Next Article in Journal
Novel Injectable Fluorescent Polymeric Nanocarriers for Intervertebral Disc Application
Next Article in Special Issue
Ciprofloxacin Release and Corrosion Behaviour of a Hybrid PEO/PCL Coating on Mg3Zn0.4Ca Alloy
Previous Article in Journal
A Review on Phyto-Therapeutic Approaches in Alzheimer’s Disease
Previous Article in Special Issue
Bioactive Silicon Nitride Implant Surfaces with Maintained Antibacterial Properties
 
 
Search for Articles:
Title / Keyword
Author / Affiliation / Email
Journal
Article Type
 
 
Advanced Search
 
Section
Special Issue
Volume
Issue
Number
Page
 
Journals
JFB
Volume 14
Issue 2
10.3390/jfb14020051
jfb-logo
Submit to this Journal Review for this Journal Propose a Special Issue
► Article Menu

Article Menu

share Share announcement Help format_quote Cite question_answer Discuss in SciProfiles thumb_up
...
Endorse textsms
...
Comment
first_page
settings
Order Article Reprints
Font Type:
Arial Georgia Verdana
Font Size:
Aa Aa Aa
Line Spacing:
Column Width:
Background:
Article

Gallium-Doped Hydroxyapatite Shows Antibacterial Activity against Pseudomonas aeruginosa without Affecting Cell Metabolic Activity

by
Marika Mosina
1,2,
Claudia Siverino
3,
Liga Stipniece
1,2,
Artemijs Sceglovs
1,2,
Renats Vasiljevs
1,2,
T. Fintan Moriarty
3 and
Janis Locs
1,2,*
1
Rudolfs Cimdins Riga Biomaterials Innovation and Development Centre, Institute of General Chemical Engineering, Faculty of Materials Science and Applied Chemistry, Riga Technical University, Pulka 3, LV-1007 Riga, Latvia
2
Baltic Biomaterials Centre of Excellence, Headquarters at Riga Technical University, LV-1048 Riga, Latvia
3
AO Research Institute Davos, 7270 Davos, Switzerland
*
Author to whom correspondence should be addressed.
J. Funct. Biomater. 2023, 14(2), 51; https://doi.org/10.3390/jfb14020051
Submission received: 15 December 2022 / Revised: 4 January 2023 / Accepted: 11 January 2023 / Published: 17 January 2023
(This article belongs to the Special Issue Advances in Biomaterials Engineering)
Browse Figures
Review Reports Versions Notes

Abstract

:
Calcium phosphates (CaPs) have been used in bone regeneration for decades. Among the described CaPs, synthetic hydroxyapatite (HAp) has a chemical composition similar to that of natural bone. Gallium-containing compounds have been studied since the 1970s for the treatment of autoimmune diseases and have shown beneficial properties, such as antibacterial activity and inhibition of osteoclast activity. In this study, we synthesized hydroxyapatite (HAp) powder with Ga doping ratios up to 6.9 ± 0.5 wt% using the wet chemical precipitation method. The obtained products were characterized using XRD, BET, FTIR, and ICP-MS. Ga3+ ion release was determined in the cell culture media for up to 30 days. Antibacterial activity was assessed against five bacterial species: Pseudomonas aeruginosa, Escherichia coli, Staphylococcus aureus, Staphylococcus epidermidis, and Streptococcus pyogenes. The biocompatibility of the GaHAp samples was determined in human fibroblasts (hTERT-BJ1) through direct and indirect tests. The structure of the synthesized products was characteristic of HAp, as revealed with XRD and FTIR, although the addition of Ga caused a decrease in the crystallite size. Ga3+ was released from GaHAp paste in a steady manner, with approximately 40% being released within 21 days. GaHAp with the highest gallium contents, 5.5 ± 0.1 wt% and 6.9 ± 0.5 wt%, inhibited the growth of all five bacterial species, with the greatest activity being against Pseudomonas aeruginosa. Biocompatibility assays showed maintained cell viability (~80%) after seven days of indirect exposure to GaHAp. However, when GaHAp with Ga content above 3.3 ± 0.4 wt% was directly applied on the cells, a decrease in metabolic activity was observed on the seventh day. Overall, these results show that GaHAp with Ga content below 3.3 ± 0.4 wt% has attractive antimicrobial properties, without affecting the cell metabolic activity, creating a material that could be used for bone regeneration and prevention of infection.

