Bone tissue engineering aims to use biodegrade able scaffolds to replace damaged tissue. This scaffold must be gradually degraded and replaced by tissue as similar as possible to the original one. In this work a hybrid porous scaffold containing chitosan, polyvinyl alcohol and bioactive glass was successfully obtained and subsequently characterized by scanning electron microscopy. The scaffold presented satisfactory pore size range and open interconnected pores, which are essential for tissue ingrowth. A cytotoxicity assay showed that this biomaterial allows adequate cell viability, so that it was considered suitable for an in vivo experiment. Promising results were obtained with the implant of the scaffold in an experimental model of a New Zealand rabbit femur bone lesion. Clinical and biochemical parameters measured such as complete blood count, total serum proteins, albumin, alanine aminotransferase and aspartate aminotransferase were similar between animals in the control group at all time periods studied. Histological and histometric studies showed that the scaffold was coated with a cement-like substance, exhibiting many areas of mineralized structures. Very few osteocyte-like cells or lining-like cells were found inside the amorphous mineralized deposit. In vivo results allow us to consider this scaffold as a promising biomaterial to be applied in bone tissue engineering.
Synthetic three-dimensional scaffolds for application to the regeneration of bone tissue should present an architecture similar to bone extracellular matrix and provide a suitable microenvironment for cell adhesion, proliferation and differentiation, ensuring tissue growth [
Chitosan (Chi) can be considered as one of the most thoroughly investigated materials in recent years. The non-toxicity, high biocompatibility, and antigenicity of chitosan have driven its potential applications in biomedical field [
In other words, the polymer blend and cross-linked polymer system may present a different degradation behavior under physiological fluid conditions, where part of the polymer network may undergo fast solvation and another portion may experience slow degradation by depolymerization. Hence, chitosan joined to other polymers has opened a new line of research for altering or tailoring the property of interest. In previous works [
Mechanical strength of porous scaffolds are also crucial with respect to the regeneration of hard tissue such as bone, which must support a load and meet specific mechanical needs while stimulating bone regeneration. The most investigated approach to attain the desired levels of strength is the production of composites and hybrid systems [
In previous works [
We developed a model of bone lesion in a New Zealand rabbit femur, which does not resolve spontaneously, with the generation of a fibrous tissue that does not have the original characteristics of the tissue prior to the injury, in order to use it to consider the osteoregenerative potential characteristic of the scaffolds to be tested [
The present work investigates Ch/PVA containing 20% of bioactive glass (w/w), with a Ch:PVA mass ratio of 1:1. Pore size, morphological and in vitro cytotoxicity characteristics were evaluated to characterize these biomaterials. We also tested the biomaterial in an in vivo implant procedure in our experimetal model of New Zealand rabbit femur bone lesion, considering not only the implant tissues but also the post-surgical clinical and biochemical studies of the animals.
All reagents were supplied by Aldrich Chemical. Poly(vinyl alcohol) (PVA) solution 5.0% (w/v) was prepared by dissolving PVA (80% hydrolysis) in deionized water (100 mL) under mechanical stirring speed of 280rpm at 70˚C (±2˚C) for 45 minutes.
A solution of Chitosan (C) with high molecular weight and deacetylation (DD) > 75% (1% w/v) was prepared by dissolving 1 g commercial powder in 100 ml deionized water. 2 ml acetic acid was added to the solution, and then subjected to mechanical stirring for 24 hours. Bioactive glass 60 s precursor solution (BG) was obtained by acid hydrolysis and polycondensation of Tetraethylorthosilicate (TEOS-(Si(OC2H5)4)), alkoxide precursor of SiO2, and Triethylphosphate (TEP-((C2H5O)3PO)), alkoxide precursor P2O5. Hydrolysis occurred by adding deionized water and nitric acid as catalyst reagents. 85 g of Calcium Nitrate (Ca(NO3)2∙4H2O) was then added as a precursor of CaO. The nominal composition of the bioactive glass was the following: 60% SiO2, 36% CaO; 4% P2O5. Glutaraldehyde solution (2.0% w/v) was prepared by diluting 25% glutaraldehyde 2 ml in 23 ml deionized water.
