Revue des Composites et des Matériaux Avancés-Journal

of Composite and Advanced Materials

Vol. 34, No. 2, April, 2024, pp. 125-132
Journal homepage: http://iieta.org/journals/rcma

Enhancing the Biocompatibility of Titanium Implants with Chitosan-Alginate Bio-

Composite Coatings Reinforced with HAP and ZnO
Hanaa A. Al-Kaisy1 , Rasha Abdul-Hassan Issa2 , Noor K. Faheed3* , Qahtan A. Hamad1
1
Department of Materials Engineering, University of Technology, Baghdad 10081, Iraq
2
Ministry of Higher Education and Scientific Research, Baghdad 10011, Iraq
3
Department of Chemical Engineering, College of Engineering, University of Misan, Amarah 10044, Iraq

Corresponding Author Email: noor.kf@uomisan.edu.iq

Copyright: ©2024 The authors. This article is published by IIETA and is licensed under the CC BY 4.0 license
(http://creativecommons.org/licenses/by/4.0/).

https://doi.org/10.18280/rcma.340201 ABSTRACT

Received: 18 September 2023 The current work aims to enhance the biocompatibility and antibacterial properties of
Revised: 10 February 2024 titanium implants using chitosan/Na alginate matrix composite as a coating layer
Accepted: 26 February 2024 reinforced with various ratios of hydroxyapatite (HAP) and ZnO by the Sol-Gel Dip
Available online: 29 April 2024 method resulting in a product of exceptional purity, a limited dispersion of particle sizes,
and the creation of a homogeneous nanostructure. The coating layer is characterized by
FE-SEM for microstructure observation. From the results, it was concluded that the
Keywords: precipitation of a bio-composite coating layer by Sol-Gel Dip was suitable for creating a
hydroxyapatite (HAP), ZnO, chitosan, Na strong, adherent biocompatible layer of chitosan/alginate with a thickness of about
alginate, biocomposite coating, Sol-Gel Dip (126.9µm). While the average diameter is approximately (21.5µm). The results showed
method that the dip-coating deposition method is very suitable for making CS-based composite
coatings reinforced with ZnO and HAP. From the anti-bacterial test results, it was found
that the addition of ceramic particles (HAP or ZnO) to the microstructure for the coating
samples revealed a uniform distribution of all types of the natural polymer coating layer
on the implants, indicating a suitable preparation and type of coating process (Sol-Gel
Dip Composite Coating), which also enhanced the coating's roughness property and
effective at inhibiting bacterial growth. This work revealed the assets of chitosan/Na
alginate matrix composites in various percentages, which have not been tried up to now
and could be very important for the development of the biomedical field.

1. INTRODUCTION for medical implants, surgical materials, and tissue adhesives

[10, 11]. Many biologically effective alternatives are used to
As compared to the attributes of metals, ceramics, and even replace part of the tissue (bone tissue, for example), using
composite materials, polymers' properties, particularly their polymeric natural materials such as chitosan, which are
mechanical aspects, must be improved in any manner possible characterized by their availability and good biological
[1]. As a result, polymer-based composites, which are properties (excellent biodegradation and similarity to natural
heterogeneous systems, improve toughness and strength with bone) [12-15].
high performance through the distribution of reinforcing The science of tissue engineering has shown a great deal of
particles [2-4]. The surface and mechanical properties are very potential in the natural ionic alginate polymer. It is very
important in choosing the material for any application, and the adsorptive and can be utilized to produce polymer scaffolds
most important of these properties for medical applications, since it is renewable, antimicrobial, and affordable. Because it
for example, is the nature of the material's surface, which is is compatible with human tissues, produces biological matter,
the first feature that interacts with the surroundings and thus and creates and maintains moisture around wounds, sodium
determines the fate of the material's performance [5]. Without alginate finds utility in tissue engineering technologies [16,
having an adverse effect, surface modification approaches can 17].
precisely enhance a surface's bio-performance characteristics It is anticipated that chitosan-alginate films with varying
and compatibility [6, 7]. Changing the surface of implanted ratios of mass combined with zinc oxide and HAP ceramic
biological substances can improve biocompatibility and nanoparticles, as reinforcements will offer several significant
reduce the incidence of associated illnesses [8]. Multiple medical benefits, such as film development, biological
technologies are now being used to improve the performance compatibility, broad antimicrobial properties, biodegradable
of medical implants, including the use of bioactive and high hemostasis, and superior attachment to injured tissues and
osseointegrated active coatings for metallic titanium substrates blood vessels [18].
[9]. One way to increase osseointegration is the use of coatings Hyaluronic acid, collagen, and chitosan are examples of

