# New Collagen-Dextran-Zinc Oxide Composites for Wound Dressing

Authors: Georgeta Păunica-Panea; Anton Ficai; Minodora Maria Marin; Ștefania Marin; Mădălina Georgiana  Albu; Vlad Denis Constantin; Cristina Dinu-Pîrvu; Zina Vuluga; Mihai Cosmin  Corobea; Mihaela Violeta Ghica
Journal: Journal of Nanomaterials
 (2016)

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## Abstract

The goal of this paper was the design, development, and characterization of some new composites, based on collagen and dextran as natural polymers and zinc oxide as antimicrobial, to be used in wound healing. Collagen hydrogels with various concentrations of dextran and zinc oxide were investigated in terms of rheological analysis. The spongious composites, obtained by freeze-drying of hydrogels, were evaluated by morphology (SEM), water uptake, and biological (enzymatic biodegradation) analysis. All the results were strongly influenced by the nature and concentration of composite components. Based on the performances of the hydrogels, stationary rheometry, porous structure, morphology, and biological behavior, the antimicrobial spongious composite based on collagen and dextran with 50% ZnO were the most promising for future applications in wound dressing and a biomaterial with high potential in skin regeneration.


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## Body

## 1. Introduction

Wound healing is a significant problem for health-care systems worldwide, accounting over 1.5% of the world population [1]. The most affected by chronic wounds, as ulcers, are elderly and diabetic people. Moreover, an untreated or not correctly treated wound can lead to large area of necrosis and to systemic infection [2]. To avoid such complications, the best solution is the use of antibacterial biomaterials to treat or prevent infection of the tissues.Collagen is one of the most used polymers in biomaterials field, due to its excellent properties in biocompatibility, biodegradability, with well-established structure, biologic profile, andin vivo response [3]. It is a bioactive medical device used in different types of injuries (varicose ulcer, burns, wounds, opened surgery, etc.) as haemostatic and medical dressing [4]. Being a natural protein, collagen itself cannot heal the infected tissue because bacteria use it as a substrate [5–7]. Another natural polymer, dextran, a polysaccharide was proven to stimulate wound healing, control the proliferation of bacteria, and affect the metabolism of tumor cells, smooth muscle cells, and endothelial cells [8]. Dextran-based hydrogel containing chitosan microparticles loaded with growth factors [9] and silk fibroin nanofibrous materials with dextran [10] were also successfully used in wound healing, but some simpler solutions were not exploited yet.In order to induce antimicrobial activity, the polymeric scaffolds have to be more bioactive by decoration with antimicrobials like antifungals, antivirals, antiparasitics, or nonpharmaceutical (like essential oils). Zinc oxide (ZnO) was widely related to exhibit antimicrobial activity and higher stability than organic molecules [11, 12]. Also, it was used to accelerate the healing of both chronic and acute wounds [13] because of its epithelialization and bacteriostatic properties. ZnO represents today one of the most reliable choices in obtaining composites with potential applications in wounds care [14, 15].The aim of this study is to develop new simple solutions for wound dressings based on collagen and dextran. The scaffold was designed by using dextran for wound healing and ZnO for antimicrobial properties. The systems are prepared by lyophilization method in order to obtain efficient absorbent properties for wound dressings and porous structures. The composites in form of hydrogels were evaluated by rheological analysis and the spongious forms were investigated by water uptake, biodegradability in collagenase solution, and SEM.


## 2. Materials and Methods

### 2.1. Materials and Reagents

Type I fibrillar collagen gel having a concentration of 2.46% (w/w) was extracted from calf hide using the technology currently available at the Research-Development Textile Leather National Institute Division Leather and Footwear Research Institute—Collagen Department [3]. Dextran fromLeuconostoc spp. (Mw 15,000–25,000) was purchased from Fluka (USA) and zinc oxide nanopowder (<50 nm particle size) was from Sigma-Aldrich (USA). Sodium hydroxide and hydrochloric acid were of analytical grade. Type I collagenase obtained fromClostridium histolyticum was purchased from Sigma-Aldrich (Germany) and glutaraldehyde was from Merck (Germany).