The scaffolds were fabricated by mixing PVA solution with Chitosan solution with a CHI to PVA ratio of 1:1, as shown in
The resulting solution was poured into 7 ml vials with a syringe and kept at room temperature for 72 hours, the time required for gelation to occur. The vials
Scaffold CHI:PVA ratio | Composition (%) | |||
---|---|---|---|---|
Chitosan | PVA | VB | Glutaraldehyde* | |
1:1 | 40 | 40 | 20 | 3 |
*In relation to polymers mass.
were kept tightly closed during gelation and then frozen for 72 hours in a refrigerator at −20˚C. The frozen vials were immersed in liquid nitrogen for 20 minutes and then placed in the lyophilizer (Model: K105-Company Liotop-SP/Brazil) for 48 h with −98˚C condenser temperature and −4˚C sample collector temperature. The pressure in the collector was 30 mmHg.
Scanning Electron Microscopy (SEM) FEI-Inspect-S50/Czech Republic was used for scaffold characterization. Previously, samples were frozen by liquid nitrogen immersion and fractured in order to obtain the internal fracture surface for analysis. This surface was coated with gold.
The cyxotoxicity assay aims to detect the potential of a material or device to produce lethal or sublethal effects on biological systems at the cell level. The release of toxic subproducts of the biomaterial can damage the cells or reduce the rate of cell culture growth. A biomaterial can be considered toxic for use in a biological system when it shows under 50% of cell viability compared to the positive control. Formazan crystals were solubilized and optical density was determined by a spectrophotometer at 595 nm. Primary culture of human fibroblasts at the fourth passage was plated in 24-well plates at a density of 1 × 104 cells/well. Cell populations were normalized with DMEM for 24 hours, after which time the medium was changed and the samples were placed into wells. The cylindrical samples were sliced into four equal parts, sterilized by irradiation at 15 kGy for 30 minutes, and then soaked in saline solution (PBS) for 24 hours. DMEM was used as an experiment positive control and PBS 10× as a negative control. All assays were performed in triplicate (n = 3). Cells were incubated at 37˚C in a 5% CO2 humidified atmosphere for 72 hours. At the end of the incubation period, the culture medium was removed and discarded and 210 µL/well of DMEM was added. Then 170 µL/well of MTT solution (Invitrogen) (5 mg/ml) was added and the plate was incubated at 37˚C in a 5% CO2 humidified atmosphere for 2 hours. The cells were observed under an optical microscope (MO) to display the formazan crystals that were solubilized by the addition of 210 µL/well of a solution of SDS 10%-HCl (0.01 M hydrochloric acid―10% of sodium dodecyl sulfate water) followed by incubation at 37˚C in a 5% CO2 humidified atmosphere for 18 hours. 100 µL was transferred from each well to a 96-well plate, in triplicate, and optical density was measured in a spectrophotometer at 595 nm. All the steps were performed in minimuml lighting conditions. Results were analyzed using one-way ANOVA test followed by Bonferroni test and expressed as mean ± SEM.
Adult female New Zealand white rabbits with an average weight of 3.5 kg (n = T10) were randomly divided into two groups: C (Control) and T (treated rabbits with bone defects caused by surgery). Rabbits were kept in individual cages with food (PROVIFE, Argentina) and water ad libitum. Experimental procedures regarding the use of animals were approved by the Bioethics Committee of Rosario National University (Resolution No. 150/2015). Its regulations are in agreement with the well-established guidelines for animal care and manipulation to decrease pain and suffering of the animal, according to the 3Rs (replacement, reduction and refinement) and follow international laws for the care and use of laboratory animals.