125
natural polymers that have demonstrated some inherent spectroscopy and differential scanning calorimetry techniques,
bioactive effects in tissues like cartilage tissue [19]. Natural correspondingly, the effects of SS and HAP on the chemical
polymers provide the means to recognize the biological system structure and thermal characteristics of the bio epoxy were also
as a result of their macromolecular composition resembling assessed. These composites are an intriguing prospect that
tissues. This further results in the aversion of problems with could be employed in the orthopedic area, according to the
toxicity and activation of a chronic inflammatory response, as results. Hamad et al. [29] created a novel coating made of
well as the absence of recognition by cells, which are chitosan and alginate that incorporates nano-titanium dioxide
commonly induced via numerous artificial polymers [20]. (TiO2) and nano-niobium (V) oxide as reinforcement materials
It has high biocompatibility and does not cause risks of to create a bio-composite layer using the dip coating technique.
disease transmission or immune rejection. It is mainly utilized The findings demonstrated that coatings incorporating
in many biomedical uses, especially in the arrangement of nanoparticles had an identical antibacterial impact as coatings
bone fillers, coating materials for metal implantations, etc. made of chitosan and alginate. Additionally, lowering
[21]. Evaluation of the influence of a sodium alginate coating bacterial activity for all kinds of nanoparticles that target the
encumbered with ascorbic acid on the lifecycle of samples was bacteria, stopping cell proliferation, and strengthening the
first coated in a sodium lactate solution. The samples were composite material's antimicrobial properties.
analyzed in terms of sensory and microbiological One of the main things to be worried about with metallic
characteristics. The sample covered with ascorbic acid showed devices in human beings is corrosion, which not only erodes
the longest projection life, which was about 60% longer than the implant but also runs the danger of contaminating bodily
the control group [22]. The growth of ZnO nanoparticles in fluids and tissues with ions of metal. Two avenues exist that
chitosan coatings is caused by the use of chitosan-based allow this corrosion to happen. Wear (as in synthetic joints)
overlay coatings for antimicrobial medical uses, such as the and electrochemical deterioration cause physical erosion.
reinforcement of chitosan coatings with ZnO nanoparticles in Applying a bio composite layer that encourages bone cell
various weight ratios [23]. attachment and proliferation to the implant's metallic surface
Ahmed et al. [24] improved the bone impedance and is one way to improve osseointegration and assist shield it
corrosion resistance of 316 L stainless steel by using from ions that could cause corrosion.
electrophoresis methods. Various HAP-Zein coatings are This paper provides a comprehensive, analytical evaluation
being deposited. With improvements in biological of the use of dip-coating deposits to establish a composite
environment performance and high-capacity simulated body coating consisting of sodium alginate and chitosan that is
fluid (SBF) adherence. Hamad et al. [25] produced a thin poly strengthened with zinc oxide and hydroxyapatite, to improve
(methyl methacrylate) resin coating film from several the exterior of a pure titanium alloy, and to develop
bioceramics as strengthening constituents by utilizing the dependable, portable, and useable systems, along with a
electrostatic deposition method. The mechanical review of their challenges, shortcomings, and potential. It is
characteristics were enhanced, and the coating layers' surfaces widely utilized for implantable items such as dental crowns,
were homogenous without cracking defects. The composite artificial hip and knee joints, and bone plates, that restore
coating was compact with consistent dispersants and persistent injured hard tissue. In closing, the author discusses possible
with a homogenous mix inside the coating, according to the future paths for the creation and improvement of innovative
SEM&EDX findings. To enhance coating layer characteristics, biomaterials with a wider range of improved biological uses.
Hamad et al. [26] employed various bioactive reinforcements
(biotin and hydroxyapatite) in varied amounts (5% and 10%).
The dip-coating procedure was utilized to apply coatings to 2. MATERIALS AND METHODS
pure Ti, SS 316L, and SS 304 substrates. Sample evaluation
comprises contact angle measurement (wettability), MTT, and 2.1 Manufacture of testing samples
a microstructure statement using field emission scanning
electron microscopy (FE-SEM). The results show that adding As a substrate, pure Ti discs with square specimen
metallic elements and those with varying particle sizes dimensions (2cm*2cm*1mm) were used. This alloy's
enhanced the mixtures in the alginate matrix, improving the chemical composition was 0.08 C wt.%, 0.015 H wt.%, 0.05
composite materials' overall qualities. This had an additive N wt.%, 0.51 Fe wt.%, and the rest Ti wt.%). The test was
impact on the composite materials' attributes. To improve and conducted at the State Company for Examination and
develop the surface properties of this metal, Hamad et al. [27] Engineering Rehabilitation. Carbide silicon sheets of 200 and
created a CS-based composite coating augmented with 400 grit are used to polish surfaces to get a uniform surface
nanosilver and biotin that was deposited on a pure Ti substrate condition before the coating process.
using a dip-coating process. Field emission scanning electron The chitosan-sodium lignite bio-coating ratio that was
microscopy, atomic force microscopy (AFM), Fourier selected was 70:30. In the chitosan coating specimen, 0.75g of
transforms infrared (FTIR), and wettability experiments were chitosan nano-powder was immersed in 4ml of dilute acetic
used to examine the surface morphology of the unique CS acid, creating a milky mixture. After that, the solution is put
composite coating. Findings indicate that using various on a magnetic moving plate to guarantee homogeneity and get
particle sizes helps improve the mixtures in alginate, having a rid of any bubbling that may have formed. The NaOH solution
twofold impact on the film's characteristics. Hadi et al. [28] was removed, raising the pH level to 6.0. Next, 10 milliliters
evaluated two nanocomposite structures made from bio-epoxy of water were used to dissolve 0.25 grams of sodium alginate.
and readily accessible HAP and bio-epoxy and seashell (SS) After mixing the two solutions of polymers for ten minutes
nanoparticles, both of which could be utilized in bone at 350rpm, the mixture was homogenized. Employing a
substitution. Both fillers had nanoparticles that were 50nm in magnetic stirrer, the previously prepared material was once
size, and the percentages of the strengthening phase were 1, 3, more stirred for 60 minutes at the ambient temperature. A
7, and 15 wt.%. Utilizing the Fourier transform infrared variety of ceramic powders were utilized to create coatings for

