This paper reports the preliminary results on the morphology of low porosity hydroxyapatite scaffold and its compatibility as a substrate for osteoblast cells. Although having low porosity, the hydroxyapatite scaffold was found to be capable of sustaining cell growth and thus assisting bone ingrowth. Due to the low porosity nature, the scaffold provides higher strength and therefore more suitable for applications with load-bearing requirements such as spinal spacer. The hydroxyapatite scaffolds are prepared via powder processing techniques, using a combination of wet mixing, powder compaction, and sintering processes. The scaffold porosity is estimated via image analysis and micro-CT, which detect porosity level of approximately 16% and pore size of 13
Over the years, many healthcare products related to the improvement of a person’s wellbeing as one ages have seen an increase in demand [
In the context of bone-related diseases, hydroxyapatite (HA) has been widely used for bone replacement material due to its similarity in composition with respect to bone. The composition of bone mineral is comparable to sintered HA. The mineral component of bone is a biological apatite, where carbonate substitutes phosphate ions by about 3–5 wt.% [
HA has been reported to have bioactivity nature and thus assists integration and interaction of osteoblast with the implants [
There are typically two types of HA being researched, namely, dense and porous HA. Both dense and porous types of HA have been applied in many biomedical applications. Dense HA is usually referred to as HA implants with porosity up to 5% and pore size of approximately 1
The current research focuses on the use of near dense HA structures. By having porosity, however minimal, the HA structures will be able to maintain their advantage of assisting cell ingrowth and osteoconductive properties, but at the same time, the structure is mechanically strong enough to withstand breakage. A dense HA spacer for cervical spine is one of the several applications that would benefit from a near dense HA structures with porosity to a certain degree. A clinical outcome of a dense HA spacer was previously reported as equal to autologous iliac crest interbody fusion and that patients who underwent the HA fusion had less need for secondary operation due to plug slippage [
HA scaffold is typically prepared from axial powder compaction of HA powder, followed by binder removal process and further densification of the HA material [
In this research study, low porosity HA scaffolds are prepared via wet powder mixing process, followed by pressureless sintering for the pore former removal. The samples are then characterized and tested for their morphology using microcomputed tomography and image processing. The potential cell growth on the manufactured scaffolds is also tested using MTT assays and collagen staining quantification.
Hydroxyapatite (HA) powder was supplied by Himed (powder size distribution of D10 = 95.95
The scaffold was processed via powder processing route. HA powder was first mixed with corn starch, as a binder-cum-pore forming agent, with the percentage of 80 weight (wt.)% of HA and 20 wt.% of starch. The starch was first dissolved in warm water (70°C) while continuously stirring the solution. The HA powder was added little by little into the dissolved starch solution. Deionized water was added to the solution. The subsequent mixing process was carried out in a jar mill (Gardco 764 AVM) for 3 hours at 120 rpm. Alumina balls were used in the mixing process, with the powder-to-ball mass ratio of 1 : 4.
The HA/starch solution was then air dried for 48 hours and pulverized in room temperature by crushing and grinding the dried HA/starch cake using a mortar and pestle. The HA/starch powder was then compacted with the force of 49.03 kN. The pellets were subsequently subjected to thermal debinding-cum-sintering process (CM Rapid Temp Furnace) in atmospheric environment. The starch was burnt out from the green part during the debinding stage. The debinding process was conducted at holding temperatures of 250°C, 300°C, and 600°C for 1 hour at each holding temperature to ensure complete removal of the binder. The subsequent sintering was performed at 1250°C for 2 hours. The final manufactured scaffolds were 24.4 mm in diameter and 4.8 mm in height.
Surface porosity of the scaffolds was evaluated using SEM (Leica S360) and image analysis (Adobe Photoshop Element v.3). The samples were first gold coated (sputter coated SC7640) prior to SEM inspection using EHT supply of 15 kV. Seven distinct areas (
Internal morphological test was conducted using microcomputed tomography (micro-CT, SkyScan 1172) scans carried out with sample sized 2 × 2 × 2 mm. The pixel size used was 4.3
The porosity of the scaffold was indirectly calculated from the sample’s true volume, measured using a pycnometer (Micromeritics, AccuPyc 1330). Ten samples were used for the measurement (
Hardness measurement of the HA scaffolds was conducted using a Vickers microhardness measurement tool (MMT-X3, Matsuzawa Co., Ltd.). A diamond indenter with 490.3 N load was used to indent eight distinctly different locations on the scaffold (
The scaffolds were sterilized using autoclave process. Subsequent to the sterilization, the scaffolds were washed with phosphate buffer saline (PBS) and were conditioned with the cell media (Invitrogen, MEM Alpha Medium, with Ribonucleosides and Deoxyribonucleosides, cat. 22571).