Antibiotic prophylaxis and anesthetic treatment were performed according to a procedure previously described [
Surgical techniques were performed in a similar way to a procedure previously described (38). The intervention began with a longitudinal cutaneous incision of 4 cm in the internal lateral distal metaphysis of the femur, immediately above the medial condyle. Medial and lateral flaps were divided, and a non-muscular aponeurotic plane was opened until reaching the desired bone area. The central point of the perforation was marked with a bradawl, and a 6 mm diameter lesion was made using a drill attached to a sterile (UV) electric motor. The hemostasis of the lesion was performed using a sterile swab plus gauze. Then, the area was dried with a sterile gauze. The tested scaffolds, SGB, previously rehydrated in the animal`s own blood, were implanted and the wounds were sutured. The aponeurotic plane was first sutured using resorbable material type 3/0; the skin was sutured with 3/0 Nylon and disinfected with povidone-iodine.
During the study period, animals were clinically monitored on a daily basis as to overall status, mobility and food intake. Body temperature was measured daily during the first week, and then weekly. Biochemical parameters were evaluated by standard procedures at days 0, 2, 30 and at the end of the study; complete blood count, total serum proteins, albumin, alanine aminotransferase (ALT) and aspartate aminotransferase (AST) were evaluated by standard procedures commercial kits (Wiener lab Group, Argentina). The results were compared to the results obtained from control animals of the same age at each time period and analyzed using the Kruskall-Wallis test.
Three months after surgery, animals were euthanized using three doses of anaesthesia, as previously described for other experimental models [
Distal epiphysis from femurs were obtained after cuts made 4 cm above the metaphysis with a carborundum disc cutter (Dochem, China) using a dental drill under irrigation with distilled water. The implanted matrix areas were marked with Indian ink. The samples were subjected to decalcification using modified Morse solution (Okayama University Dental School) and embedded in paraffin following well-established protocols. Then samples were serially cut (5 µm) to obtain oriented tissues (ephiphysis, metaphysis with implanted matrix on the same plane) and stained with Hematoxylin & Eosin (H&E) and Masson’s Trichromic. All specimens were examined with light microscopy and evaluated by a single pathologist. Subsequently, another pathologist (certified by the Health Ministry of Argentina. license N˚ 31455) performed an independent review to verify microscopic observations. The reported results reflect the mutually-agreed-upon diagnoses by both pathologists. Photomicrographs were taken from slides of each specimen by means of an Olympus SC50 camera adapted to Olympus BX 43 microscope using CellSens Standard 1.17 Olympus Soft 2009-2017 and Olympus stereo zoom SZ 51.
Histometric Analysis: Photomicrographs were taken from slides of each specimen, with an Olympus SC50 camera adapted to an Olympus BX 43 microscope using CellSens Standard 1.17 Olympus Soft 2009-2017. Five photos of each slide from the hybrid matrix area at 40× magnification, were obtained. The compartments chosen were: cement mineralized substance, inflammatory infiltrate and interstitial tissue measured with Image Pro Plus analysis system (Media Cybernetics, Silver Spring, MD, USA Version 4.5.0.29 for Windows 1998/NT/2000). Values were expressed as percentages [
The SGB pore morphology was analyzed by SEM and is shown in
regions analyzed ranging from 64 to 234 µm in 1:1 scaffold. The scaffolds presented satisfactory pore size range, and opened interconnected pores, which are essential for tissue ingrowth. The presence of pores of different sizes is very important since bone tissue grows through interconnected pores in the range from 100 to 200 µm, while cell adhesion and vascular formation occur with pores whose size is smaller than 100 µm.
The cells cultures directly in the presence of 1:1 scaffold presented above 90% viability. The assay showed that this biomaterial allows adequate cell viability and is considered suitable for in vivo tests (
The welfare of the animals during the first two days post-implantation was slightly affected, with disrupted walking, as expected. After six days, treated animals behaved similarly to their non-operated control counterparts. Temperature values, food intake and all biochemical parameters measured in the treated group were similar between control animals at every time studied (n.s.d., p > 0.05).
Two areas were selected to evaluate in vivo bone biocompatibility: 1) Femur-scaffold interface experimental lesion, and 2) Scaffold.