### 2.2. Preparation of Composite Collagen Hydrogels

Dextran and zinc oxide in the concentration given in Table1 were added to initial collagen gel followed by adjusting collagen concentration at 1% and pH 7.4 and then cross-linked with 0.25% glutaraldehyde (related to collagen dry substance).Table 1
Codification and composition of composite collagen hydrogels.
Code of gels
Collagen, %
Dextran,  %∗
Zinc oxide, %∗∗
G1
1
0
0
G2
1
0
25
G3
1
0
50
G4
1
0
75
G5
1
5
0
G6
1
5
25
G7
1
5
50
G8
1
5
75
∗Related to gel volume; ∗∗Related to dry substance of collagen.The composite collagen hydrogels obtained, coded as G1–G8, were characterized by rheology and then conditioned by freeze-drying.


### 2.3. Rheological Analysis and Data Modeling

The stationary shear flow was carried out at 37°C using a rotational viscometer MultiVisc-Rheometer Fungilab. The measuring system was equipped with a standard spindle TR 9 and a ThermoHaake P5 Ultrathermostat to maintain the sample temperature at37±0.1°C during the experiment. The experimental conditions for rheological analysis were previously described [16]. Briefly, before each measurement, the hydrogel was mechanically equilibrated at the aforementioned temperature for about 10 minutes. The flow properties for collagen hydrogels with different concentrations of zinc oxide were assessed applying a rotational speed over the range from 0.3 to 60 rpm that corresponds to a shear rate between 0.1 and 20.4 s−1. The shear stress as a function of shear rate-up curves was obtained. The rheological data were analyzed applying different models: Bingham (1), Casson (2), Ostwald-de Waele (3), and Herschel-Bulkley (4) [16, 17], and the determination coefficients (R2) values were used as an indicator to select the one that best fitted the upward flow profiles:(1)τ=τ0+η·γ˙,(2)τ0.5=τ00.5+η0.5·γ˙0.5,(3)τ=K·γ˙n,(4)τ=τ0+K·γ˙n,where τ is shear stress (Pa), γ˙ is shear rate (s−1), η is plastic viscosity (Pa·s), τ0 is yield stress (Pa) related to the minimum stress to be applied for determining the start of hydrogel flow, K is consistency index (Pa·sn) associated with the hydrogel viscosity, and n is flow behavior index indicating the flow profiles [18–20].The Table Curve 2D software was used to evaluate theR2 values and rheological parameters specific for each model.


### 2.4. Preparation of Spongious Collagen Composites

All the composite hydrogels obtained were freeze-dried using a Delta 2–24 LSC lyophilizer (Martin Christ, Germany) and the lyophilization program previously described [21] and porous composites in spongious forms were obtained. The spongious samples were named M1 for the one obtained from G1, M2 for the one obtained from G2, and so on until M8.


### 2.5. Water Absorption

In order to determine the water absorption, the scaffolds were first immersed in water at 37°C. At scheduled time intervals, the samples were withdrawn and weighed. The water adsorption was calculated using the following equation:(5)water uptake=Wt-WdWdg/g,where Wt denotes the weight of the swollen samples at immersion time t and Wd denotes the weight of the dry samples (initial samples). All the samples were studied in triplicate.


### 2.6.In Vitro Degradation by Collagenase

In order to investigate the enzymatic degradation of collagen scaffolds, mass loss was monitored as function of exposure time to a collagenase solution. Pieces of 1 × 1 cm collagen composites were immersed in a collagenase solution and incubated at 37°C. At predetermined intervals, the swollen pieces were removed from the collagenase solution and weighed. The percent of degradation was calculated using the following equation:(6)%weight  loss=Wi-WtWt×100,where Wi is the initial weight and Wt is the weight of the samples after a time t. All the samples were studied in triplicate.


### 2.7. Scanning Electron Microscopy (SEM)

SEM analyses were performed on a HITACHI S2600N electron microscope, on samples covered with silver layer for each collagen composite.