126
metal substrate samples. A sieve analyzer was utilized to sift Figure 2.
every kind of powder within the 50-150μm range. A composite
coating layer consisting of natural polymer-based materials
strengthened with reinforcement has been deposited using the
dip coating process.
The precursor mixture is submerged in the substrate.
Continue moving forward at a steady pace for thirty minutes,
or until the specimen's whole surface is thoroughly moistened
with the coating reagent. The substrate was pulled forward at
a consistent speed to carry out the drainage and deposition
processes. The film is deposited, or a tiny layer of the solution
containing the precursor is retained. Liquid availability. It will
emerge from the top. After that, the specimen is dried outside
for the solvent to evaporate and leave behind a thin film of Figure 2. Composite and coating fabrication practice
precipitate.
The dip coating technique has been utilized to deposit a 3.1 Field emission scanning electron microscopy (FESEM)
coating film of HA/ZnO-based natural polymer with
reinforced materials, as presented in Table 1. Field emission scanning electron microscopy (FESEM) was
A metal screening equipment with revolving plate utilized to assess the morphologic characteristics of all
technology produced a smooth surface. To provide the sample composite films according to (ASTM F1372) standards. In
surface with a consistent form, silicon carbide films were used addition, the microstructural analysis of samples employing
to polish the bare surfaces of the specimens. 400, 500, 600, FESEM. To fit inside the apparatus, the testing material was
and 800 grit SiC films were employed. to be polished. 100rpm divided into tiny pieces. Each sample is first blasted with gold
rotational speed. The specimen must be rotated 90 degrees from the surface to the edge to accomplish optimum electric
between phases to achieve adequate grinding, and the grinding conductivity. After that, secondary electron pictures are
angle must always be the same throughout the grinding captured while maintaining a working voltage of 10Kv.
process. The specimens were disinfected with liquid methanol
to eliminate any surface contaminants to guarantee scratch- 3.2 Inhabitation of bacterial test
free top polishing with rough diamonds. After that, the
specimens were air-dried and cleaned in deionized water. To measure the inhibition of bacterial growth and resistance
Then, we repeat the same previous steps to prepare the to antibiotics, the area of residence test in clinical settings is
coating solution by adding zinc oxide and apatite hydroxide at used according to (ASTM E2149-10) standards. The usual
a ratio of 15%. Ti samples are immersed in the coating solution diffusion technique with agar wells was used to test the
for 30min. Samples are left treated with a natural polymer- synthetic powders' antibacterial effectiveness against two
based coating. The samples are then taken out of the solution types of bacteria: S. aureus and E. coli. Müller-Hinton agar
and dried at room temperature in the open air. Figures 1 and 2 was used for the diffusion test. The diffusion approach
show the steps of the biocomposite coating samples in this involves adding a dense inoculum of the microorganisms
study. FESEM, EDS, and the biological activities of the under investigation to Petri plates to produce 4 mm thick
prepared natural polymer matrix of the polymer biocomposite layers and semi-confluent growth. Coating layer specimens
the coating was made with different ceramic particles. were soluble in pure water at a concentration of 250µg/ml to
create the test solutions. Solution specimens were placed on
Table 1. Samples on pure Ti substrate agar and maintained at 37℃ for 24 hours. The larger the
Inhibition Zone Size the larger the antibacterial activity of the
- Composition of Coating wt.% tester, and the larger the diameter of the inhibition area usually
1 (70% chitosan+30% Na alginate) matrix
indicates that the sample is more active [30].
2 15% HA+85% matrix
3 15% ZnO+85% matrix
4 7.5% HA+7.5% ZnO+85% matrix 3.3 Energy dispersive spectroscopy (EDS)

