Nanomaterials-Upconverted Hydroxyapatite for Bone Tissue Engineering and a Platform for Drug Delivery

Abstract

Hydroxyapatite is a basic mineral that is very important to the human body framework. Recently, synthetic hydroxyapatite (SHA) and its nanocomposites (HANs) are the subject of intense research for bone tissue engineering and drug loading system applications, due to their unique, tailor-made characteristics, as well as their similarities with the bone mineral component in the human body. Although hydroxyapatite has good biocompatibility and osteoconductive characteristics, the poor mechanical strength restricts its use in non-load-bearing applications. Consequently, a rapid increase in reinforcing of other nanomaterials into hydroxyapatite for the formation of HANs could improve the mechanical properties. Most of the research reported on the success of other nanomaterials such as metals, ceramics and natural/synthetic polymers as additions into hydroxyapatite is reviewed. In addition, this review also focuses on the addition of various substances into hydroxyapatite for the formation of various HANs and at the same time to try to minimize the limitations so that various bone tissue engineering and drug loading system applications can be exploited.

Introduction

Since nanotechnology has emerged across multiple disciplines in recent years, nanomaterials have been gaining interest in biomedical applications especially in the sector of bone tissue engineering. Among various advanced nanomaterials, nanocomposites are composed of numerous nanoscale materials or nanoscale materials reinforced with other types of material. Generally, nanocomposites are formulated and designed in order to amend the properties of certain materials to meet their application. With the urgent need for the clinical development of bone-restoring nanomaterials that are able to mimic and imitate the structure and function of natural bone and are biocompatible to in vivo environment, bone tissue engineering has come out and is flourishing lately. In bone tissue engineering, nanocomposites would focus on rejuvenation of bone tissue instead of bone superseding.

Bone and dentin contain about 45–70 wt.% of calcium phosphate, 10 wt.% of water and the remaining part is collagen.^82,107 The mineralization of calcium phosphate produces hydroxyapatite (Ca₅(PO₄)₃ OH) in the bone formation process which leads to body enlargement.^65,94 However, extensive studies on bone mineral proved that the mineral in bone contains impure hydroxyapatite due to the presence of minor groups and elements, namely carbonate (CO₃^2-), hydrogen phosphate (HPO₄^2-), sodium (Na⁺) and magnesium (Mg²⁺) ions, and trace elements such as strontium (Sr²⁺), potassium (K⁺), chloride (Cl⁻) and fluoride (F⁻).⁷³ These varied elements were utilized in the biochemical reactions of bone metabolism.

Hydroxyapatite is naturally found within the mineral phase of shells,¹² teeth⁷² and bones in mammalian bodies.²⁹ Meanwhile, synthetic hydroxyapatite commonly exists as a white powder. Nonetheless, the elements and characteristics of synthetic hydroxyapatite complement natural hydroxyapatite found in living organisms. The properties of synthetic hydroxyapatite depend on the synthesis technique being implemented,³² and hydroxyapatite and hydroxyapatite-reinforced nanomaterials are substantially used in various applications particularly in the biomedical area. Owing to its feature chemically matching with biological calcified tissue, it is extraordinarily biocompatible.⁴⁸ In addition, hydroxyapatite is a bioactive ceramics broadly used as particulate forms or powder in bone repairs, matrix for drug delivery as well as acting as a coatings material for metal prostheses²² in order to enhance biological activity. Hydroxyapatite has high osteoconduction properties,⁹⁸ and it was a material that merged into bone without adverse reaction. Hydroxyapatite is the most stable calcium phosphate ceramic material regarding temperature, pH and composition of intravascular fluid.⁴⁹

Aside from its advantages, hydroxyapatite has poor mechanical strength which limits its broad application, especially as an implant material.⁷⁷ The mechanical properties of pure hydroxyapatite are in the range of 120–150 MPa, 38–300 MPa and 38–250 MPa for compressive, tensile and bending strength.³⁶ Thus, hydroxyapatite-reinforced nanomaterials have been tested and experimented with rigorously, and hydroxyapatite doped versions were used as therapeutic agents to carry the drug locally to specific sites of the body without provoking an immune reaction. From the bone replacement viewpoint, an optimal bone scaffold material should meet the following properties for bone tissue engineering purposes, as illustrated in Figure 1: (1) Biodegradability is an optional feature for every type of scaffold. Scaffold predominantly exhibits degradation properties to give spaces for the growing cell. A man-made scaffold that consists of biodegradable materials will eventually break down into small fragments, disseminate and be absorbed in the body at particular phases, and is followed by the growth of new bone tissue.¹¹² (2) Biocompatibility of material is pivotal in the scaffold system as it will protect living tissues from harm and toxicity.⁹⁸ The materials used for scaffold development must be able to be incorporated well into the body without showing any harmful effects. (3) Proper mechanical strength of scaffold is a prerequisite to bear the cell ingrowth. The mechanical strength of the scaffold surface will support the adhering cells to grow. Tensile and compressive tests usually were employed to evaluate the mechanical strength of scaffolds in bone tissue engineering.¹⁰⁵ Besides that, (4) an interconnected porous system is a significant parameter in designing bone scaffold. The pattern of a highly porous interconnected structure with multivariate pore-size distribution will determine the cell recruitment, cell adhesion,¹⁷ cell proliferation and differentiation,⁶⁷ and gives a passage to gases and nutrient conveyance until the basement for consistent cell growth rate and elimination of waste product along the process.¹⁰⁰

Figure 1.

Some important properties of a bone scaffold.

This present work reviews the appropriate methods employed to produce the optimum amount of products, and the preliminary studies in the biomedical field. In the first section of the review, the authors discuss briefly the synthesis technique of hydroxyapatite nanoparticles and their nanocomposite. Second, the authors revise the application of hydroxyapatite-containing nanocomposites for bone tissue engineering and as a therapeutic agent in drug delivery systems.

Synthesis of Synthesized Hydroxyapatite

Hydroxyapatite can be synthesized using a chemical precursor. Several methods have been created, for instance, dry method, wet method, thermal method, or a combination of these methods.³³ Besides that, hydroxyapatite can also be produced from natural sources such as mammalian bones,⁴¹ egg shells⁴⁶ and plant sources.^4,45 Each of these methods controls the sizes, chemical composition, crystallinity and morphology of synthesized hydroxyapatite, and those properties influence the biocompatibility, bioactivity, mechanical strength and biological properties. Figure 2 summarizes the several methods used to synthesize the synthetic hydroxyapatite.

Figure 2.

Methods to synthesize the synthetic HA.

