slightly shifted and increases at a wavenumber of 560 cm−1, indicating the formation of an amorphous calcium phosphate layer. Together with a peak growing at 600 cm−1 it forms a double peak assigned to the bending vibrations of phosphate groups. This double peak typically indicates the formation of hydroxyapatite since it is characteristic for an orthophosphate lattice. Another peak forms between 1130 and 975 cm−1 with a shoulder at 960 cm−1 indicating the formation of a phosphate enriched crystalline hydroxyapatite layer attributed to the stretching of PO4 groups (Koutsopoulos, 2002; Stanciu et al., 2007; Macon et al., 2015; Hum, 2016).
FIGURE 6. (A) FTIR spectra of zein + MH coated BG scaffolds before and after immersion in SBF, (B) pH values of SBF after immersion of zein +MH coated BG scaffolds.
Furthermore, a peak at wavenumber of 800 cm−1 can be assigned to the typical silica-rich layer on the scaffold surface (Cerruti et al., 2005). The pH of the SBF solution was measured after each incubation time. Figure 6B shows the fast increase of pH during the first days of immersion. After one week the pH has risen to nearly 7.7 and then it stays relatively stable at this value for the last two weeks of the test. This significant increase in pH is typical for bioactive glasses as the dissolving glass rapidly releases ions like sodium and calcium in exchange of protons from the surrounding SBF (Ciraldo et al., 2018). The higher ion concentration causes the increase in pH and favors the dissolution of the Si – O – Si bonds followed by the formation of HCA on the surface of the scaffold. Studies have shown that a higher alkaline pH (7.5 and 8.0) is an ideal environment for the formation of HCA (De Aza et al., 1996).
Release behavior of MH
The concentrations of MH released from the scaffolds in PBS were measured with a UV-Vis spectrometer after different time points. The measured values showed a surprisingly fast release of MH within the first hour of immersion in PBS. This result correlates with the SEM observations and FTIR spectra of the samples after immersion in SBF since after one day no MH was detected. As can be observed in Figure 7, after 1 h, MH concentration stays relatively constant, indicating that no significant further release was taking place. The concentration of MH in the PBS solution with a volume of 2 ml for each scaffold was about 5 mg/ml for the 10 wt.% and 7 mg/ml for the 20 wt.% MH coating. These values, however, are not very accurate as a great difference of MH concentration in PBS between the measured scaffolds can be seen.
Originally it was anticipated that zein would encapsulate MH and it was expected that a slow release of MH would occur, as it is the case for other types of drugs encapsulated in zein, like for instance oleic acid (Arcan and Yemenicioğlu, 2014). The fast release of MH is probably due to its good solubility in water and low encapsulation and distribution in the zein coating, therefore when water penetrates through pores in the zein coating MH is rapidly released.
The antibacterial activity of uncoated and coated scaffolds was assessed with S. aureus bacteria. The strongest antibacterial effect was observed for the coated scaffolds containing MH. The coating with 20 wt.% MH and zein showed significantly lower colony-forming units of bacteria compared to the other samples, as depicted in Figure 8B. Similarly, after 2 h incubation, the values of the optical density (turbidity measurements) were lower for MH containing scaffolds, followed by zein coated and uncoated BG scaffolds, as shown in Figure 8A. Furthermore, the viability of bacteria was assessed via the reduction of Alamar blue, in accordance with the results of optical density at 8 h, samples containing MH showed lower bacteria viability compared to the uncoated scaffolds and control sample with only S. aureus. Despite the fast release of MH, it was possible to obtain an antibacterial effect of the coatings.
FIGURE 8. Antibacterial behavior of uncoated and coated BG scaffolds. (A) Turbidity measurements. (B) Colony-forming units of S. aureus. (C) Reduction of Alamar blue after 8 h.
Representative pictures of the bacteria colony units in agar plates are shown in Figure 9. These plates correspond to 10−5 dilution for all tested samples. Therefore it is possible to directly compare the effect of each material on the bacterial growth. Significant differences can be observed between the MH containing scaffolds in which fewer or no bacteria colonies were counted compared to the control and the other samples. In the case of uncoated BG scaffolds, it was not possible to count the colonies since there was a joint of colonies instead of the individual ones observed in the other plates.