Graphical Abstract

1. Introduction

Calcium phosphates (CaPs) are widely used in bone regeneration due to their unique properties, such as biocompatibility, osteoinductivity, and osteoconductivity [1,2,3]. They are often applied as bone cements [4], scaffolds [5], and coatings [1,2]. The biological activity of any CaP depends on the physicochemical properties, such as Ca/P molar ratio and solubility. Even though there is a great number of CaPs, hydroxyapatite (HAp) is the most extensively used one due to its similarity to the mineral component of bone. HAp is the most thermodynamically stable phase of CaP, with a characteristic Ca/P molar ratio of 1.67 and relatively low solubility. Numerous studies focusing on HAp have been undertaken in the last decades with both in vitro and in vivo assays, and conclusions have underlined its osteoconductive and osteoinductive properties [6,7,8,9,10,11,12,13].
In orthopedics, bacterial infection is a major problem leading to revision surgeries, implant removal, and possibly even amputation. Bacterial contamination of the wound may arise from the patient’s skin or from the surrounding environment [14,15,16,17]. Antibiotics have proven to be the gold standard in preventing and treating infections. However, the systemic administration of antibiotics can have a negative effect on the body (e.g., renal toxicity or microbiome dysbiosis), and it can lead to the potentially low active local concentration of antibiotic at the infection site. Additionally, antibiotic resistance of clinically relevant pathogens is increasing every year, which only emphasizes the need for the development of new biomaterials with improved antibacterial properties [18].
The doping of CaPs, including HAp, with different metal ions has often been performed to enhance the material properties, in terms of bioactivity and/or antibacterial properties [19]. HAp has the ability to incorporate isomorphic substituents, such as magnesium (Mg), sodium (Na), strontium (Sr), silver (Ag), copper (Cu), etc., due to its flexible and stable crystalline structure [20]. The addition of antibacterial ions such as Ag [21,22], Cu [23,24], Zn [25], and Ga [26] provides antibacterial assets to CaPs. Tailoring a biomaterial with the aforementioned capacities could help to prevent bacterial growth at the surgical site after implantation.
Gallium has been known since the 1970s, and next to its antibacterial potential, it has been used to treat bone diseases. Gallium nitrate (Ga(NO3)3) is used as a drug to treat hypercalcemia [27,28,29]. The antibacterial activity of gallium compounds, such as gallium maltolate, nitrate, and citrate has been reported against different bacterial species, such as Mycobacteriaceae (M.) tuberculosis, Mycobacterium (M.) avium, Staphylococcus (S.) aureus, Escherichia (E.) coli [30], and Pseudomonas (P.) aeruginosa [31,32]. To date, the antibacterial activity of gallium-doped hydroxyapatite (GaHAp) has primarily been assessed against P. aeruginosa [29,33]. The antibacterial activity of gallium against both Gram-positive and Gram-negative bacterial species is supported by the similarity between Ga3+ and Fe3+ ions [34]. Namely, Ga3+ replaces Fe3+ in bacteria, resulting in the disruption of protein metabolism and leading to bacterial death [16,32].
In this study the antibacterial activity of GaHAp synthesized using the wet precipitation method was tested for the first time against a wide range of bacterial species: P. aeruginosa, E. coli, S. aureus, S. epidermidis, and S. pyogenes. Additionally, the biocompatibility of the produced GaHAp was assessed on human fibroblasts (hTERT-BJ1).

2. Materials and Methods

2.1. Synthesis of the Gallium-Doped Hydroxyapatite (GaHAp)

Gallium-doped hydroxyapatite (GaHAp) was synthesized via wet chemical precipitation using calcium oxide (CaO; >98%; Jost chemical, St. Louis, MI, USA), orthophosphoric acid (H3PO4; 75%; “Latvijas ķīmija” Ltd., Riga, Latvia), and gallium nitrate hydrate (Ga(NO3)3·xH2O; 99.9% trace metal; Sigma-Aldrich, Burlington, MA, USA). In order to calculate the mass of gallium nitrate hydrate, the amount of water molecules of Ga(NO3)3·4.2H2O was determined with inductively coupled plasma mass spectrometry (ICP-MS; Agilent 7700X; Santa Clara, CA, USA). The gallium concentrations used in the synthesis were 2, 4, 6.3, and 8 wt% with respect to the theoretical HAp yield. The initial (Ca + Ga)/P molar ratio of the reagents was 1.67. The molar ratio was kept constant for all the concentrations. Three replicates of the synthesis were performed for each Ga concentration.
The synthesis processes were performed in the synthesis workstation EasyMax 102 Advanced (Mettler Toledo, Columbus, OH, USA). CaO powder was added to deionized water, under vigorous stirring (420 rpm) at room temperature (22 °C), in order to obtain Ca(OH)2 suspension. Then, Ga(NO3)3·4.2H2O powder was added and stirred for five minutes. The synthesis mixture was heated to 45 °C, and the temperature was maintained constant during synthesis. Then, 2M H3PO4 was added to the starting suspension of Ca(OH)2 and Ga(NO3)3·4.2H2O at an addition rate of 0.6 mL/min. The addition rate was reduced to 0.1 mL/min while approaching the synthesis end pH, 6.90 ± 0.05. The obtained precipitates were aged in the mother liquors at ambient temperature overnight (approximately 20 h). After ageing, the precipitates were vacuum-filtered and washed with 1 L of deionized water. HAp synthesized without Ga(NO3)3·4.2H2O (also known as pure HAp) was used as a reference.
The synthesized products were used in two forms depending on the performed test: as paste (filtered wet precipitates) or as dried powder. GaHAp paste was steam-sterilized in a table-top autoclave at 121 °C for 20 min. To obtain powder, the paste (sterilized or non-sterilized) was dried in an oven at 105 °C for 24 h. Dried agglomerates were crushed with a mortar and pestle to obtain fine powder. GaHAp paste was used in the indirect cytotoxicity tests, while GaHAp powder was used in physicochemical characterization, antibacterial assays, and direct cytotoxicity tests.