The analysis portion of the EDS system functions as a

function that integrates into SEM devices. EDS analysis was
performed on specimens utilizing bulk analysis, which is
supplied by "TESCAN Vega II XMU" and yields semi-
quantitative values of the parts. These powders underwent an
EDX test following (ASTM E1508-12a) standards to
determine the chemical composition of their constituent parts.
Between 5nm and 2 microns is the beam width, and it performs
Figure 1. The steps of preparation of the biocomposite at elevated voltages of 2 to 50kV.
coating

4. RESULT AND DISSOCIATION

3. METHODOLOGY
4.1 Morphological analysis
Coating and composite fabrication procedures may be
presented in the arrangement of a diagram as displayed in Figure 3 indicates the FESEM/EDS images for the chitosan

127
with Na-alginate composite coating, which is reinforced with
ZnO and HA by the Sol-Gel Dip method. A typical structure
of a polymer matrix (a homogeneous porous film) was
observed. The chitosan/alginate matrix of the polymer coating
is shown in Figure 3 (a) without any additions. The exterior of
the substrate was seen to be consistently smooth. After a
uniform coating of Chi-Alg was put on, the textured surface of
the Ti substrate showed no visible pores [31]. With no major
defects and a small amount of porosity that helps to promote
osseointegration, Figure 3 (b) showed a uniform dispersion of
the ZnO ceramic nano-particles across the coating's
Chito/ALg matrix. The incorporation of 15 vol. % ZnO into
the matrix resulted in a heterogeneous surface appearance,
which dramatically altered the surface's shape and increased
its roughness [32]. As illustrated in Figure 3 (c), the uniform
and smooth surface layer of the coated surface, the consistent
quality, and the rather uneven dispersion of the HAP ceramic
particles were noted. Surface adhesion increased because of
the natural polymeric coating's surface texture forming with
uniform dispersion and high bonding after 15% HAP was (b) ZnO/Chitosan+alginate matrix
added to its structure [26]. The uneven form of the inorganic
component and the rather irregular distribution of particles in
the matrix completely changed the surface's morphology, as
seen in Figure 3 (d) particularly after being strengthened with
HA and ZnO particulates, a chitosan/alginate layer developed
and coated the whole surface. The accumulated layer's
morphology was substantially different from the pure coating.
Particle size variations resulted in a rougher composite surface
with preferred homogeneity because of the reinforcing
particles' consistent distribution in the substrate and an
excellent relationship of granular sizes among them.
Therefore, combining various types of reinforcing materials
results in a high-quality coating substance with favorable
surface biological characteristics. It is simpler to improve the
interactions between the elements in the matrix when varied
particle scaling sizes are used. A preferred combination of
particulate strengthening substances with an improved dual
impact on enhancing the general characteristics of the
composite film is produced as a consequence of the large
surface area of ZnO particles increasing the attraction forces (c) HA/Chitosan+alginate matrix
and facilitating biotin precipitate at the surface of the HA
particle [33, 34].