Dry Method

Dry methods are further classified into two different techniques, namely mechanochemical method and solid-state method.⁸³ Essentially, the dry method involves the mixing of precursor chemicals which are calcium and phosphate in dry form in order to synthesize hydroxyapatite.^24,39 The dry method usually does not involve specific and controlled conditions; therefore, dry methods are convenient for the large-scale production of powder.¹⁹

Wet Method

The synthesis of hydroxyapatite via wet method is in an aqueous solution, and some of this method usually involves the extraction of hydroxyapatite such as chemical precipitation and hydrothermal method. The wet method employs an optimum temperature to synthesizes hydroxyapatite, where the temperature is near to the temperature of the synthesis process of hydroxyapatite in the bone tissue.²⁹ Despite the advantages of employing wet methods, such as morphology regulation and control of average size of powder,¹¹⁶ the disadvantages, like manifesting low crystallinity due to low temperature during the process, restrict its use in producing synthesized hydroxyapatite.^56,100

Thermal Method

In the thermal method, the materials will undergo a decomposition process which is attributed to the high processing temperature.⁹ Throughout all the synthesis methods, namely, combustion and pyrolysis, both methods are rarely employed for synthesizing hydroxyapatite because of difficulty to monitor the processing parameters and secondary aggregates of product. However, thermal methods, notably the combustion technique, were proven to improve antibacterial properties of hydroxyapatite.⁵⁷

Hydroxyapatite Scaffold Containing Nanomaterials as Implant Material in Bone Tissue Engineering: Anti-Bacterial, in vitro and in vivo Studies

The musculoskeletal system is responsible for supporting the body structure and provides a bone scaffold for the mammalian body.⁶⁰ Technically, the bones of the human skeleton represent anchor sites for muscles, tendons, ligaments and other connective tissues to link tissues and organs and allowing the body’s motion.⁹² The natural aptitude of bones is emphasized in the body’s unique ability to repair itself via bone regeneration. Nevertheless, bone defects of greater than 50% of bone loss or approximately 1–2 cm in length of bone bore that are caused by major injuries do not spontaneously heal without intervention.⁵³

Recently, autogenous bone implants (also known as autologous transplantation) were seen as the gold standard in bone regenerative therapies, and generally the bone cells are taken from the patient’s own iliac bone. However, there are many drawbacks of autologous implantation such as unmet supply with great demand, inflammation risk, severe infection and donor site complications among patients. Allograft implants are other therapies used in clinical interventions where the bone cell is taken from other patients. Despite its advantages like providing some growth factors and disclosed osteoinductive properties by activating the signaling pathway to generate new bone cells, limitations like infection between donor and receiver, immune dismissal and even probably also failure restrict their use in bone defect repair.

In the past decades, researchers have shown great interest in engineered bone tissue, as they viewed it as a divergent treatment that potentially suppresses all the issues faced by the current clinical treatments. They suggested that engineered tissue strategies are perceived as the finest techniques since the process is implemented directly to the patient’s tissue until the operation is completed. A summary of the integration between hydroxyapatite and other materials to produce nanocomposite scaffold is depicted in Figure 3. Bone tissue engineering is a multidisciplinary field that combines biology and engineering principles and techniques for rejuvenation of bone tissue and involves the evolution of biological substitutes of the autograft and allograft of the bone-implant treatment. Bone tissue structure pertained to a 3D scaffold system to allow them to control the structure together with its mechanical and physical properties.¹⁸

Figure 3.

HA reinforced with other materials to form bone scaffold.

Many alternatives have been made to diminish the limitation of hydroxyapatite in bone tissue engineering by adjusting nanocomposite structures through the integration of nanomaterials into hydroxyapatite. In this section, the authors aim to focus on the application of hydroxyapatite reinforced with nanomaterials in the bone tissue engineering field by reviewing the antibacterial, in vitro and in vivo studies.

Hydroxyapatite–Metals Nanocomposite

Silver

Silver is a precious metal with potent antibacterial properties, extensively used in biomedical applications, mainly bone tissue regeneration. In a study conducted by Qais et al⁸⁴ silver nanoparticles were extracted from Murrayakoenigii (L.) (M.koenigii) leaves to study the antibacterial activity of silver nanoparticles (AgNPs). Silver nitrate solution (AgNO₃) was prepared and added to aliquots of M.koenigii aqueous extracts. After 4 hours of incubation of mixed solution, the solution turns to a dark brown color indicating the formation of AgNPs. XRD results showed that the average size of MK-AgNPs (M.koenigii-silver nanoparticles) was found to be 13.54 nm which is within the nanosize range. Moreover, in the results of antimicrobial activity against E. coli and S. aureus, methicillin-susceptible Staphylococcus aureus 2 (MSSA2) showed the most resistance among all bacterium types. MK-AgNPs indicate larger inhibition zones in comparison to AgNO₃, 16 mm and 15 mm, respectively. When bacteria are detected in nearby living tissue cells, the silver ion will diffuse out to inhibit the bacteria growth. This is due to the greater surface area of AgNPs which gives a large contact area with the pathogen and makes it easier to destroy. Similarly, Cardozo et al¹¹ found that in the combination of AgNPs with natural antibiotics extracted from the plant, phenazine-1-carboxamine produced a synergic effect against the strains by amending their cell wall structure. The AgNP action mechanism is through the attack of respiratory part and cell separation, which led to microbial inactivation. In addition, the AgNPs not only adsorbed on the cell membrane surface but also inside the pathogen.⁹³ It evinced that the AgNPs attach to the cell membrane and infiltrate inside the pathogen as well.

Recent studies done by Khan et al⁵⁰ had developed a polymeric nanocomposite scaffold composed of arabinoxylan-co-acrylic acid, nano-hydroxyapatite (nHA), nano-aluminum oxide (nAl₂O₃) and graphene oxide (GO) via free radical polymerization. These nanocomposite (ARX-GO-nHA/n-Al₂O₃-AAc) scaffolds were coated with silver nanoparticles (AgNPs) to enhance the antibacterial properties of the scaffold. AA-Ag1, AA-Ag2 and AA-Ag3 denote each of polymeric nanocomposite scaffolds based on the amount of GO. Anti-bacterial activities were observed against E. coli, P. aeruginosa (Gram-negative) and S. aureus (Gram-positive). The AA-Ag3 nanocomposite, with the highest GO content, had the maximum inhibition zone of antibacterial activities. This can be explained by the sharp GO edges puncturing the membrane by an adsorbing, wrapping and capturing effect and stimulating Ag ions to the GO sheets due to the highly negative charge that successfully boosts up antibacterial activities. The oxidation of AgNPs by water/oxygen induce Ag⁺ ions and reactive oxygen species (ROS) to inhibit replication by attacking the deoxyribonucleic acid (DNA).⁵⁰