The scaffolds were divided into two groups, each having three scaffolds (
MTT ((3-(4,5-dimethylthiazol-2-yl)-2,5-diphenyltetrazolium bromide) concentration of 0.5 mg powder (Sigma) per 1 mL of PBS was used. The culture plates were incubated at 37°C for 1 hr. Subsequently, the MTT solution was removed off the plate. Acidified isopropanol (prepared by mixing 25
Collagen stain was prepared by mixing a solution of sirius red (direct red 80, Fluka) 1 mg/mL in saturated picric acid (Fluka). The samples were washed with distilled water prior to addition of the collagen stain. The immersed samples were then shaken at room temperature overnight. Following that, the samples were washed with distilled water until the red coloring stopped eluting. Subsequently, the samples were destained with a mixture of 0.2 M sodium hydroxide (Sigma) and methanol in a ratio of 1 : 1 and were mildly shaken for 15 minutes at room temperature. Two liquid samples were taken from each solution of the scaffolds and control wells, such that the density could be read. The optical density was then measured using a spectrophotometer (Bio-Tek ELx800), using 490 nm wavelength.
This section discusses the observations gained from the surface porosity, micro-CT, and
SEM micrographs were used to estimate the surface pore size and porosity level of the scaffold. Figure
Cross-section image of the HA samples.
Images of the sample surface were used in the image analysis to estimate the porosity of the scaffolds. Figure
Typical image analysis of HA scaffold. (a) Micrograph of surface structure (magnified 200 times); inset: typical pores on scaffold surface (magnified 1000 times). (b) Surface porosity of the scaffold, highlighted by the black contrast colour.
Further analysis with the micro-CT confirms the porosity estimation of the HA scaffold within its volume. Micro-CT estimates the morphological parameters of the scaffolds, such as the porosity and average pore size. The micro-CT measurement result is reported in Table
Micro-CT measurement result.
Measurement | |
---|---|
Pore size | 13.21 |
Closed porosity |
|
Open porosity |
|
Total porosity |
|
Micro-CT image of the HA sample.
Micro-CT shows that the total porosity of the sample is 15.8% (±0.5%). This porosity is approximated to be a combination of open porosity and closed porosity. Open porosity refers to the pores that are interconnected between one another, and closed porosity refers to isolated pores within the scaffold.
The total porosity is shown to be almost evenly divided between the open and closed porosities. It indicates that there are similar amount of both interconnected and isolated pores. Assuming that the pore-forming agents were evenly distributed in the scaffold during the processing, the isolated pores would be predominant in the scaffold. However, the micro-CT finding showed that approximately half of the porosity was open and interconnected pores. There were two reasons of this finding. Firstly, there were pore formers that were not homogenously mixed, presumably during the wet mixing process. Secondly, densification of HA typically starts at temperature range from 700 to 800°C [
To further verify the porosity analysis, the porosity of the HA samples (
The pycnometer measures the sample’s true volume, whereas the bulk volume is calculated from the measured height and diameter of each sample. The average porosity obtained from the measurement was 22.7% (±2.96%).
It is noted that there is a difference between the porosity calculated using the pycnometer and the porosity estimated by both image analysis and micro-CT. One of the main sources of differences is that there could be due to the loss of data resolution and incorrect identification of the pore edges during the CTAn analysis of the micro-CT volume of interests. Hence, the total pore areas and volume could be underestimated.
From the micro-CT, the average pore size of the HA scaffolds is analyzed to be 13
The porosity and pore size obtained from the process are well below the so-called definition of highly porous structures that are commonly reported, with minimum 40% porosity and pore size of 100
The HA samples were found to have microhardness property of 5.28 (±1.08) GPa. This hardness property is distinctively higher compared to similar HA scaffold with porosity of 20%, as reported by Ma et al. [
MTT is a colorimetric assay that is used to qualitatively identify the cell locations in a substrate. This assay measures the reduction of yellow MTT solution by mitochondrial succinate dehydrogenase that is found in live cells. The MTT enters the cells and passes into their mitochondria where it is reduced to an insoluble, dark, purple formazan product. The cells are then solubilized with an organic solvent, and the released dark purple formazan reagent is measured spectrophotometrically. Quantitatively, for a 2D substrate, the colour intensity of the purple liquid indicates the relative number of cells that were alive in the substrate.
After the addition of MTT solution, both the HA scaffolds and control plates showed signs of live cells occupying the space. This was indicated by the purple colour that appeared on the scaffolds and the control plates as a reaction between the MTT solution and live cells, as shown in Figure
HA scaffolds after MTT staining.
As the reduction of MTT into dark purple formazan can only occur in metabolically active cells, the appearance of the dark purple colour is a sign of the cell viability in the scaffolds and on the control plates.
It is noted the cells are able to slightly penetrate to the circumference of the scaffolds. It is observed in Figure
Cells indicated at the scaffold circumference.