d) ZnO+HA/Chitosan+alginate matrix

Figure 3. FESEM images of the (a) Chitosan+alginate matrix,

(a) Chitosan+alginate matrix (b) ZnO/Chitosan+alginate matrix, (c) HA/Chitosan+alginate
matrix, and (d) ZnO+HA/Chitosan +alginate matrix biocomposite
coating layer at different magnifications

128
 Figure 5. FESEM/EDS of (A) HA/chitosan+algenate, (B)
ZnO/chitosan+algenate and (C) ZnO+HA/chitosan+algenate
Composite coated Ti substrate

Furthermore, a high degree of adhesion with the surface is

perceived from coated sample images, as presented in the
Figure 3. The accumulation of ceramic particles in the matrix
leads to the formation of cluster-like particles that form fine
particles on the surface. It can be depicted that the
reinforcement with ceramic particles (ZnO/HA) increased the
surface roughness of the coating due to the formation of the
microspheres on the material's surface during deposition. The
composite coating thickness of ZnO+HA within the polymer
matrix sample was measured from the SEM micrograph
(Figure 4) and was about (126.9µm). While the average
diameter is approximately 21.5µm.
Figure 5 indicates the FESEM/EDS images for the
composite coating of ZnO/HA within the polymer matrix.
FESEM of HA showed only a few small particles of calcium
and phosphor within the polymer coating due to the few
additional percent, and the result analysis of the HA composite
coating showed (11.27 wt.% Ca), (0.0.39 wt.% Phosphor) and
the result analysis of the HA composite coating showed (11.27
wt.% Ca), (0.0.39 wt.% Phosphor), with 4.51 wt.% C and 4.08
wt.% O, as shown in Figure 5 (a). While for ZnO within the
polymer matrix, the clusters of zinc oxide within composite
coating film are formed with weight percents of Zn, C, and O
in EDS analysis of 2.04 wt.%, 2.57 wt.%, and 5.32 wt.%,
Figure 4. FESEM images of (a) average diameter and (b) respectively, the C percent was (8.78 wt.%) in ZnO+HA
thickness coated of the ZnO+HA/chitosan-alginate composite composite coating as shown in Figure 5 (b). While revealing
coated layer cross-section more particles of hydroxyapatite within the natural polymer
matrix, reaching Ca weight percentage of 22.75, P 0.43%, and
decreasing in Zn content to 1.48%, respectively, as shown in
Figure 5 (c) [29]. The EDS leads to also clearly shows that the
C % significantly decreased. This is likely due to the raised
depletion of the ceramic powdered substances, which will
allow for greater diffusion and coupling with the matrix. This
will give the coating the required protection, but it may also
occasionally lead to an upsurge in cracking because of
compressive stresses being generated at the coating layer [35].

4.2 Inhibition of bacterial test

Figures 6 and 7 show the size of the housing area of bacteria

for the composite coating layer (ZnO+HA+chitosan-alginate).
The findings in Figure 6 demonstrated that by reducing the
level of activity of bacterial growth and proliferation cycle at
the composite's surface, the addition of metallic nanoparticles
as strengthening elements to the polymer matrix improved the
antibacterial performance of the entire composite. The
development of bacteria was limited to the composite coating,
demonstrating its capacity to prevent bacterial growth with a
rise in the hydroxyapatite or zinc percentage, but it was