Besides that, Kumar et al⁵⁵ employed a freeze–thaw method with a simple modification to synthesize a silver hydroxyapatite (Ag-HA) reinforced gelatin-alginate-PVA cryogel nanocomposite. The XRD results of Ag-HA nanoparticles indicate the reinforcement of Ag⁺ ions into the hydroxyapatite lattice, with increased crystalline properties which are 9.3 nm and 81.8% for size of crystallite and crystallinity, respectively. SEM microscopic imaging shows the pores were present in Ag-HA nanoparticles which facilitate cell attachment, as it activates the bone-implant process, hence enhancing bio-integration and stability by assisting in the diffusion of neighboring bone tissue. The porosity of nanocomposite scaffolds is more than 80% and is suitable for bone tissue engineering because it will allow cell migration and proliferation. Antibacterial assays of Ag-HA nanoparticles and cryogel nanocomposite scaffolds were done towards Bacillus spp. and E. coli sp. The inhibition zones were found to be 18 mm and 22 mm for Bacillus spp. while they were 12 mm and 24 mm for E. coli sp., respectively. The authors revealed that when the antigen is detected surrounding cell tissue, Ag ions will be released from Ag-HA nanoparticles, and at the same time the tissue cells adhered to the scaffold surface as the surface has fibroblast morphology. This also proved that the presence of Ag nanoparticles does not affect the compatibility and toxicity towards the tissue cell and the aptitude for cell adhesion and growth. The Ag-HA nanoparticles are more efficient to prevent the growth of bacteria without altering the biocompatibility properties of hydroxyapatite compared to native hydroxyapatite. Additionally, the concentration of Ag nanoparticles influences the degree of bacterial activity inhibition.³⁷ The higher the concentration of Ag nanoparticles in the nanocomposite scaffold, the greater the efficiency of bacterial growth inhibition. Nevertheless, it is important to control the concentration of silver in the scaffolds because an excessive amount of silver can lead to inhibition of bone tissue growth and increase toxicity in the human body.^44,87

Zinc

Zinc plays an important role in the human body. The dissemination of zinc in the human body is nearly 57% in muscle, 29% in bone, 6% in the skin, 5% in the liver, 1.5% in the brain and 0.1% in blood plasma.⁸⁰ Zinc is involved in several enzyme activities such as protein synthesizing and deoxyribonucleic acid (DNA) and ribonucleic acid (RNA) activation via zinc finger protein. In recent times, zinc as a trace element has been experimented with and developed for cardiovascular and orthopedic applications due to its favorable properties like mechanical durability, biocompatibility, biodegradability and use as an adequate antimicrobial agent.⁹⁶ Furthermore, from a bone formation standpoint, zinc is crucial in stimulating osteoblast cell formation,¹³ protecting bone from breakdown, and it reduces the toxic effect from other metals, especially cadmium.¹⁵ As noted by Qi et al,⁸⁵ when streptozotocin-induced diabetic rats were treated with 0.25 mg/kg/d zinc sulfate by daily gavage feeding for 8 weeks, this resulted in thicker trabecular bone, and bone mineral density (BMD) and femoral bone significantly improved, although the rats were still diagnosed as hyperglycemic.

Ofudje et al employed hydroxyapatite-containing zinc (HA-Zn) nanocomposites via chemical co-precipitation method for bone regeneration application.⁸¹ The result revealed that the higher the zinc content in the HA-Zn nanocomposite, the lower the crystallinity of apatite. The deformity existed in the hydroxyapatite lattice structure as zinc ions were introduced into hydroxyapatite and caused a dwindling to the structure of hydroxyapatite. In spite of that, the incorporation of Zn into hydroxyapatite requires sintering at high temperatures to substitute calcium ion (Ca) and fill the vacancy in the lattice site. SEM analyses show the round shape and needle-like structure of hydroxyapatite nanocrystals with lengths within the range of 15–35 nm and width 4–12 nm. It is worth noting that the hydroxyapatite nanoparticle size is vital for the implant material in order to ensure contact reaction and stability of the natural/artificial bone attachment. Further, the morphologies of HA-Zn nanocomposite demonstrate the presence of interconnected porosity in the scaffold structure,⁸¹ which is beneficial in stimulating bone formation as it is a prerequisite for bone tissue engineering. Anyhow, 20% of Zn-doped hydroxyapatite shows the highest inhibition area, while no inhibition area was observed when the bacteria were treated with pure hydroxyapatite, indicating that hydroxyapatite lacks antimicrobial activity. As mentioned, the crystallinity of hydroxyapatite decreased when 20% of zinc was inserted and caused the enlargement of apatite surface area, thus forcing microorganisms to attach to the apatite surface, and resulting in cell death. Hydroxyapatite tends to bind with functional groups (imidazole, thiol, carboxyl and amino groups) on the pathogen surface due to the protein-type membrane, and eventually altering the surface morphology of the pathogen.¹⁰¹

Recently, a study on the osteogenesis behavior of citrate zinc hydroxyapatite nanocomposite for bone tissue engineering was done by Fernandes et al.²⁸ A one-step hydrothermal technique was utilized in synthesizing citrate zinc hydroxyapatite (cit-Zn-HA) nanocomposite. The presence of zinc in cit-Zn-HA nanocomposite reduced the Ca/P atomic ratio to 1.55 from the normal level of 1.67, but the ratio of cit-HA was near the normal ratio, which is found to be 1.66. These results can straightforwardly be related to the Ca(Cit)⁻ ions that could be replaced by Zn-citrate ions, so the amount of Ca decreases upon the addition of Zn. As such, the Ca ion (0.99 Å) has a larger ionic radius compared to Zn (0.74 Å). Significant depletion was observed in nanoparticle length along the longest axis upon the presence of zinc, resulting in the decrease in length of hydroxyapatite nanoparticles. This result is in agreement with previous studies,⁸¹ evidencing that the incorporation of zinc with hydroxyapatite shortens the length of nanoparticles and impacts the crystallinity and morphology as well. Other than that, the osteogenic response of human bone marrow-derived stromal cells (hBMSCs) indicates good cell viability without apoptotic events and elongated F-actin-stained cells with the conspicuous nucleus as well as the cell-to-cell connection. Overall, the cell proliferation results presented more exuberant, with highest ALP activity and obvious calcium phosphate deposits when exposed to cit-Zn-HA compared to cit-HA and Zn-HA. These results are demonstrating that the osteogenic and mineralization activities are perhaps due to a synergistic effect as a result of zinc and citrate incorporation into HA.