2.2. Characterization Methods

2.2.1. X-ray Diffraction

The phase composition of the powders was analyzed using X-ray diffractometry (XRD; PANalytical X’Pert PRO; Westborough, MA, USA). XRD patterns were recorded using Ni filter and Cu Kα radiation at 40 kV and 30 mA, with a 2θ range of 10–70°.
The crystallite size was calculated from the X-ray diffraction profiles, according to the Debye–Scherrer equation (Equation (1)). The strong reflection of [002] was used by measuring the full width at half maximum (FWHM).
D = k λ β c o s θ  
where K is the Scherrer constant with a value of 0.9 [30], λ is the wavelength of light used for diffraction, β is the “full width at half maximum (FWHM)” of the [002] peak, and θ is the measured angle.

2.2.2. Fourier Transform Infrared Spectrometry

The chemical composition of the powders was analyzed using Fourier Transform Infrared Spectroscopy (FTIR; Bruker Tensor 27 spectrometer; Bruker Corporation, Billerica, MA, USA). FTIR spectra were recorded in Attenuated Total Reflectance (ATR) mode. Spectra were obtained at a resolution of 4 cm−1, over a range of wavenumbers from 400 cm−1 to 4000 cm−1, with an average of 50 scans. Before every measurement, a background spectrum was taken and deducted from the sample spectrum.

2.2.3. Specific Surface Area and Particle Size

The specific surface area (SSA) of the powders was determined using the Brunauer–Emmett–Teller (BET) method (ISO 9277:2010; QUADRASORB SI and Quadra Win, Quantachrome Instruments, Boynton Beach, FL, USA). Before BET analysis, samples were degassed for 24 h at 25 °C (Autosorb Degasser Model AD-9; USA) to remove all moisture and vapor. The SSA of the samples was analyzed using a nitrogen adsorption–desorption isotherm.
Particle size dBET was calculated according to Equation (2) as stated in ISO standard No. 13779-3 “Implants for surgery Hydroxyapatite Part 3: Chemical analysis and characterization of crystallinity and phase purity”, assuming particles to be spherical and nonporous.
d B E T = 6 / ( ρ × S S A )
where ρ is the density of HAp and GaHAp, determined with a helium pycnometer (Micro UltraPyc 1200e; Quantachrome Instruments, Boynton Beach, FL, USA) as described in Section 2.2.4.

2.2.4. Helium Pycnometry

The true density of the powders was determined using a helium pycnometer. The instrument (cell volume) was calibrated with stainless-steel calibration spheres of known volume. After calibration, samples with known weight were filled into the sample cell and purged with helium gas in pulse mode (50 pulses). Detailed measurement parameters for helium pycnometry are described elsewhere [35].

2.2.5. Transmission Electron Microscope

The morphology of the powders was observed using a transmission electron microscope (TEM; FEI Tecnai G2 F20; Hillsboro, OR, USA) operated at 200 kV. Detailed sample preparation for TEM analysis is described elsewhere [36].

2.3. In Vitro Release of Gallium Ions

The investigation of Ga3+ ion release from GaHAp paste was performed in Dulbecco’s Modified Eagle Medium (DMEM) with 1 g/L glucose (without NaHCO3; Gibco, Thermo fiscer science, Waltham, MA, USA), with the addition of NaHCO3 (99.7%; Sigma-Aldrich, Burlington, MA, USA) and NaN3 (99.5% (as preservative); Sigma-Aldrich, Burlington, MA, USA). Afterwards, the medium was filter-sterilized through a 0.22 μm filter.
Prior to the ion release tests, GaHAp paste was steam-sterilized at 121 °C for 20 min. The sterile paste samples (50 mg of dry mass) were added to 50 mL of DMEM, vortexed and incubated at 37 °C in a table-top environmental shaker–incubator at 70 rpm (ES-20; Biosan, Riga, Latvia). During the first 72 h, the medium was collected by centrifuging the samples at 1610 g for 3 min and was then replaced with 50 mL of fresh DMEM every 24 h. Thereafter, the medium was refreshed every 72 h. The Ga concentration in the eluate was measured using ICP-MS (Agilent 7700X; Santa Clara, CA, USA). Three parallel measurements were performed for each GaHAp paste composition.

2.4. Antibacterial Tests

The antibacterial properties of GaHAp and Ga(NO3)3·4.2H2O were determined against five bacterial species: Gram-negative P. aeruginosa (strain Paer09) and E. coli (strain American Type Culture Collection (ATCC) 25922); Gram-positive S. aureus (strain JAR 06013), S. epidermidis (strain ATCC 35984), and S. pyogenes (strain ATCC 19615). Different bacterial species were recovered from frozen stocks (−80 °C in 20% (v/v) glycerol) and cultured in tryptic soy broth (TSB; Oxoid, Basel, Switzerland) overnight in ambient air at 37 °C and agitation at 100 rpm. The overnight culture was then diluted with TSB to an optical density (OD) of 0.1 at 600 nm (106–107 colony-forming units (CFU)/mL).
The GaHAp powder used for the antibacterial experiments was prepared from sterilized paste that was dried for 24 h at 105 °C and ground using a pestle. Afterwards, the powder was packed and sterilized with hot air in a drying oven for 2 h at 134 °C.