## 2.1. Materials and Reagents

Type I fibrillar collagen gel having a concentration of 2.46% (w/w) was extracted from calf hide using the technology currently available at the Research-Development Textile Leather National Institute Division Leather and Footwear Research Institute—Collagen Department [3]. Dextran fromLeuconostoc spp. (Mw 15,000–25,000) was purchased from Fluka (USA) and zinc oxide nanopowder (<50 nm particle size) was from Sigma-Aldrich (USA). Sodium hydroxide and hydrochloric acid were of analytical grade. Type I collagenase obtained fromClostridium histolyticum was purchased from Sigma-Aldrich (Germany) and glutaraldehyde was from Merck (Germany).


## 2.2. Preparation of Composite Collagen Hydrogels

Dextran and zinc oxide in the concentration given in Table1 were added to initial collagen gel followed by adjusting collagen concentration at 1% and pH 7.4 and then cross-linked with 0.25% glutaraldehyde (related to collagen dry substance).Table 1
Codification and composition of composite collagen hydrogels.
Code of gels
Collagen, %
Dextran,  %∗
Zinc oxide, %∗∗
G1
1
0
0
G2
1
0
25
G3
1
0
50
G4
1
0
75
G5
1
5
0
G6
1
5
25
G7
1
5
50
G8
1
5
75
∗Related to gel volume; ∗∗Related to dry substance of collagen.The composite collagen hydrogels obtained, coded as G1–G8, were characterized by rheology and then conditioned by freeze-drying.


## 2.3. Rheological Analysis and Data Modeling

The stationary shear flow was carried out at 37°C using a rotational viscometer MultiVisc-Rheometer Fungilab. The measuring system was equipped with a standard spindle TR 9 and a ThermoHaake P5 Ultrathermostat to maintain the sample temperature at37±0.1°C during the experiment. The experimental conditions for rheological analysis were previously described [16]. Briefly, before each measurement, the hydrogel was mechanically equilibrated at the aforementioned temperature for about 10 minutes. The flow properties for collagen hydrogels with different concentrations of zinc oxide were assessed applying a rotational speed over the range from 0.3 to 60 rpm that corresponds to a shear rate between 0.1 and 20.4 s−1. The shear stress as a function of shear rate-up curves was obtained. The rheological data were analyzed applying different models: Bingham (1), Casson (2), Ostwald-de Waele (3), and Herschel-Bulkley (4) [16, 17], and the determination coefficients (R2) values were used as an indicator to select the one that best fitted the upward flow profiles:(1)τ=τ0+η·γ˙,(2)τ0.5=τ00.5+η0.5·γ˙0.5,(3)τ=K·γ˙n,(4)τ=τ0+K·γ˙n,where τ is shear stress (Pa), γ˙ is shear rate (s−1), η is plastic viscosity (Pa·s), τ0 is yield stress (Pa) related to the minimum stress to be applied for determining the start of hydrogel flow, K is consistency index (Pa·sn) associated with the hydrogel viscosity, and n is flow behavior index indicating the flow profiles [18–20].The Table Curve 2D software was used to evaluate theR2 values and rheological parameters specific for each model.


## 2.4. Preparation of Spongious Collagen Composites

All the composite hydrogels obtained were freeze-dried using a Delta 2–24 LSC lyophilizer (Martin Christ, Germany) and the lyophilization program previously described [21] and porous composites in spongious forms were obtained. The spongious samples were named M1 for the one obtained from G1, M2 for the one obtained from G2, and so on until M8.


## 2.5. Water Absorption

In order to determine the water absorption, the scaffolds were first immersed in water at 37°C. At scheduled time intervals, the samples were withdrawn and weighed. The water adsorption was calculated using the following equation:(5)water uptake=Wt-WdWdg/g,where Wt denotes the weight of the swollen samples at immersion time t and Wd denotes the weight of the dry samples (initial samples). All the samples were studied in triplicate.


## 2.6.In Vitro Degradation by Collagenase

In order to investigate the enzymatic degradation of collagen scaffolds, mass loss was monitored as function of exposure time to a collagenase solution. Pieces of 1 × 1 cm collagen composites were immersed in a collagenase solution and incubated at 37°C. At predetermined intervals, the swollen pieces were removed from the collagenase solution and weighed. The percent of degradation was calculated using the following equation:(6)%weight  loss=Wi-WtWt×100,where Wi is the initial weight and Wt is the weight of the samples after a time t. All the samples were studied in triplicate.