Copper

Among various metals employed for bone replacement application, copper (Cu) is the most often-used metal due to its significant role in the human body and antibacterial properties. Cu can destroy bacteria through lipid peroxidation, oxidation of protein, DNA disruption and promoting reactive oxygen species (ROS).⁶⁹ Essentially, the antibacterial activities of copper are known to be more efficient in high temperatures and high relative humidity within hours.^31,34 In one study viable endospores in Clostridium difficile spp. were completely inactivated within 24 h to 48 h on a copper surface.¹¹¹ Another study was conducted by Sahithi et al⁹¹ who investigated the antibacterial activity of hydroxyapatite and hydroxyapatite-doped Cu nanocomposite against Gram-positive strain (S. aureus) and Gram-negative strain (E. coli). Staphylococcus aureus (S. aureus) is a type of pathogen that is commonly associated with bone device-related infections and also antibiotic resistance, while Escherichia coli (E. coli) tends to decrease osteoblast cell viability during the osteogenesis process of bone formation.^21,68,102 Hydroxyapatite behaved like an inert material as it does not support or prevent bacteria growth in the same way as the control. But, when hydroxyapatite is doped with Cu, the optical density value indicates antibacterial activity events in both Gram-positive and Gram-negative bacteria. Also, the MTT assay proved that these nanomaterials combinations are safe to be used for bone implants since the cell viability remains unchanged. Contrary to the results obtained by Nam et al,⁷⁶ pure hydroxyapatite and CuHA nanocomposite show good antibacterial activity. The addition of Cu solely improved the inhibition of E. coli and S. aureus activity compared to pure hydroxyapatite. As the concentration of Cu increased in the hydroxyapatite nanocomposite, the antibacterial ratio increased from 22% to 89% and 29% to 98% against E. coli and S. aureus, respectively. The Cu ions in the hydroxyapatite nanocomposite will tie up hydroxyapatite to the cell wall and disrupt the bacterial cellular system.¹⁰¹ Nevertheless, a different type of bacterium will have distinct sensitivity depending on their membrane structure, as shown in Figure 4A and B. The Gram-positive bacteria are more attracted to Cu ions due to the negatively charged surface of lipoteichoic and teichuronic acid inside the porous layer of peptidoglycan. The copper ion will be attached to the outer layer of Gram-positive bacteria by electrostatic forces, resulting in cell damage by protein denaturation and destruction of the cell membrane.⁵ On the other hand, Gram-negative bacteria have a compact outer member structure that will act as a barrier to prevent the penetration of certain compounds, especially high molecular weight compounds, thus making them less attractive to metal ions.⁵ Although the high content of Cu indicates good antimicrobial activity, it was evidenced that it also increases the apoptosis event which is forbidden for bone tissue engineering.² Therefore, it is mandatory to choose the optimum concentration of Cu content in the nanocomposite scaffold in order to provide the finest living environment for cells.

Figure 4.

Structure of (A) Gram-positive and (B) Gram-negative bacteria.

Aside from topical antibacterial agents, Cu is predominant in providing cell proliferation of osteoblast assisting in cell differentiation,² and it is important in promoting angiogenesis fit for bone regeneration.⁵ The combination of Cu and hydroxyapatite has been shown to improve hydroxyapatite properties as well as facilitate cell growth for bone regeneration. For instance, Ai et al² investigated hydroxyapatite scaffold doping with Cu for bone tissue engineering. The CCK-8 test was done using different Cu ratios, namely 1CuHA, 5CuHA, 10CuHA and 15CuHA, to observe cell proliferation of bone mesenchymal cells (BMSCs). They noticed that 1CuHA promotes cell proliferation and also 5CuHA maintained a good growth state of BMSCs. In contrast, 10CuHA and 15CuHA showed high inhibition rates after inoculation for 7 days. Similarly, Guo et al³⁵ found that at low Cu content, copper-doped calcium polyphosphate (CCAP) nanocomposite scaffolds exhibited good cell proliferation of human osteoblast while high Cu content nanocomposites impeded the cell proliferation. Thus, when the Cu ions surpass the optimal limit, this leads to significant toxicity effects on cells⁸⁹ and increases the free radical species production that causes neurodegenerative diseases.³⁸

In addition, SEM micrographs² showed the presence of interconnected pores in CuHA scaffolds that is convenient for cell migration, cell proliferation and vascularization to facilitate cell growth. A study was done by Stanic et al¹⁰¹ on the cytotoxicity of HA-Cu nanocomposites towards living cells by testing rat primary osteoprogenitor cells and demonstrated that the cell viability remained unchanged, and it confirmed that copper ion is safe to be used with hydroxyapatite for bone tissue engineering. Nonetheless, the addition of copper ions will affect the crystallinity of hydroxyapatite, but it can be avoided by sintering and aging processes during the preparation steps. Thus, the hydroxyapatite doping with Cu of nanocomposite scaffolds is applicable in their use as a nanomaterial implant for bone tissue engineering at the optimum ratio of Cu content and in controlled conditions.

Hydroxyapatite–Polymer Nanocomposite

Chitosan

Owing to features like biodegradability producing degradable products, high biocompatibility and commercial availability, much attention has been paid to the chitosan application in both research and development for bone filler.⁸⁹ Chitosan is a type of natural polymer derived from the deacetylation of chitin treated with alkaline substances. It has a structure composed of plentiful reactive amino and hydroxyl groups as illustrated in Figure 5.²⁶ This reactive amino group is very useful to induce a cellular response in scaffolds formulation as it improves surface chemistry and wettability and reduces hydrophobicity of scaffolds surface in order to initiate cell attachment, spreading and proliferation.¹¹⁰ The degradation of chitosan in the in vivo environment generates small, non-toxic and readily absorbed molecules of amino and polysaccharides.⁹⁵ To tailor characteristics such as solubility, chemical reactivity and biological activity to diversify its application in bone tissue engineering, chitosan needs some modification. The incorporation of chitosan with other nanomaterials was reported to be more suitable for cell growth promotion. A study was done by Li et al⁶¹ on the incorporation of hydroxyapatite and chitosan for bone tissue engineering applications to enhance their strength. The results evinced that the compressive strength of hydroxyapatite nanocomposite scaffolds shows an increment from 101.67 MPa to 108.92 MPa upon the addition of 20% and 40% of chitosan, respectively. However, the compressive strength begins to decrease when the concentration of chitosan was higher than 50%. This is due to the hydrogen bonding that forms between these materials and chelation between two phases which increased their mechanical properties. These results were in agreement with data gained by Lou et al,⁶⁶ who stated that the compressive strength of poly-(l-lactic acid)/chitosan fiber (PLLA/CTSF) nanocomposite scaffolds increased upon the addition of chitosan fiber. In addition, the in vitro test shows the nanocomposite has potent bioactivity properties. The burn-out test indicates that hydroxyapatite nanoparticles are distributed uniformly into chitosan at a high percentage of chitosan in contrast to low chitosan percentage, the hydroxyapatite nanoparticles not fully attached by chitosan and merely act as a glue to link these grains homogeneously.

Figure 5.

Chemical structure of chitosan.