2.4.1. Minimal Inhibitory Concentration (MIC) of Ga(NO3)3·4.2H2O

Ga(NO3)3·4.2H2O was dissolved in milliQ water and diluted from 75 μg/mL to 450 μg/mL with TSB. A total volume of 150 μL of the solutions was mixed with 150 μL of TSB in a 96-well plate. A volume of 5 μL of bacterial culture with OD600 = 0.1 was added to each well and incubated for 24 h at 37 °C at 100 rpm. Bacterial growth (OD600) was measured for 18 h at 37 °C in a plate reader (MultiskanGo; Thermo Scientific, Waltham, MA, USA) or it was quantified via serial dilution and total viable count on tryptic soy agar (TSA) plates.

2.4.2. Antibacterial Properties of GaHAp

GaHAp powders were suspended in TSB at concentrations of 1, 2, and 4 mg/mL. A total of 300 μL of the suspension was transferred to a 96-well plate, and 5 μL (OD600 = 0.1) of bacteria was added to each well. The absorbance of the plate at 600 nm was measured as described in Section 2.4.1.

2.5. Cytocompatibility Test

2.5.1. Cytotoxicity of Ga(NO3)3·4.2H2O

Cytotoxicity was tested on telomerase-immortalized human foreskin fibroblasts (hTERT-BJ1), which were purchased from Clontech (Clontech Laboratories, Mountain View, CA, USA). hTERT-BJ1 were routinely cultured as previously described [37]. Briefly, hTERT-BJ1 were cultivated in DMEM with 1 g/L glucose (without NaHCO3; Gibco, Thermo fiscer science, Waltham, MA, USA), supplemented with NaHCO3 (99.7%; Sigma-Aldrich, Burlington, MA, USA) and 10 % fetal bovine serum (Biochrome, Sigma-Aldrich, Burlington, MA, USA), with the addition of 100 μg/mL streptomycin (Gibco) and 100 U/mL penicillin (Gibco), at 37 °C in a humidified 5% CO2 atmosphere. In total, 104 cells per well were seeded on a 96-well plate. The following day, Ga(NO3)3·4.2H2O solutions at different concentrations (75–450 μg/mL) were applied to the cells and incubated for one and three days. To determine cell viability, CellTiter-Blue (Promega, Promega Corporation, Madison, WI, USA) was performed following the manufacturer’s instructions. Cell viability (calculated in %) was determined as the fluorescence ratio between cells grown in the presence and absence of Ga(NO3)3·4.2H2O solutions. The average values and standard deviations were calculated from three parallel samples in three independent experiments. Dimethyl sulfoxide (DMSO; Sigma-Aldrich, Burlington, MA, USA) was used as a negative control.

2.5.2. Cytotoxicity of GaHAp

hTERT-BJ1 cells were cultured as described above, and the cytotoxicity of GaHAp was assessed using direct and indirect methods. For the direct test, 104 cells per well were seeded on a 96-well plate, and the following day, GaHAp powder suspensions (prepared as described in Section 2.4.2, at concentrations of 1, 2, and 4 mg/mL in DMEM) were applied to the cells and incubated for one, three, and seven days.
In the indirect test, 1.5 × 104 cells per well were seeded on a six-well plate, and the following day, a cell strainer (Corning®, Amsterdam, The Netherlands), with a pore size of 100 µm containing GaHAp paste (250 ± 50 mg), was placed in each well and incubated for one, three, and seven days. In order to determine cell viability, CellTiter-Blue was performed in both tests following the manufacturer’s instructions. Cell viability (%) was determined as the fluorescence ratio between cells grown in the presence and absence of GaHAp. The average values and standard deviations were calculated from three parallel samples. As a negative control, DMSO was used.

2.6. Statistical Analysis

The results are presented as mean values ± standard deviations (SDs) of three experiments. Statistical analysis was performed on microstructure parameters (specific surface area, density, and particle size) and on cytocompatibility test data using one-way ANOVA with Tukey’s multiple comparison test, and p < 0.05 was used as a limit to indicate statistical significance (ns > 0.05; * p < 0.05; ** p < 0.01; *** p < 0.005; **** p < 0.001).