1) A bi-layer tissue was observed at the femur-scaffold interface formed by an inner thick fibrous tissue surrounded by an outer thick bone layer (Photo 3(a)). The new bone layer was formed by lamellar and reticular trabecular bone, thus forming the composite bone and located in the FEL (femoral experimental lesion). Close to this area, few hematopoietic tissue spaces were distinguished (Photo 3(b)). Micro-haemorrhage areas and micro-fragmented foreign body particles similar to SBG surrounded by dilated congestive blood vessels were observed.
2) Scaffold
The SGB surface was coated with a cement-like mineralized substance, osteoblast-like cells were attached and extracellular matrix was produced (Photo 3(c)), and newly formed bone anchored on the SGB surface (Photo 3(d)). Inside the new bone tissue formation, some bone particles probably obtained from the surgery process were found (Photo 3(e)). They were surface resorbed and covered by new bone formation; scattered osteogenesis was initiated inside them. Very few osteocyte-like cells and lining-like cells were found inside the amorphous mineralized deposit. Also, erythrocytes, lymphocytes and macrophages as well as cells debris were observed inside the scaffold (Photo 3(f)).
Inside the SGB matrix, 64% bone-cement mineralized substance and 28% inflammatory exudate were produced, with 8% interstitial space (
The amount of mechanical stimulation performed by the scaffold depends on the porosity, pore size, pore distribution, architecture and mechanical properties of the materials. The presence of pores of different sizes is very important since bone tissue grows through interconnected pores in the range between 100 and 200 μm, while cell adhesion and vascular formation occur in pores below 100 μm. The presence of macropores (>100 μm and <500 μm) is ideal for the growth and adhesion of the cells and the release of the nutrients to the center of the newly forming tissue. The ideal pore size for the growth of bone tissue is between 75 and 250 μm [
A biomaterial can be considered toxic for use in biological systems when it causes under 50% of cell viability. The assay conducted in this study showed that this biomaterial allows adequate cell viability and is considered suitable for in vivo testing.
The implantation of SGB did not cause either clinical or biochemical alterations in the implanted animals, which is promising for future considerations of implants in other types of injuries. Certain scaffolds, when degraded, produce
total area | Percentage of |
---|---|
Cement Mineralized Substance | 64 |
Inflammatory Exudate | 28 |
Interstitial Space | 8 |
undesirable secondary effects at the metabolic level or generate hepatic alterations. The fact that SGB implants did not produce any detectable alterations indicates that they are biocompatible.
Our results showed that SGB underwent fast degradation and size decrease after bone implantation at FEL (femoral experimental lesion, thus showing its ability to be resorbed. Inside SGB, 64% of cement mineralized substance, similar to hydroxy carbonate apatite-like (HCA) reaction layer, was produced on its surface, covered by new bone-like formation with few osteocyte-like cells inside and lining-like cells outside, after implantation into the host tissues, as a result of bioactive glass component reaction [
Moreover, the cement mineralized substance showed a granulated aspect that could be explained by dissolution, leaching and precipitation of SGB [
The presence of 28% inflammatory cells and macrophages found in our results could be explained by Vander et al. [
It could be considered that the lower values from macrophages allowed us to observe bone-like formation as well as osseointegration inside the scaffold of bone particles from the host bone, detached throught the experimental surgery lesion. This concept was supported by Li et al. [
The scaffold obtained through the lyophilization route showed adequate pore structure, presenting high porosity and suitable interconnected pores. The biological test provides evidence that it was non-toxic for the cell culture, which confirms that the biomaterials were adequate for the subsequent in vivo test. In vivo results allow us to consider SGB scaffold as a promising bone tissue engineering biomaterial.
The authors declare no conflicts of interest regarding the publication of this paper.
Coletta, D.J., Missana, L.R., Martins, T., Jammal, M.V., García, L.A., Farez, N., De Glee, T., Issa, J.P.M. and Feldman, S. (2018) Synthetic Three-Dimensional Scaffold for Application in the Regeneration of Bone Tissue. Journal of Biomaterials and Nanobiotechnology, 9, 277-289. https://doi.org/10.4236/jbnb.2018.94016