Notes: Adapted from Sami El-banna F, Mahfouz ME, Leporatti S, El-kemary M, Hanafy NAN. Chitosan as a Natural Copolymer with Unique Properties for the Development of Hydrogels. Appl Sci. 2019;9(11):2193 (doi.org/10.3390/app9112193).²⁶

The synthesis of chitosan film (CS) was done, incorporating hydroxyapatite/halloysite nanotubes (HA/HNTs) nanocomposite via hydrothermal technique to improve the differentiation and proliferation of MC3T3-E1 preosteoblast cells.¹²⁰ According to SEM analysis results, hydroxyapatite nanoparticles attach to HNTs surface inversely proportionally, and the nanoparticles dispersed uniformly on the surface of the tubes, linked by van der Waals forces¹¹⁵ that generated between them. When CS is reinforced to HA/HNTs nanotubes, the increment in tensile strength and elastic modulus is 48.31 MPa and 1427.4 MPa at dry condition, whereas for pure CS film it is only 28.61 MPa and 856.1 MPa, respectively. According to the literature, there are interlinkage forms by CS and nanotubes namely electrostatic interaction and hydrogen bonding.⁶⁴ The authors reveal that the CS reinforcement to HA/HNTs nanocomposites demonstrates good biocompatibility to induce cell differentiation. The acridine orange/ethidium bromide (AO/EB) staining indicated the cell differentiation and proliferation on CS/HA/HNTs nanocomposite was more preferable to bare CS and CS/HNTs nanocomposites. The experimental data were also in good agreement with alkaline phosphatase (ALP) activity results. The ALP activity of cells, when treated with the lowest ratio of HA/HNTs, 1–1 (denoted as CS/1-1), shows the greatest result among the groups, after 7 days of cell culture. In addition, the mineralization of calcium was significant on hydroxyapatite-containing nanocomposite in contrast to the pure CS film. This is because the hydroxyapatite content influenced the degree of mineralization that leads to calcium deposited on nanocomposite.

The degree of degradation was found to be faster than usual, due to the thermal transfer from hydroxyapatite particles being more efficient, which facilitates the breakdown of the chitosan structure.⁷⁸ However, usually, CS-HA is hybridized with other compounds so that it is suitable for bone regeneration application.

Alginate

Alginate is a type of anionic polymer that is usually extracted from brown seaweed.⁶² This natural polymer is used extensively as gel due to its features such as low-cost viability and hydrophilicity, and as it is biocompatible and biodegradable in normal physiological conditions. A scaffold made from hydroxyapatite, gelatin and alginate nanocomposite via titration of precursor materials (calcium chloride, sodium biphasic phosphate and gelatin/alginate solution) was found to be an excellent material to endow the crystallinity, the mechanical strength of hydroxyapatite and particle distribution on the scaffold surface for biomedical applications.¹⁰⁴ The functional groups of alginate, namely, β-D-manunronic and α-L-gluronic acids, bonded by 1–4 linkages and formed thermally stable calcium alginate upon the addition of calcium ion as shown in Figure 6.¹

Figure 6.

Formation of calcium alginate.

Besides, the hydroxyapatite particles were dispersed homogeneously, and a similar result was also found by Teng et al,¹⁰⁴ when the alginate was added at pH=10.⁵² This is because the negatively charged hydroxyapatite particles were repelling each other in conditions of high pH, and consequently the particles scattered. Furthermore, the interaction between alginate and hydroxyapatite forms stable hydrogels, due to the negative charge of alginate ions attracted to Ca²⁺ ion in hydroxyapatite,¹¹⁸ therefore, it formed a stable complex.⁵²

Trigonella Foenum-Graecum Seed Polysaccharide

Trigonella foenum-graecum seed polysaccharide (TFSP) is an annual leguminous plant usually found in Mediterranean countries, Europe, Northern India, Argentina and Egypt.²⁵ The polysaccharide is classified as a bioactive natural polymer and is broadly used in biomedical applications due to its antioxidant, antiviral, antitumor and anti-inflammatory properties.⁵¹ The hydroxyapatite-chitosan (HA-CS) nanocomposite and TFSP were synthesized via co-precipitation technique by Zia et al.¹²² The nanocomposite was proven suitable for biomedical applications due to its tremendous properties. The porosity of HA-CS nanocomposite reinforced with TFSP was 60.3 ± 0.17%, ie within the range of cancellous bone, 50–90%.⁵³ It proves that the presence of TFSP will increase the porosity and increase the surface area of the scaffold, and therefore it gives a pathway for protein adsorption, nutrient carriage, neo-vascularization, cellular shifting, drug diffusion and also better particle size distribution and surface roughness, which will facilitate cell attachment for tissue growth. This is due to functional groups of hydroxyapatite, CS and TFSP producing equilibrium linkages and forming a chemical bond that will give rise to the porosity of nanocomposite. The porous network structure of the nano-scaffold might be the reason for the better mechanical strength than HA-CS alone. Other than that, the high mechanical strength was also due to the hydrogen bonding produced between nanoparticles and the homogeneous distribution of particles when TFSP was added.

Besides the improvement of mechanical properties, the high water absorption capacity of the nanocomposite was attributed to the porosity structure paralleled with the hydrophilicity nature of TFSP which allows water to penetrate inside. Furthermore, TFSP was found to be compatible with living tissue because it does not have any toxic effect on erythrocytes and the degradation time of the nanocomposite shows more effectiveness instead of its binary nanoparticles in nature. This result is in good agreement with that of Ktari et al,⁵⁴ who observed that no hemolysis occurred even when the TFSP was added to the bovine erythrocytes. Moreover, the minimal inhibitory concentration (MIC) value of the nanocomposite was decreased due to the large surface area of the nanocomposite, which gives better contact and makes it easier to interrupt the cell wall of bacteria. As the MIC value decreases, a low concentration of the nanocomposite is needed to destroy the pathogen.⁵⁸ Therefore, it confirms that the anti-microbial properties of the nanocomposite are better improved upon the existence of TFSP. Nonetheless, the excessive amount of TFSP will increase the toxicity, decreasing cell viability and might have a negative impact on other cells as well. Therefore, the reinforcement of TFSP onto HA-CS nanocomposite will improve the resulting nanocomposite properties for bone tissue engineering.

Hydroxyapatite–Ceramic Nanocomposite

Montmorillonite

An ancient civilization utilized clay for tool making such as cooking utensils, pots and many others. Generally, the properties of clay are high-granularity structure made up of hydrated silicate, called phyllosilicates, and they have a diameter as small as 0.004 nm.¹⁰⁶ Several groups of clay can be used for various purposes namely talc, serpentine, smectite, etc. New research explores the uses of clay, especially montmorillonite (MMT), in biomedical studies due to their remarkable features. The sandwiched-like structure of montmorillonite consists of two tetrahedral layered and one octahedral at a 2:1 ratio. The presence of MMT can ameliorate the mechanical strength, improve porosity, lessen the fractures and degradation factor.⁷⁵