3. Results

3.1. Physicochemical Characteristics

The main characteristics of the synthesized powders are summarized in Table 1. The GaHAp powders had a higher specific surface area (SSA) than the HAp powders (p < 0.05), revealing that the addition of Ga led to the reduction in the particle size. After steam sterilization, the SSA decreased. Nevertheless, the SSA of the sterilized GaHAp powders was higher than that of the HAp powders (p < 0.05).
The phase composition of the synthesized powders was analyzed using XRD, and the corresponding XRD patterns are shown in Figure 1. Regardless of the chemical composition, all the XRD patterns have characteristic apatite peaks that correspond to the values reported in the literature [38,39]. The XRD patterns did not reveal the presence of additional phases or peak shifts across the different materials. The different amounts of Ga added to the synthesis (2, 4, 6.3, or 8 wt%) did, however, produce a broadening of the XRD peaks (Figure 1A). After steam sterilization, the characteristic peaks become sharper, which indicates an increase in the crystallinity of the samples (Figure 1B).
The crystallite sizes of the diffraction plane [002] for HAp and GaHAp powders were calculated using the Debye–Scherrer equation, and the obtained values are summarized in Table 2. According to these calculations, nano-sized crystallites were obtained, regardless of their chemical composition. With the addition of Ga, the crystallite size of GaHAp decreased compared with the HAp powders. However, before sterilization, differences in crystallite size were not observed among the GaHAp powders.
The FTIR spectra (Figure 2) of HAp and GaHAp show similar appearances. All spectra have HAp characteristic absorbance bands corresponding to ν3 PO43− group vibrations at 1030 and 1097 cm−1. The absorbance band from the vibration of group ν1 PO43− is observed at 960 cm−1. Moreover, the absorbance bands at 604 and 560 cm−1 can be attributed to ν4 PO43− group vibrations. The band at 635 cm−1 corresponds to the vibration of the OH− group. The band assignments are in accordance with literature data [40,41]. The characteristic absorbance bands become broader with the increase in Ga content in the synthesized powders.
TEM micrographs were used to analyze the morphology of HAp and GaHAp particles (Figure 3). The TEM results showed a rod-like shape for GaHAp particles and a size less than 50 nm, which corresponds to the value calculated using BET data. The size of the nanoparticles decreased with the increase in Ga concentration.

3.2. In Vitro Ga3+ Release

The release profiles of Ga3+ from the GaHAp paste samples are shown in Figure 4. For 2 GaHAp and 4 GaHAp, ion release was measured until days 21 and 27, respectively, as the amount of Ga detected at subsequent time points was below the ICP-MS detection limit (<0.2 mg/kg). In the case of samples with higher Ga concentrations, i.e., 6.3 GaHAp and 8 GaHAp, a gradual release was observed up to 30 days. No high initial or burst release of Ga3+ was observed for any GaHAp. The cumulative Ga3+ release rate was higher from samples with lower Ga content, namely, 2 GaHAp (44.3 ± 0.9%) and 4 GaHAp (43.1 ± 3.6%), while 6.3 GaHAp and 8 GaHAp Ga release rates were 48.6 ± 1.1% and 49.8 ± 4.6%, respectively, within 30 days.

3.3. Antibacterial Activity

3.3.1. Minimal Inhibitory Concentration of Ga(NO3)3·4.2H2O

P. aeruginosa and S. aureus growth in the presence of Ga(NO3)3·4.2H2O solution was measured by means of absorbance (OD600), and the results are shown in Figure 5. After 18 h of incubation, a total inhibition of P. aeruginosa growth was observed (Figure 5a). In contrast, S. aureus (Figure 5b) and E. coli, S. epidermidis, and S. pyogenes (Figure S1) showed growth reduction in the presence of Ga(NO3)3·4.2H2O, but not complete inhibition.
The minimal inhibitory concentration (MIC) and CFU/mL of bacterial species are shown in supplementary data Figure S2. The MIC of Ga(NO3)3·4.2H2O against P. aeruginosa was 75 μg/mL; against S. aureus—150 μg/mL; against E. coli—200 μg/mL; against S. epidermidis—250 μg/mL; and against S. pyogenes—75 μg/mL.

3.3.2. Antibacterial Properties of GaHAp

The growth curves of P. aeruginosa and S. aureus in the presence of 1, 2, and 4 mg/mL GaHAp powder suspensions are shown in Figure 6 and Figure 7. The growth curves of the other bacterial species (S. epidermidis, S. pyogenes, and E. coli) are shown in Figure S2.
In the case of 1 mg/mL GaHAp, only the highest Ga-containing powder (8 GaHAp) showed inhibitory effects on P. aeruginosa growth (Figure 6a). With 2 mg/mL (Figure 6b) and 4 mg/mL (Figure 6c) GaHAp, a stronger inhibitory effect was observed, and when using 4 mg/mL (Figure 6c), total inhibition of P. aeruginosa growth with 4 GaHAp, 6.3 GaHAp, and 8 GaHAp was observed. Growth inhibition was detected with the same concentration of 4 GaHAp and 6 GaHAp against S. aureus (Figure 7c), S. epidermidis (Figure S3), S. pyogenes (Figure S4), and E. coli (Figure S5).

3.4. Cytocompatibility Test

3.4.1. Cytotoxicity of Ga(NO3) 3·4.2H2O

The cell viability of hTERT-BJ1 in the presence of Ga(NO3)3·4.2H2O solution is shown in Figure 8. A rapid decrease in cell viability was observed after the first day, starting from 150 μg/mL Ga(NO3)3·4.2H2O (p < 0.001). Concentrations of Ga(NO3)3·4.2H2O above the MIC (75 μg/mL) exhibited an increased toxicity already on the first day. After three days, only the cells exposed to 75 µg/mL Ga(NO3)3·4.2H2O showed maintained metabolic activity, around 80%.