## 2.7. Scanning Electron Microscopy (SEM)

SEM analyses were performed on a HITACHI S2600N electron microscope, on samples covered with silver layer for each collagen composite.


## 3. Results and Discussion

The influence of ZnO concentration on upward flow curves plotted as shear stress as a function of shear rate for hydrogelsG1÷G4 is presented in Figure 1.Figure 1
The up flow curves for collagen hydrogels with different ZnO concentrations tested at 37°C.The upward rheograms presented in Figure1 indicated that the hydrogels G1÷G4 showed a non-Newtonian character, the shear stress increase with shear rate increase.Table2 summarizes the values obtained for determination coefficients by fitting the experimental data to various rheological models ((1)–(4)) described in Section 2.Table 2
The determination coefficients’ values for different rheological models tested at 37°C.
Rheological models/hydrogels
G1
G2
G3
G4
Casson
0.9832
0.9481
0.9418
0.9397
Bingham
0.9233
0.8432
0.8308
0.8168
Ostwald-de Waele
0.9838
0.9904
0.9913
0.9954
Herschel-Bulkley
0.9959
0.9936
0.9931
0.9976As can be seen from Table1, the Herschel-Bulkley model best fitted the rheological data shear stress as a function of shear rate.The dependence of ZnO concentration on the flow descriptors characteristic to Herschel-Bulkley model is given in Table2.The data presented in Table3 show that the hydrogels G1÷G4 exhibit a pseudoplastic behaviour with yield stress facilitating their flow and allowing their good manipulation [16, 22]. The values of flow index between 0.212 and 0.445 indicate a high degree of pseudoplasticity, especially for G2–G4. The presence of ZnO in formulation determined an increase of consistency index and yield stress, the highest values being recorded for the hydrogel containing a concentration of 75% ZnO related to collagen dry substance. The values of the aforesaid descriptors increase with ZnO concentration, more obvious for the hydrogels with 25% and 50% concentration. Thus, the presence of a lower concentration of ZnO (G2) determined the doubling of yield stress value and also a marked increase of consistency index value (about 4.24 times) compared to sample G1. Moreover, the doubling of ZnO concentration from 25% to 50% determined a more important increase of the rheological parameters for G3 related to G2 (40% for yield stress and 38% for consistency index) compared to G4 related to G3, increase from 50% to 75%, respectively (21% for yield stress and 38% for consistency index).Table 3
Herschel-Bulkley model fitting parameters for collagen hydrogels with different concentrations of ZnO.
Rheological parameters/hydrogels
G1
G2
G3
G4
Yield stress (Pa)
4.707
9.704
13.559
16.406
Consistency index (Pa·sn)
5.251
22.282
30.920
33.787
Flow index
0.445
0.287
0.218
0.212Similar patterns as recorded forG1÷G4 were obtained for the hydrogels G5÷G8 with dextran, the flow curves being also described by the Herschel-Bulkley model. The addition of dextran in formulations does not significantly modify rheological parameters specific to the above model for collagen-zinc oxide hydrogels.The results of the rheological analysis showed that the concentration of zinc oxide is the main factor influencing the flow properties of the designed hydrogels. Thus, beside the own pharmacological effect, zinc oxide concentration significantly affects the flow parameters.TheG1÷G8 hydrogels were freeze-dried and spongious collagen composites (M1÷M8) were obtained and characterized by water absorption, enzymatic degradation, and morphology by SEM.The water uptake capacity is a very important property for an ideal wound dressing in order to maintain a moist environment and to keep the excessive exudates. Figure2 presents the water absorption after 4 hours and 2 days for the collagen composites obtained.Figure 2