A scaffold made up of chitosan-hydroxyapatite-zinc oxide incorporated with organically modified montmorillonite (ZnCMH) was synthesized, and the mechanical strength reached the optimum value with the addition of only 5% of montmorillonite (OMMT), while the strength of the control sample (ZnCH) without OMMT was the lowest.⁸ The authors prepared samples with different percentages (wt%) of chitosan (CS) and OMMT at a constant ratio of 5% of hydroxyapatite-zinc oxide (HA-ZnO) and the control contained solely zinc, chitosan and hydroxyapatite (ZnCH) to favor the best properties of nanocomposite scaffold for bone tissue engineering. The tensile strength of all of the samples with OMMT is within the range of human trabecular bone between 10 and 3000 MPa.⁷⁴ Cao et al¹⁰ reported that chitosan-collagen nanocomposite with 5% addition of montmorillonite (MMT) demonstrates that the microstructures and interconnected pores in the nanocomposite contribute to the increased mechanical strength by maintaining its mechanical stability. Besides, hemolytic assay indicates blood compatibility (not causing harm to erythrocytes) with a value less than 7% upon the presence of zinc and OMMT. This result proved that the nanocomposite is non-toxic to human blood cells. The percentage of hemolysis that is acceptable is below 5%, and it is precisely stated as highly hemocompatible.⁴¹ The addition of 5% OMMT in the nanocomposite is at the optimum as it induces the proliferation of human osteoblastic MG-63 cells, whilst above 10% of OMMT content in the nanocomposite will hinder the cell growth.

Antibacterial assays of the nanocomposite were studied to indicate the effectiveness of the nanocomposite in combating bacterial growth such as Gram-positive bacteria, Bacillus cereus (B. cereus) and Lysinibacillus fusiformis (L. fusiformis), and Gram-negative bacteria, Escherichia coli (E. coli). ZnCMH I–III (refer to Table 1) nanocomposite exhibits a significant inhibition area against both Gram-positive and Gram-negative strains. This is due to each of the materials in the nanocomposite having good antibacterial properties. Therefore, the inclusion of OMMT is hemocompatible, induces cell proliferation, enhances the antibacterial activity and mechanical strength and makes it suitable for use in bone tissue engineering. Table 1 depicts the effects of OMMT on tensile strength, hemocompatibility, cell growth and antibacterial activity of the nanocomposite.

Table 1.

Effects of OMMT Towards Tensile Strength, Hemocompatibility, Cell Growth and Antibacterial Activity of HA-Based Nanocomposite

	CTS (%wt)	OMMT (%wt)	Tensile Strength (MPa)	Hemocompatible (%)	Proliferation of MG-63 Cells	Antibacterial Activity (mm)
						L. fusiformis	B. cereus	E. coli
ZnCH	95	0	16.16±0.32	5.5	Lowest	12.3±0.62	11.6±0.51	11.259
ZnCHM I	90	5	30.13±0.16	4	Highest	17.2±0.72	12.8±0.62	11.8±0.57
ZnCHM II	85	10	29.80±0.21	5	Moderate	18.0±0.58	13.5±0.58	12.4±0.55
ZnCHM III	80	15	23.07±0.26	7	Higher than control	12.3±0.62	14.1±0.51	12.9±0.68

Notes:Data from Bhowmick A, Lal S, Pramanik N, et al.⁸

Zirconia

Zirconia is known as bijou in ancient civilization. The crystalline dioxide of zirconium has mechanical strength similar to metal and the same color as teeth.⁷⁰ Zirconia can exist in three forms: it is monoclinic (M) at room temperature and stable in low temperature of 1170 °C; above 1170 °C it converts to the tetragonal (T) phase. When the temperature is higher than 2370 °C, it is in cubic (C) form, and this phenomenon is called polymorphism. Among these three phases, the T form has the properties of high strength, toughness and is more biocompatible than other phases. After heating to 1500–1700 °C, the surface started to expand and the created stresses lead to the surface breaking into small pieces.³⁰ The M-phase is feeble at room temperature, therefore, to prevent the T-phase from being converted to M-phase, a stabilization process is needed.⁷

Zirconia has a macroporous structure that gives it mechanical strength about seven times greater than hydroxyapatite. Therefore several efforts of research have been conducted in the coating of zirconia on hydroxyapatite surface to combine the bioactive properties of hydroxyapatite and mechanical strength of zirconia to produce a better structure and character of calcium phosphate composite for biomedical applications.^56,59 The large pore size and high porous density help cell proliferation and osteogenesis by enabling transportation of nutrients and gas conversion.¹²¹

Zhang et al¹¹⁹ employed the digital light processing (DLP) method to synthesize zirconia combined with hydroxyapatite. DLP is a common method used based on its high-speed processing and high precision to improve the competence of new materials. As a result, the mechanical strength of hydroxyapatite was increased, and the toughening effect of zirconia at 1200 °C and 1250 °C was also increased. Additionally, the unusual grain growth of pure hydroxyapatite without zirconia addition shows irregular particle size and shape, whilst the presence of zirconia resulted in the uniform microcrystal distribution and grain growth on the hydroxyapatite surface. The grain boundary shifting and grain growth of hydroxyapatite were the consequence of a smaller size of zirconia particles that adhered to the larger surface of zirconia during the sintering process.¹¹⁹ This result proves that the introduction of zirconia gives better mechanical strength and toughness to the ceramics. Moreover, the in vitro studies resulted in the elongated growth and assembling of the mouse bone mesenchymal stem cells (mBMSCs) that come from the rough surface of the composite.

Application of Hydroxyapatite-Containing Nanomaterials in Drug Delivery System

Osteomyelitis is inflammation of bone commonly caused by bacterial infection during bone implant. The three types of pathogen, namely Staphylococcus (notably Gram-positive S. aureus and S. epidermidis), Enterobacteriaceae and Pseudomonas, are responsible for osteomyelitis. As noted by Jensen et al,⁴⁰ the bacteria were adhered to the bone implants through the formation of biofilm, isolated part on the implant surface. The implant-associated infection arises as a serious problem since it causes perpetuated antimicrobial treatment and non-success of implants, therefore, several research works have been implemented to give us prospects for hampering bacterial adhesion and avoiding implant-related diseases. The traditional prophylaxis which delivers antibiotics (orally or injected) presumably has toxicity to the renal system and liver on account of the high dose of antibiotics intake and incomplete diffusion into the cells. Hence, another prominent area of research, the nanodelivery system, has been developed and administered for targeting drugs directly to diseased cells in the human body as well as minimizing side effects. A nanodelivery system employed nanoscale particles made up of materials designed at the molecular level which are usually tiny-sized so that they can easily move inside the human body. Nanodelivery systems essentially are intended to: transport the drug locally to the target location of the body in a controlled manner, reduce toxicity and side effects, improve patient relief by lowering the dose¹⁰⁸ and reducing manufacturing costs.⁹⁷ These systems combining antibiotics with a matrix serve as a vehicle that will transport drugs into desired cells.