129
significantly reduced for pure matrix films [33]. This outcome (2) The surface morphology determined by FESEM
is brought about by the polymer composite layers' constant analysis of the bio-composite polymer base coating showed
hydrophilic character, which outperforms pure coatings and different sizes and shapes of particles embedded in the matrix
promotes reduced bacterial adhesion. We further infer that for with a uniform layer of chitosan/alginate with a thickness of
the composite layer (HA/ZnO inside chitosan+alginate), its about (126.9µm). While the average diameter is
antibacterial effect versus Escherichia coli was greater than approximately (21.5µm).
that against S. aureus. Nonetheless, the bio-coating clusters on (3) The scanning electron microscope (SEM) images of the
titanium substrates generally demonstrated strong suppression Chi-Alg formed composite coating boosted with ZnO and
of the bacterial development zone, demonstrating acceptable HAP nanoparticles demonstrated uniform adhesion among the
biocompatibility to be utilized as an implant coating in medical coating and the substrate, demonstrating the suitability of the
devices [36]. dip coating technique.
Figure 7 illustrates the diameter of the inhibition zone (mm) (4) EDS mapping showed that there is a high concentration
for composite material samples. The increase in the diameter of Ca, phosphorus, and Zn near the surface within the polymer
of the inhibition zone is due to the double effect of the ceramic matrix, especially at (ZnO+HA), which gives sufficient
particles on the cell walls of both bacteria [37]. In addition, surface area for diffusion and the creation of more coupling
due to the nature of the microstructure, the additive ceramic between the coating layers.
particles precipitated in the (chitosan+alginate) natural (5) The size and diameter of the inhibition area of the
polymer matrix due to the large differences in particle size and different composite coating samples (HA and
surface charge, making the composite surface rougher with ZnO/chitosan+alginate) are larger than those of the pure
preferred homogeneity, which helped to promote and prevent matrix, indicating their possible ability to inhibit bacterial
cell growing and increase the antimicrobial performance of the growth and effective biocompatibility.
composite materials [29]. (6) Although access to information and time are restricted.
The results of this study suggest that these various coatings can
be used as a starting point for more investigation and
development in the area of biomedical surface engineering.

ACKNOWLEDGMENT

The authors would like to thank all the operations at the

University of Technology-Baghdad.

Figure 6. Diameter of the inhabitation zone of different REFERENCES

composite coating samples
[1] Park, J., Lakes, R.S. (2007). Biomaterials: An
introduction. Springer Science & Business Media.
[2] Yoruç, A.B.H., Sener, B.C. (2012). Biomaterials, a
roadmap of biomedical engineers and milestones.
Retrieved from InTech: http://www. intechopen.
com/books/a-roadmap-of-biomedical-engineers-and-
milestones/biomaterials
[3] Isa, Z.M., Hobkirk, J.A. (2000). Dental implants:
Biomaterial, biomechanical and biological
considerations. Annals of Dentistry University of Malaya,
7(1): 27-35. https://doi.org/10.22452/adum.vol7no1.6
[4] Anselme, K. (2000). Osteoblast adhesion on
Figure 7. Size of the inhabitation zone in agar plate different biomaterials. Biomaterials, 21(7): 667-681.
samples https://doi.org/10.1016/S0142-9612(99)00242-2
[5] Faheed, N. K., Hamad, Q. A., Issa, R. A. H. (2024).
Investigation of the effect of thermal, mechanical, and
5. CONCLUSIONS morphological properties of bio-composites prosthetic
socket. Composite Interfaces, 31(3), 331-355.
A composite coating made of chitosan/Na alginate matrix [6] Bashar, S., Al-Kaisy, H.A., Al-Shroofy, M.N. (2022).
and strengthened with hydroxyapatite and ZnO was created Preparation of bio-composite coatings on titanium
using the dip-coating deposition process. The matrix substrate by electrostatic spray deposition. Key
reinforcement with varying particle sizes enhances the Engineering Materials, 937: 129-138.
characteristics of the composite such as (morphological https://doi.org/10.4028/p-224uc8
properties, and antibacterial activity): [7] Jayaswal, G.P., Dange, S.P., Khalikar, A.N. (2010).
(1) The polymer coatings were enriched with active ceramic Bioceramic in dental implants: A review. The Journal of
powders (HA and ZnO with a natural polymer matrix). It was Indian Prosthodontic Society, 10: 8-12.
characterized by continuity, and homogeneity, and consisted https://doi.org/10.1007/s13191-010-0002-4
of a lamellar structure with flattened particles of different [8] Hornat, C.C., Urban, M.W. (2020). Shape memory
shapes and sizes. effects in self-healing polymers. Progress in Polymer