3.4.2. Cytotoxicity of GaHAp

The influence of GaHAp on human fibroblast (hTERT-BJ1) viability was tested by applying GaHAp powder directly on the cells. After three days of exposure to different GaHAp concentrations (1, 2, and 4 mg/mL), cells were still metabolically active (above 80% viability) (Figure 9b). However, on day seven (Figure 9c), a rapid decrease in cell viability was observed with 2 mg/mL 8 GaHAp and with 4 mg/mL 4 GaHAp, 6.3 GaHAp, and 8 GaHAp paste samples (less than 40 %).
Human fibroblast (hTERT-BJ1) viability using the different GaHAp paste samples is shown in Figure 10. The indirect test results indicate that the released Ga3+ from GaHAp paste samples did not have cytotoxic effect at any time point, and even after seven days, cell viability was around 90%. Additionally, the metabolic activity of the cells exposed to 6.3 GaHAp and 8 GaHAp paste samples on day three was significantly increased.

4. Discussion

In the present work, we successfully synthesized Ga-doped-HAp using the wet chemical precipitation method.
The morphological and structural nature of the obtained GaHAp coincides with that in previously described studies [29,33,42,43]. The synthesized products had low crystallinity, as suggested by the low-intensity, broad XRD peaks [38,39]. The adsorption of smaller ions, such as Ga3+ compared with Ca2+, on the HAp crystal surface results in the inhibition of crystallization and crystal growth [29,42,44,45,46]. Additionally, steam sterilization had a significant effect on the morphology of the final product. Re-crystallization of the product was observed in the XRD patterns, due to the fact that a hydrothermal reaction occurs under high-temperature and -pressure conditions. This process leads to the nucleation of the crystals and their growth as described in [44,45]. Due to the low crystallinity of the samples obtained in our study, it is challenging to detect the Ga3+ substitution of Ca2+ in the structure. Possibly, Ga3+ is adsorbed/chemisorbed on the particle surface or taken up in the interstitial positions [47]. However, there is no universal technique to detect ion substitution in the interstitial position.
The potential of HAp materials to act as delivery systems of antibacterial Ga3+ ions was investigated by assessing ion release in the cell culture medium. The release of antibacterial ions from the implant material during the initial periods after surgery is important in preventing the development of infections [48]. As bone-associated infections oftenoccur within four months of surgical interventionsprolonged delivery of antibacterial ions may be necessary [28]. Thus, it is important to evaluate the release of Ga3+ ions over long periods. The Ga3+ release profile depends on the Ga content in products, the degree of Ca deficiency of products, the released media, and the conditions [49]. The increase in Ga content in the HAp samples is at the expense of reducing the Ca/P molar ratio. Thus, non-stoichiometric or Ca-deficient HAp (CDHAp) is obtained, which is more soluble than HAp [50]. If Ga does not enter the Ca site in HAp crystallites, it accumulates in the hydrated layer on the surface of crystallites. Additionally, during the first 72 h, the cumulatively released amount of Ga3+ increases more rapidly, i.e., the frequent refreshing of the medium results in a faster release of the ions. Ideally, the flow of the release medium should be aligned with the flow rate of physiological fluids at the site of implantation. The results of the ion release tests have shown that by increasing the Ga concentration above 3.3 ± 0.4 wt%, it is possible to obtain HAp for long-term delivery of Ga3+. Furthermore, approximately 50% of ions were not released within the timeframe of our study, suggesting further long-term delivery up to four months.
The biological properties of Ga(NO3)3·4.2H2O, used as the gallium source, were compared to GaHAp paste or GaHAp powder. Ga(NO3)3·4.2H2O and GaHAp showed similar antibacterial activity against different Gram-positive and Gram-negative bacterial species. This might be connected to the bacterial cell wall structure (Figure S7) [32,51]. Gram-positive bacteria have a thicker cell wall, which makes the bacterial cell impenetrable for Ga compared with Gram-negative bacteria. On the other hand, Gram-negative bacteria, with their thinner cell wall, have a membrane that can lead to Ga penetration. Additionally, Gram-negative bacteria have Fe-dependent metabolism, and Ga3+ can replace Fe3+ on active enzymatic sites and disrupt protein metabolism, leading to bacterial death [52]. Interestingly, the HAp nanoparticles without Ga also showed delayed bacterial growth. This could be explained by the fact that nanoparticles themselves can have a negative effect on bacterial growth [48,50]. However, GaHAp did not show total inhibition of P. aeruginosa growth, as observed in the case of Ga(NO3)3·4.2H2O. This effect is related to the delayed Ga3+ release from HAp, leading to lower Ga3+ concentration in media during the first 24 h. Ga(NO3)3·4.2H2O completely inhibited P. aeruginosa growth, but this was not observed in the case of E. coli, even though both bacteria are Gram negative. The iron uptake pathway via siderophore enterobactin (ENT) in P. aeruginosa and E. coli is different [53]. In contrast with other studies, in our results, we obtained bacterial growth inhibition at higher concentrations of GaHAp powder. For example, Kurtjak et al. obtained inhibition of P. aeruginosa growth with 0.9 g/mL GaHAp containing 3 wt% of Ga (synthesized using the co-precipitation method) [29]. In addition, Ballardini et al. showed an antibacterial effect of Ga-doped HAp against P. aeruginosa and S. aureus. However, E. coli and C. albicans showed higher resistance to Ga-doped HAp after 24 h [54]. Even though the final product was Ga-doped-HAp, the synthesis methods used differed in the previous examples. These important findings indicate that the synthesis method influences key properties of the final material.
It is also important to test the biocompatibility of the produced material. In this study, we observed different effects of Ga(NO3)3·4.2H2O and GaHAp paste or powder on cell metabolic activity. Ga(NO3)3·4.2H2O has a strong acidic nature, which hydrolyzes in a wide pH range of aqueous media. This process leads to the formation of hydroxylate species, predominantly [Ga(OH)4]− and hydronium ion (H3O+) [55,56,57], leading to the acidification of cell culture media. Indeed, we observed a change in medium color between 75 and 450 μg/mL Ga(NO3)3·4.2H2O, indicating a decrease in pH, which results in cell death. The results from the direct and indirect tests of GaHAp on human fibroblast show the importance of evaluating the interactions between the new developed biomaterial and cells. When the materials (GaHAp paste or powder) were not in direct contact with the cells, we observed a higher metabolic activity in fibroblasts after 7 days. Presumably, the ions released from GaHAp paste (Ga3+ but also Ca2+) can stimulate cell growth. In the case of pure HAp, cell viability was approximately 120%. It has already been reported that Ca2+ ions promote bone formation and maturation [2]. From the literature, Pajor et al. observed the toxic effect of GaHAp prepared with the dry method on the BALB/c 3T3 clone A31 mammalian cell line compared with the same material prepared with the wet method. In the study, this coherence was explained with the solubility of the materials obtained with different synthesis methods [42]. That was another confirmation that the material form and the method used can have an influence on material–cell interactions.