There are two categories of matrix, viz. biodegradable and non-biodegradable. A non-biodegradable carrier, for instance, polymethyl methacrylate (PMMA) had been proven to prevent osteomyelitis effectively, but the non-biodegradable feature limits its use as a drug carrier since the beads need to be removed surgically afterward. In consequence, scientists were intrigued to employ biodegradable nanomaterials such as hydroxyapatite due to its privileged characteristics that would create novel opportunities in nanodelivery systems. Apart from biocompatibility and bioactivity properties, the adsorption abilities of hydroxyapatite, as it consists of positively charged surface, Ca²⁺, attracting anion and negatively charged ions, PO₄^3-, pairing with cation, make it convenient as a drug nanocarrier.

A study was conducted by Venkatasubbu et al¹⁰⁹ using alginate-doped hydroxyapatite nanoparticles with ciprofloxacin for drug delivery application. Ciprofloxacin is one of the common drugs widely used to obviate infection during bone implant due to it having a low minimum inhibitory concentration, as low as 0.25–2 mg/L. From the results gained, the drug-matrix ratio influenced the quantity of drug-load, and also 0.8 mg of ciprofloxacin is an optimum amount of drug-load for 1 mg hydroxyapatite nanoparticle. At first, the release of ciprofloxacin in a burst in native hydroxyapatite nanoparticles is probably due to leakage of hydroxyapatite volume, but the presence of alginate not only extended the drug release time but also release sustainably at a controlled rate. Ciprofloxacin (CFX) was again the choice of antibiotic for Albahy et al³ who investigated nano-hydroxyapatite (nHA) combined with multi-walled carbon nanotubes (MWCNTs) as a drug matrix. The authors disclosed that the hydroxyapatite-doped MWCNTs indicate higher drug-load than the native nHA due to influential effects from the MWCNTs. The drug release profile evinced that the prolonged release of CFX would be maintained for months with less of a burst effect and showing the minutest detrimental effects with the highest compliance. K-carrageenan crosslinked hydroxyapatite-chitosan hydrogel nanocomposite (Chito-Car-HA)-loaded CFX was synthesized by Reza et al,⁸⁸ aimed at the sustained release of the antibiotic. At 120 hours, a sustained and prolonged release of CFX was achieved with Chito-Car-HA nanocomposite through diffusion process. This result demonstrates the successful loading of CFX in the nanocomposite through the freeze-drying method. Despite drug release behavior, the authors observed the in vitro antibacterial study against two strains that often cause bone abnormalities and chronic osteomyelitis, viz. E. coli and S. aureus. The nanocomposite-capped CFX hydrogels indicate a significant zone of inhibition of bacterial growth because the CFX drug can mobilize simply in media and punctures the membrane of pathogen cells, hampering the DNA replication and pathogen growth.

Tang et al¹⁰³ were involved in the synthesis of gentamicin-loaded carbonated hydroxyapatite coatings (CHACs) using the lyophilization method. The CHACs were deposited on titanium plates and loaded in gentamicin solution at different doses. CHACs-loaded gentamicin indicates outstanding drug loading in comparison with titanium plates due to: (1) the surface area of CHACs increases the active sites of Ca²⁺ and PO₄^3- groups that would increase the affinity of carrier towards gentamicin antibiotic; (2) the mesopores and macropores present in the CHACs' structure control the drug diffusion at a specific rate as well as providing space for drug loading events; and lastly, (3) a low crystallinity of CHACs consists of interstitial space that would provide more active sites for drug molecule adsorption.

Contrastingly, titanium plates show low drug efficiency because of a lack of pores in their structure and an inappropriate surface area for drug loading. Consequently, there was no gentamicin release from titanium plate neither in low doses nor high doses because of low drug loading property and physical adsorption of gentamicin leading to drug leaking when soaking in PBS solution. As was foreseeable, the drug release profiles of gentamicin in CHACs plates present a stable and prolonged release up to 24 hours for both doses. The hydrogen bonding that held CHACs and gentamicin restrains the instant release of gentamicin from CHACs. Similarly, gentamicin-doped hydroxyapatite NPs complexed on coated titanium were prepared by the sol-gel coatings method and successfully demonstrated in drug delivery applications.⁷⁹ The authors evinced that the gentamicin was released within the time frame for prophylaxis during the peri- and post-operative period, which is up to 99% at a controlled rate after 48 hours. The addition of BMP-2 on the coating did not release tremendously, and it is not necessary for stimulating BMSC differentiation as well as promoting bone healing. Table 2 portrays a few examples of hydroxyapatite-based nanocomposites in drug delivery systems.

Table 2.

HA-Based Nanocomposites for Drug Delivery System

HA Nanocomposites	Drug Used	Drug Release Properties	Antibacterial Activity	Reference
HA-alginate	Ciprofloxacin	–	–	[6]
HA-MWCNTs	Ciprofloxacin	Sustained-release for a month	–	[3]
HA-K-carrageenan-chitosan	Ciprofloxacin	Sustained-release at 120 hours	A significant zone of inhibition against E. coli and S. aureus	[88]
Carbonated HA coatings on titanium plates	Gentamicin	Sustained-release up to 24 hours	A high content of gentamicin against S. epidermis	[103]
HA-coated titanium	Gentamicin	Sustained-release after 48 hours	Partially eliminates S. aureus and S. epidermis	[79]

Recent Patents on the Integration of Hydroxyapatite-Nanomaterials for Bone Tissue Engineering and Drug Delivery System

The hydroxyapatite-based nanocomposite scaffold has been explored widely in biomedical applications. Scientists tend to merge hydroxyapatite with other materials such as metals, polymers, ceramics, etc. Table 3 presents recent patents on hydroxyapatite-based nanocomposites combined with other substances for bone tissue engineering and drug delivery systems.

Table 3.

Recent Patents on Hydroxyapatite-Based Nanocomposites for Bone Tissue Engineering