130
 Science, 102: 101208. [23] Boura-Theodoridou, O., Giannakas, A., Katapodis, P.,
https://doi.org/10.1016/j.progpolymsci.2020.101208 Stamatis, H., Ladavos, A., Barkoula, N.M. (2020).
[9] Swain, S.K., Bhattacharyya, S., Sarkar, D. (2011). Performance of ZnO/chitosan nanocomposite films for
Preparation of porous scaffold from hydroxyapatite antimicrobial packaging applications as a function of
powders. Materials Science and Engineering: C, 31(6): NaOH treatment and glycerol/PVOH blending. Food
1240-1244. https://doi.org/10.1016/j.msec.2010.11.014 Packaging and Shelf Life, 23: 100456.
[10] Islam, M.S., Todo, M. (2016). Effects of sintering https://doi.org/10.1016/j.fpsl.2019.100456
temperature on the compressive mechanical properties of [24] Ahmed, Y., Yasir, M., Ur Rehman, M.A. (2020).
collagen/hydroxyapatite composite scaffolds for bone Fabrication and characterization of zein/hydroxyapatite
tissue engineering. Materials Letters, 173: 231-234. composite coatings for biomedical applications. Surfaces,
https://doi.org/10.1016/j.matlet.2016.03.028 3(2): 237-250, https://doi.org/10.3390/surfaces3020018
[11] Gammariello, D., Incoronato, A.L., Conte, A., Del [25] Hamad, Q. A., Rahman, H. J. A., Faheed, N. K. (2023).
Nobile, M.A. (2016). Effect of sodium alginate coating Improving some mechanical properties of green
with ascorbic acid on shelf life of raw pork meat. Journal biocomposite by natural pumpkin powders for prosthetic
of Food Technology Research, 3: 1-11. socket. In AIP Conference Proceedings (Vol. 2787, No.
http://doi.org/10.18488/journal.58/2016.3.1/58.1.1.11 1). AIP Publishing.
[12] Dhafer, G., Al-Shroofy, M.N., Al-Kaisy, H.A. (2022). [26] Hamad, Q.A., Al-Hasani, F.J., Faheed, N.K. (2022).
Electrostatic deposition of poly (Methyl Comparative study of biotin and hydroxyapatite on
Methacrylate)/Titanium carbide coatings on austenitic biological properties of composite coating. International
316L stainless steel implant. Engineering and Journal of Biomaterials, 2022.
Technology Journal, 40(6): 918-925. https://doi.org/10.1155/2022/8802111
http://doi.org/10.30684/etj.2022.131478.1038 [27] Hamad, Q.A., Al-Kaisy, H.A., Al-Shroofy, M.N.,
[13] Hamad, Q.A., Abed, M.S. (2019). Investigation of thyme Faheed, N.K. (2023). Evaluation of novel chitosan based
and pumpkin nanopowders reinforced epoxy matrix composites coating on wettability for pure titanium
composites. Journal of Mechanical Engineering implants. Journal of Renewable Materials, 11(4): 1601-
Research and Developments (JMERD, 42: 153-157. 1612. http://dx.doi.org/10.32604/jrm.2023.023213
http://doi.org/10.26480/jmerd.05.2019.153.157 [28] Hadi, A.N., Mohammed, M.R. (2022). Performance of
[14] Scaffaro, R., Lopresti, F., Maio, A., Sutera, F., Botta, L. biocomposite materials reinforced by hydroxyapatite and
(2017). Development of polymeric functionally graded seashell nanoparticles for bone replacement. Journal of
scaffolds: A brief review. Journal of Applied Nanotechnology, 2022.
Biomaterials & Functional Materials, 15(2): 107-121. https://doi.org/10.1155/2022/9156522
https://doi.org/10.5301/jabfm.5000332 [29] Hamad, Q.A., Abdulrahman, S.A., Issa, R.A.H. (2022).
[15] Yoruc, A.B.H., Sener, B.C. (2012). A roadmap of Investigation some characteristics of biocomposites
biomedical engineers and milestones biomaterials. coating for biomedical implants. Key Engineering
InTech Janeza Trdine, Croatia. Materials, 936: 3-11. https://doi.org/10.4028/p-nt9b2f