5. Conclusions

Gallium-doped hydroxyapatite (GaHAp) was successfully obtained, and it showed promising biological properties. The optimal Ga3+ doping rate of HAp ranges from 2 to 5.5 ± 0.1 wt%, as it was shown from the analyses of the morphological properties and biological activity. The addition of Ga to the synthesis media promoted the formation of HAp with smaller particle sizes. GaHAp provided long-term gallium ion release with Ga concentrations above 3.3 ± 0.4 wt%. Additionally, GaHAp had a bacteriostatic effect on multiple bacterial species, both Gram positive and Gram negative, without substantial toxicity towards human fibroblasts. The GaHAp samples showed superior inhibition of P. aeruginosa compared with the other bacterial species, representing a material advantage for the early-stage treatment of bone defect, as it prevents further bacterial growth and could prevent the development of chronic and acute infection.

Supplementary Materials

The following supporting information can be downloaded at: https://www.mdpi.com/article/10.3390/jfb14020051/s1, Figure S1: Growth curves in the presence of Ga(NO3)3·4.2H2O at different concentrations of (A) E. coli, (B) S. epidermidis, and (C) S. pyogenes, Figure S2: S. epidermidis growth curves in the presence of GaHAp paste at different concentrations, Figure S3: S. pyogenes growth curves in the presence of GaHAp paste at different concentrations, Figure S4: E. coli growth curves in the presence of GaHAp paste at different concentrations, Figure S5: The minimal inhibitory concentration of Ga(NO3)3·4.2H2O against 5 bacterial species, Figure S6: Human fibroblasts (hTERT-BJ1) were exposed to GaHAp for the indirect test on day 3. PC—positive control; scale bar—200 μm, Figure S7: The structural difference between Gram-negative and Gram-positive bacteria (created using Biorender.com. accessed on 7 December 2022).

Author Contributions

Conceptualization, M.M., L.S. and J.L.; methodology, M.M., C.S., R.V. and A.S.; validation, J.L., T.F.M., L.S. and C.S.; formal analysis, M.M., R.V. and A.S.; investigation, M.M., L.S., R.V., C.S. and A.S.; resources, J.L. and T.F.M.; data curation, L.S., C.S., A.S., J.L. and T.F.M.; writing—original draft preparation, M.M. and L.S.; writing—reviewing and editing, M.M., L.S., C.S., A.S., J.L. and T.F.M.; visualization, M.M.; supervision, L.S, J.L, C.S. and T.F.M.; project administration, J.L; funding acquisition, J.L. All authors have read and agreed to the published version of the manuscript.

Funding

This work was funded by the EuroNanoMedIII project “NANO delivery system for one-shot regenerative therapy of peri-implantis” (ImplantNano, GA.ES RTD/2020/19) and the European Union’s Horizon 2020 research and innovation program under grant agreement No. 857287.

Institutional Review Board Statement

Not applicable.

Informed Consent Statement

Not applicable.

Data Availability Statement

The data presented in this study are available upon request from the corresponding author. The data are not publicly available due to project agreement.

Acknowledgments

The authors would like to thank Jana Vecstaudza and Kristaps Rubenis for their scientific discussion sessions.

Conflicts of Interest

The authors declare no conflict of interest.