Patents/Year	Method of Invention	Claims	Reference
CN 110665055/2020	The scaffold is produced by mixing calcium nitrate and ammonium phosphate to synthesize hydroxyapatite, the sericin solution taken from silkworm cocoons after being immersed in a lithium bromide aqueous solution.	A complex porous scaffold derived from sericin and nano-hydroxyapatite used as a carrier to monitor the growth factors of bone morphogen 2 by detecting the loading and release of the osteogenesis process.	[20]
CN 110898257/2020	Polymerization of polylactide-propylene glycol methacrylate and hydroxyapatite.	The photocurable composite produced for bone tissue engineering to improve the mechanical property, biocompatibility, biodegradability and porosity without using a toxic solvent.	[114]
CN 110639060/2020	3D bio-printed silk fibroin-based bone tissue engineering scaffold was prepared by mixing the silk fibroin fibers, lithium bromide, gelatin, hydroxyapatite and hyaluronic acid.	The 3D bioprinting silk fibroin produced from a short material preparation process with high solubility property to engage in body metabolism to induce the growth of osteoblast, non-toxic and cheap.	[63]
CN 109260525/2019	Calcium phosphate-based bioactive ceramic printing ink was prepared by mixing hydroxyapatite, tricalcium phosphate (TCP), binder (PVA) and ethanol. The 3D printing scaffold is produced using three-dimensional inkjet printing, selective laser etching (SLS), stereo light-curing molding and digital light processing (DLP).	The 3D-printing technology is used for controlling the shape and microporous structure of scaffold to repair hard tissue.	[14]
CN 109758609/2019	The 3D scaffold produced by mixing calcium chloride, zinc chloride, deionized water, creatine phosphate, chitosan and silk fibroin.	The composite that is composed of more than one material is preferred to improve the scaffold performance with a fine method of synthesis, simple and low cost.	[16]
CN109589450/2019	The method to synthesis-guided bone tissue regeneration is simple by mixing MXene and synthetic hydroxyapatite nanowires in a specific condition.	The addition of MXene as guided bone tissue regeneration material to separate different epithelial tissue in the growing process, as well as act as a supporter for bone scaffold and, potentially, prevent any infection.	[117]
US 20180071433/2018	The porous scaffold comprised: porous tannin powder particles, dried polyethylene glycol particles, hydroxyapatite, organic acid, formaldehyde solution and biodegradable polymer (polyurethane, polylactic acid, etc).	The bone graft is biocompatible with optimum porosity and pore diameter, high compressive strength and osteocompotent of stem cells stimulate bone growth.	[99]
CN 108339152/2018	A mixture containing aliphatic polyester-polyethylene glycol block copolymer, Span-80, Tween-60, stabilizer and silver nitrate.	The loaded silver nanoparticles can provide bacteriostatic activity, and the loaded hydroxyapatite provides osteogenic activity.	[86]
CN 108297396/2018	Mix gelatin, sodium alginate, water, nanoscale hydroxyapatite with the first freeze-drying treatment, curing treatment, cleaning and second freeze drying to produce a bone tissue engineering scaffold.	The 3D bone tissue engineering scaffold is produced through extrusion deposition type 3D printing, and this method will strengthen hydroxyapatite and increase the biological affinity of the scaffold.	[47]
CN 107982578/2018	The scaffold produced by reacting these materials: β-cyclodextrin (soft segment component for polyurethane synthesis), hexamethylene diisocyanate (hard segment component), nano-hydroxyapatite and stannous octoate (catalyst).	The nanocomposite scaffold has a porous structure with good biocompatibility and mechanical properties and a simple method with low cost.	[23]
CN 106421894/2017	Hydroxyapatite powder undergoes surface modification by stearic acid, mixing the hydroxyapatite powder and a poly-L-lactic acid solution and electrostatic spinning on a mixed solution.	The scaffold has a connected porous structure that gives a pathway for nutrient transmission, the hydroxyapatite material is not degraded easily, while the product of the degradation process is useful for human metabolism.	[27]
CN 106512099/2017	The method used in producing bone tissue engineering scaffold is by mixing chitosan, acetic acid, sodium hydroxide, deionized water and calcium chloride and dipotassium phosphate, to generate hydroxyapatite.	The scaffold has high compressive strength (1.5–4.5 MPa), larger pore size, uniform distribution of nano-acicular hydroxyapatite and better biological activity.	[43]
CN 107158477/2017	The ratio amount of hydroxyapatite/collagen powder added is 0.2–0.1% of lactoferrin then, filter and centrifuge at the suitable condition. The end product will be a freeze-dried process to remove impurities.	The composites have good biocompatibility, and the addition of lactoferrin will improve the osteogenic activity of the composite. The hydroxyapatite/collagen composite can release lactoferrin at an optimum rate.	[71]
CN 105963789/2016	The scaffold materials comprise gelatin, deionized water, hydroxyapatite, stearic acid (pore former), ethanol and glutaraldehyde (aid in the cross-linking process).	The method used to produce bone tissue scaffold is low cost, uses non-toxic materials, modifies the pore size of the scaffold to an optimum size and strengthens the hydroxyapatite up to 30 MPa.	[113]
US 20150343117/2015	The method used to produce collagen/HA composites directed press a collagen scaffold into a perfusion chamber of a closed-loop perfusion flow system and constantly delivering a mineralization perfusion fluid via collagen scaffold at an optimum rate and produce collagen/HA composites.	The collagen/HA composites that are prepared using dynamic intrafibrillar mineralization are able to give a stable environment with low cytotoxicity, biodegradable and convenient for human mesenchymal stem cell (hMSC) growth.	[42]

Conclusion

Among the nanomaterials, hydroxyapatite, which has a low cost, chemical similarity to the human bone, good bioactivity, biocompatibility and osteoconductivity, shows potential use as a material bone implant and drug carrier. Hydroxyapatite nanoparticles can be produced either naturally or synthetically by several methods, namely dry, wet and thermal methods. No matter what method was adopted, the control of particle size and surface morphology is still arduous until today. Furthermore, every method has pros and cons, in terms of morphology, stoichiometry, the crystallinity of synthesized hydroxyapatite, which depends upon its final application prerequisites in the biomedical area. Hence, these criteria should be fulfilled while employing a processing technique for the synthesis of hydroxyapatite nanocomposites.

From the bone tissue engineering viewpoint, the application of hydroxyapatite as a material bone implant is gaining prominence in the biomedical field. However, many research works reported that incorporation of hydroxyapatite with other nanomaterials is more suitable for bone replacement in comparison with native hydroxyapatite due to its limitation, especially low mechanical strength and antibacterial activity. An alternative approach focuses on enhancing the mechanical strength of hydroxyapatite so that it can withstand considerable stress to support cell growth as well as inhibit the growth of bacteria in bone tissue engineering applications. The combination of hydroxyapatite and other nanomaterials, viz. metals, polymers and ceramics, was proven to improve mechanical strength and antibacterial properties of hydroxyapatite without altering its morphology. Besides, a new formulation of hydroxyapatite is also intended to deliver drugs locally to a specific site of the human body. Necessarily, besides possessing biocompatibility, bioactivity and biodegradability features, bone-implant nanomaterials must have tolerable drug delivery properties and antibacterial properties without leaving any systemic toxicity effects.

Way Forward

Hydroxyapatite-based nanocomposite for biomedical applications has gained great interest due to its ability to communicate well with inside body components. To date, researchers are still working on ideal materials that can interact with hydroxyapatite, mimicking bone scaffolds while delivering drugs to targeted cells. It is also important to fully study the biological behavior of these substituted materials, and further studies, especially in vitro and in vivo, are necessary so that the process mechanisms such as biocompatibility, biodegradation, integration of bone cell as well as drug release behavior with the nanocomposite scaffold can be well understood. In addition, the ideal characteristics of a scaffold structure need to be evaluated to develop a hydroxyapatite-based scaffold with an optimum drug release system. This paves a new path for clinical studies.

Funding Statement

This project was supported by the Ministry of Higher Education of Malaysia under the Fundamental Research Grant Scheme, FRGS/1/2018/STG07/UPM/01/2, Vot no. 5540162.

Disclosure

The authors declare no conflicts of interest in this work.