[16] Devi, N., Dutta, J. (2017). Preparation and [30] Ullah, I., Siddiqui, M.A., Liu, H., Kolawole, S.K., Zhang,
characterization of chitosan-bentonite nanocomposite J., Zhang, S., Ren, L., Yang, K. (2020). Mechanical,
films for wound healing application. International biological, and antibacterial characteristics of plasma-
Journal of Biological Macromolecules, 104: 1897-1904. sprayed (Sr, Zn) substituted hydroxyapatite coating. ACS
https://doi.org/10.1016/j.ijbiomac.2017.02.080 Biomaterials Science & Engineering, 6(3): 1355-1366.
[17] Cervini-Silva, J., Ramí rez-Apan, M.T., Kaufhold, S., https://doi.org/10.1021/acsbiomaterials.9b01396
Ufer, K., Palacios, E., Montoya, A. (2016). Role of [31] Kadhim, N.N., Hamad, Q.A., and Oleiwi, J.K.(2020)
bentonite clays on cell growth. Chemosphere, 149: 57-61. “Tensile and morphological properties of PMMA
https://doi.org/10.1016/j.chemosphere.2016.01.077 composite reinforced by pistachio shell powder used in
[18] Archana, D., Singh, B.K., Dutta, J., Dutta, P.K. (2013). denture applications,” in Proceedings of the 2nd
In vivo evaluation of chitosan-PVP-titanium dioxide International Conference on Materials Engineering &
nanocomposite as wound dressing material. Science (IConMEAS) AIP Conf, Baghdad, Iraq, March
Carbohydrate Polymers, 95(1): 530-539. 2020.
https://doi.org/10.1016/j.carbpol.2013.03.034 [32] Oleiwi, J.K., Hamad, Q.A., Rahman, H.J.A. (2018).
[19] Ambrosio, L. (2017). Biomedical composites. Tensile properties and morphological test of heat cured
Woodhead Publishing. acrylic resin reinforced by natural powders. International
[20] Boccaccini, A.R., Ma, P.X., Liverani, L. (Eds.). (2021). Journal of Mechanical and Production Engineering
Tissue engineering using ceramics and polymers. Research and Development, 8(6): 325-334.
Woodhead Publishing. [33] Hussein, M.A.K. (2022). Preparation of PMMA/SiO2
[21] Faheed, N.K., Hamad, Q.A., Oleiwi, J.K. (2022). Tensile composite sheets for tribological and mechanical tests.
and stress analysis of hybrid composite prosthetic socket Misan Journal of Engineering Sciences, 1(1): 58-68.
reinforced with natural fibers. Journal of Renewable https://doi.org/10.61263/mjes.v1i1.22
Materials, 10(7): 1989-2013, [34] Mohammed, S., Karim, A.A., Thamer, A.Z. (2023).
https://doi.org/10.32604/jrm.2022.017573 Experimental study on the effect of size, type, and
[22] Al-Hasani, F. J., Hamad, Q. A., Faheed, N. K. (2024). replacement ratio of recycled aggregate on the
Enhancing the cell viability and antibacterial properties mechanical properties of reactive powder concrete.
of alginate-based composite layer by adding active Misan Journal of Engineering Sciences, 2(1): 38-52.
particulates. Discover Applied Sciences, 6(2), 70. https://doi.org/10.61263/mjes.v2i1.43

131
[35] Issa, R.A., Al-Shroofy, M.N., Al-Kaisy, H.A. (2021). engineering: A review of recent advances. Misan Journal
Al2O3-TiO2-PMMA Bio-Composite Coating via of Engineering Sciences, 1(1): 33-46.
Electrostatic Spray Technique”, Journal of Engineering https://doi.org/10.61263/mjes.v1i1.18
Technology, 39: 504-511. [37] Faheed, N.K. (2024). Advantages of natural fiber
[36] Mohammed, M.R. (2022). Mechanical and biological composites for biomedical applications: A review of
behaviour of 3D printed PCL-based scaffolds fabricated recent advances. emergent materials, 7 :63–75.
by fused deposition modelling for bone tissue https://doi.org/10.1007/s42247-023-00620-x

132