Upon complete elution of the dark purple formazan, the colour intensity from the formazan is read by a spectrophotometer. Figure
MTT quantification of relative numbers of cells after 7 days of seeding (*indicates significant difference,
The MTT reading shows that there is a significant difference between the numbers of cells found on the scaffolds as compared to those found on the control plates. Both readings with 50,000 and 500,000 cell density have
It is noted that the initial amount of cells seeded in the two groups of scaffolds and the controls have a 10-fold difference. However, this is not reflected in the growth and proliferation outcomes after 7 days of culture. This could be explained by the fact that in general cells do not grow in a linear relationship. There are various conditions that affect cell growth. Firstly, overcrowded culture could result in cell death as there is lack of growth space and nutrients from the media. Cells could also fall off the substrate and get washed away in an overcrowded culture. Secondly, there is a limit to the number of cells that a substrate can support for a period of time. Again, this is because the substrate is a static structure which does not have any changes in the dimensions. After a certain period of time, the culture will become overcrowded. Normal cells stop dividing after they reach a certain density. It is understood that after a cell makes contact with other cells on the substrate, specific signal is relayed to inform the cell if all cellular contact points have been satisfied. If all contact points have been satisfied, the genes that signal proliferation are turned off and as such, the proliferation stops [
As MLO-A5 is an osteoblastic cell type, it would normally secrete collagen when it is proliferating healthily. The collagen staining test is used to measure the amount of collagen matrix formed by the MLO-A5 cells. The collagen staining visual observation is shown in Figure
Collagen staining of the HA samples.
The collagen staining showed that the cells were able to penetrate into the circumference of the scaffolds, as can be seen from Figure
Collagen matrices indicated at the scaffold circumference.
Quantification of collagen matrix production after 7 days of culture.
In this observation, it is seen that the collagen matrix production in the HA scaffolds was more than that produced on the control substrates. This supports the argument that a 3D HA scaffold, in this case HA scaffold, is a more suitable substrate material, preferred by the bone cells to grow, proliferate, and perform their collagen matrix production function, as compared to the polymeric 2D cell culture plate. This observation was also seen in other work, in which osteocalcin secretion and alkaline phosphatase activity were detected at a significantly higher level on 3D scaffold than on 2D cell culture plate [
It is also observed that collagen matrices produced by the scaffold with initial seeding density of 500,000 cells were less than that seeded ones with 50,000 cells. This was an interesting finding, as the earlier MTT readings showed that by the end of the 7-day culture, the cells on scaffolds seeded with initial 500,000 cells were able to proliferate more than that of scaffolds seeded with 50,000 cells. Several postulations are given. Firstly, there is a limited area in the scaffold for the osteoblast cells to contain both their proliferation and collagen matrix production activities. When there are too many cells on the substrate, there will not be enough areas for the produced collagen matrices to attach, and the layer of collagen matrices may easily fall off the substrate or get washed away by the PBS. Hence, as the cell quantity in the 50,000-cell scaffolds was less than that of the 500,000-cell scaffold, as was estimated using the MTT test, the cells in the prior scaffolds had more areas to contain the produced collagen matrix. Secondly, when the cells in the 500,000-cell scaffold were occupied in the proliferation activity, it was harder for these cells to work as much to produce the collagen matrices. In the molecular level, there is a certain driving force and energy required for any molecular activities [
The cell culture results have confirmed that the HA scaffolds are able to demonstrate its suitability to support anchorage and maintain viability of live cells. Future study would be to continue with the
The current research reported here has shown that low porosity HA scaffold could be well produced using compaction and sintering methods. The microporosity of the HA scaffold has been conducted and has shown that the pore size and porosity level of the scaffold are within the range for a low porosity scaffold. The mechanical hardness strength of the scaffold was also found to be comparable, if not higher than other HA scaffolds with similar porosity value.
The cell culture experiment has shown that HA scaffold is a more preferred substrate material as compared to the polymeric cell culture plate for culturing osteoblast cells. This is despite the standard condition of the cell culture control plates having been treated by vacuum-gas plasma to provide conducive cell attachment environment. The osteoblast cells seeded onto the HA scaffolds are found to yield favourable results in both the numbers of cells and in cellular activity after a certain period of time. This results demonstrate that the HA scaffolds are suitable to support anchorage and maintain viability of live cells. Initial cell seeding of 50,000 MLO-A5 cells is found to be sufficient for culture on the HA scaffolds. This amount of initial cell seeding density is adequate to demonstrate favourable cell growth and proliferation. This initial cell seeding density is also sufficient in order to avoid cell overcrowding for effective collagen matrix production.
It is noted that this scaffold with lower porosity or near dense properties are still capable of providing cell attachment into the pores of the scaffolds, while it simultaneously provides sufficient handling strength to potentially avoid breakage during the implantation. It is hence suggested that this type of HA scaffold could be used as effective bioactive scaffolds for applications that required high strength, such as bone or spinal implant grafts. The future works that could be carried out based on the current study is to evaluate the degradation and resorption mechanisms of the HA scaffold
The authors would like to thank Dr. Gwendolen Reilly and Dr. Anuphan Sittichokechaiwut (Department of Engineering Materials, The Kroto Research Institute, North Campus, University of Sheffield) for the valuable advice and discussion, provision of the osteoblast cells and cell culture consumables, and assistance in the cell culture process. Dr. F. E. Wiria would like to acknowledge the funding from the British Council Researcher Exchange Programme that provides the collaboration opportunity and the use of micro-CT equipment.