FIGURE 9. Agar plates after 8 h incubation of S. aureus with supernatants of the 10−5 dilution of each sample.
The combination of the biocompatibility and biodegradability of zein with the bioactive properties of BGs and the antibacterial effect of MH was shown to be an interesting approach to create multifunctional bone tissue engineering scaffolds. On the one hand, the zein coating containing MH covered the surface of the scaffolds without blocking pores or showing major cracks and irregularities. Moreover, MH was clearly recognized in the zein coating using scanning electron microscopy and FTIR spectroscopy. The coating successfully improved the mechanical properties of the porous and brittle bioactive glass scaffolds. Even if the improvement is still not enough to make the coated scaffolds useful for load-bearing applications, especially the handling of the scaffolds was notably facilitated by the coating and coated scaffolds were much tougher (less prompt to brittle fracture) than their uncoated counterparts.
Additionally, the bioactive behavior of the scaffolds was not inhibited by the coating, as the zein - MH coating starts to degrade relatively fast after immersion in SBF and hydroxycarbonate apatite begins to grow on the strut surfaces after 3 days of immersion, which should favor a fast bonding to the surrounding bone. MH was successfully released from the zein-coated scaffolds. However, some improvements are required, as the release of MH was considerably fast, likely due to MH’s good solubility in aqueous environments and poor solubility in the solution of zein in ethanol. Therefore, it is likely that in the present technology, MH was not sufficiently embedded in the zein coating, which led to a rapid MH release in less than 1 h. Consequently, no long-term antibacterial effect or activity against the formation of a biofilm on the scaffold can be expected, as MH diffuses quickly into the aqueous environment. Nevertheless, a superior antibacterial effect was observed for up to 8 h for the MH containing scaffolds. These results are in accordance with the recent literature, in which the antibacterial effect of MH in combination with BG particles and polymeric foams has been reported (Schuhladen et al., 2020). Further studies need to be carried out regarding the control of the release behavior of MH. Alternative strategies to encapsulate MH need to be analyzed in order to obtain a sustained release and therefore to open the possibility of achieving long-term antibacterial effect.
Data Availability Statement
The raw data supporting the conclusions of this article will be made available by the authors, without undue reservation.
MA-O conceived the initial idea with AB; MA-O, JW, and KL planned and carried out the experiments; MA-O wrote the first draft of the paper; MA-O, KL, and JW contributed to the analysis of the data; AB supervised the project, provided intellectual input and corrected the manuscript.
Conflict of Interest
The authors declare that the research was conducted in the absence of any commercial or financial relationships that could be construed as a potential conflict of interest.
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Keywords: bioactive glass (45S5), manuka honey, zein, polymer coating, antibacterial activity
Citation: Arango-Ospina M, Lasch K, Weidinger J and Boccaccini AR (2021) Manuka Honey and Zein Coatings Impart Bioactive Glass Bone Tissue Scaffolds Antibacterial Properties and Superior Mechanical Properties. Front. Mater. 7:610889. doi: 10.3389/fmats.2020.610889
Received: 27 September 2020; Accepted: 25 November 2020;
Published: 14 January 2021.
Edited by:Yadir Torres, Sevilla University, Spain
Reviewed by:Débora Coraça-Huber, Innsbruck Medical University, Austria
Lia Rimondini, University of Eastern Piedmont, Italy
Copyright © 2021 Arango-Ospina, Lasch, Weidinger and Boccaccini. This is an open-access article distributed under the terms of the Creative Commons Attribution License (CC BY). The use, distribution or reproduction in other forums is permitted, provided the original author(s) and the copyright owner(s) are credited and that the original publication in this journal is cited, in accordance with accepted academic practice. No use, distribution or reproduction is permitted which does not comply with these terms.
*Correspondence: Aldo R. Boccaccini, firstname.lastname@example.org