Water uptake for collagen composites.The control sample based on cross-linked collagen, M1, had higher water uptake capacity, compared to the ones which contain dextran or zinc oxide. The water uptake decreased as zinc oxide concentration increases from 25% to 75% (to collagen content). This behavior could be due to the presence of an increased concentration of zinc oxide which favors a more dense composite structure. The addition of dextran to the samplesM1÷M4 decreases the water uptake capacity.The results were confirmed also by SEM images (Figure3) which showed the compositional involvement on the spongious composites morphology. According to SEM observations all the scaffolds formed a three-dimensional (3D) porous structure. The pores inside the scaffolds were interconnected and varied in a large range, depending on zinc oxide and dextran content. For M1 (reference sample) the associated morphology (Figure 3(a)) of the structure suggests pore sizes between 80 and 270 μm, along with the increase of zinc oxide concentration the size of pores decrease to 55–105 μm (Figure 3(b)). Moreover ZnO particles could be clearly seen on collagen fibrils on SEM images. Dextran induced a more homogeneous phase appearance, with smaller pores, with sizes between 48 and 75 μm (Figure 3(c)). From Figure 3(d) it can be seen that pores forms were more uniform in the presence of dextran and ZnO nanoparticles adhered on collagen fibrils (Figures 3(d) and 3(e)).Figure 3
SEM images of collagen composites: (a) M1 (×200); (b) M4 (×200); (c) M5 (×200); (d) M7 (×500); and (e) M7 (×50000).
(a)
(b)
(c)
(d)
(e)Both the zinc oxide and the dextran affected the final porous structures of the scaffolds. Materials obtained from collagen hydrogel composites with dextran presented a more “compact” structure and the pore diameter was much smaller compared to the neat collagen ones.In vitro biodegradation of collagen composites by collagenase solution was assessed to simulate thein vivo behavior of composites used as wound dressings. High degradation rates were registered (Figure 4) for collagen samples without zinc oxide: over 50% after 4 hours and totally after 2 days.Figure 4
In vitro enzymatic degradation of collagen composites.The dextran content increased the resistance to collagenase and zinc oxide improved the overall stability of the samples. The relative collagen degradation content decreased for samples with 25% and 50% ZnO. When large amounts of ZnO (75%) were used, the enzymatic degradation slightly increases compared with 50% ZnO sample. The same tendency related to composition was observed also for the collagen dextran systems. These results can be explained by the higher amount of minerals which leads to a lower homogenous composite phase; therefore the collagen network can be more exposed to the enzymatic degradation (i.e., on the outer shell of the inorganic particles). Among the composites studied, the most stable ones at both 4 hours and 2 days were the one with collagen, dextran, and 50% ZnO. Moreover, taking into account the flow analysis for the corresponding hydrogels, the use of ZnO concentration higher than 50% was not justified since it does not lead to a marked increase of the rheological parameters and to a higher stability for the porous composites degradation. Considering the wound healing application, the effectiveness of the composite depends on the decreasing collagen rapid degradability profile for prolonged treatment and healing efficiency.


## 4. Conclusions

ZnO particles increased the pseudoplastic behavior of the composites based on collagen in solution phase. Dextran presence did not significantly influence the rheological profiles of the hydrogels. ZnO particles increased the consistency indexes and reduced the flow indexes of solution phases. The flow parameters indicated the Herschel-Bulkley model for better describing the rheological behavior.Water uptake ability for the hydrogel composites with dextran and collagen was lower, in comparison with neat collagen ones. ZnO particles were able to reduce the water uptake for both collagen and collagen/dextran matrixes.SEM morphology indicated the decrease of pore sizes and an increase in uniformity when ZnO was used. The inorganic particles were found in a dispersed state decorating the collagen and collagen/dextran fibrils.Using ZnO particles thein vitro degradation profile of the composites can be adjusted by increasing the length of the degradation process (enzymatic assisted). The biodegradability of the composites can be tailored by both dextran and ZnO particles. But large amounts of ZnO particles (75%) can lead to disruption of the composite phase distribution by exposing more collagen to the enzymatic process.Based on the performances of the hydrogels stationary rheometry and of porous structures morphological and biological investigations, the antimicrobial spongious composite based on collagen and dextran with 50% ZnO could be selected for applications to patient wounds, being a promising biomaterial in skin regeneration.



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