References

  1. Ben-Nissan, B. Advances in Calcium Phosphate Biomaterials; Springer: Berlin/Heidelberg, Germany, 2014. [Google Scholar] [CrossRef] [Green Version]
  2. Jeong, J.; Kim, J.H.; Shim, J.H.; Hwang, N.S.; Heo, C.Y. Bioactive Calcium Phosphate Materials and Applications in Bone Regeneration. Biomater. Res. 2019, 23, 4. [Google Scholar] [CrossRef] [Green Version]
  3. Samavedi, S.; Poindexter, L.K.; Van Dyke, M.; Goldstein, A.S. Synthetic Biomaterials for Regenerative Medicine Applications; Elsevier Inc.: Amsterdam, The Netherlands, 2014; pp. 81–99. [Google Scholar] [CrossRef]
  4. Ambard, A.J.; Mueninghoff, L. Calcium Phosphate Cement: Review of Mechanical and Biological Properties. J. Prosthodont. 2006, 15, 321–328. [Google Scholar] [CrossRef] [PubMed]
  5. Sun, H.; Yang, H.L. Calcium Phosphate Scaffolds Combined with Bone Morphogenetic Proteins or Mesenchymal Stem Cells in Bone Tissue Engineering. Chin. Med. J. 2015, 128, 1121–1127. [Google Scholar] [CrossRef]
  6. Driskell, T.D.; Hassler, C.R.; Tennery, V.J.; McCoy, L. Calcium Phosphate Resorbable Ceramics: A Potential Alternative to Bone Grafting. J. Dent. Res. 1973, 52, 123–131. [Google Scholar]
  7. Denissen, H.W.; de Groot, K. Immediate Dental Root Implants from Synthetic Dense Calcium Hydroxylapatite. J. Prosthet. Dent. 1979, 42, 551–556. [Google Scholar] [CrossRef] [PubMed]
  8. Zaner, D.J.; Yukna, R.A. Particle Size of Periodontal Bone Grafting Materials. J. Periodontol. 1984, 55, 406–409. [Google Scholar] [CrossRef]
  9. Klein, C.P.A.T.; de Groot, K.; Drissen, A.A.; van der Lubbe, H.B.M. Interaction of Biodegradable β-Whitlockite Ceramics with Bone Tissue: An in Vivo Study. Biomaterials 1985, 6, 189–192. [Google Scholar] [CrossRef]
  10. Brown, W.E.; Chow, L.C.C. A New Calcium Phosphate, Water–Setting Cement. Acc. Chem. Res. 1986, 351–379. [Google Scholar]
  11. Yuan, H.; Barbieri, D.; Luo, X.; Van Blitterswijk, C.A.; De Bruijn, J.D. Calcium Phosphates and Bone Induction. Compr. Biomater. II 2017, 1, 333–349. [Google Scholar] [CrossRef]
  12. Lin, L.; Chow, K.L.; Leng, Y. Study of Hydroxyapatite Osteoinductivity with an Osteogenic Differentiation of Mesenchymal Stem Cells. J. Biomed. Mater. Res.-Part A 2009, 89, 326–335. [Google Scholar] [CrossRef]
  13. Wang, Z.; Han, T.; Zhu, H.; Tang, J.; Guo, Y.; Jin, Y.; Wang, Y.; Chen, G.; Gu, N.; Wang, C. Potential Osteoinductive Effects of Hydroxyapatite Nanoparticles on Mesenchymal Stem Cells by Endothelial Cell Interaction. Nanoscale Res. Lett. 2021, 16, 67. [Google Scholar] [CrossRef] [PubMed]
  14. Ribeiro, M.; Monteiro, F.J.; Ferraz, M.P. Infection of Orthopedic Implants with Emphasis on Bacterial Adhesion Process and Techniques Used in Studying Bacterial-Material Interactions. Biomatter 2012, 2, 176–194. [Google Scholar] [CrossRef] [PubMed] [Green Version]
  15. Campoccia, D.; Montanaro, L.; Arciola, C.R. The Significance of Infection Related to Orthopedic Devices and Issues of Antibiotic Resistance. Biomaterials 2006, 27, 2331–2339. [Google Scholar] [CrossRef]
  16. Mosina, M.; Kovrlija, I.; Stipniece, L.; Locs, J. Gallium Containing Calcium Phosphates: Potential Antibacterial Agents or Fictitious Truth. Acta Biomater. 2022, 150, 48–57. [Google Scholar] [CrossRef]
  17. Coppey, E.; Mommaerts, M.Y. Early Complications from the Use of Calcium Phosphate Paste in Mandibular Lengthening Surgery. A Retrospective Study. J. Oral Maxillofac. Surg. 2017, 75, 1274.e1–1274.e10. [Google Scholar] [CrossRef]
  18. Mokabber, T. Electrochemically Deposited Antimicrobial Hydroxyapatite Coatings; University of Groningen: Groningen, The Netherlands, 2020. [Google Scholar] [CrossRef]
  19. Jiang, Y.; Yuan, Z.; Huang, J. Substituted Hydroxyapatite: A Recent Development. Mater. Technol. 2020, 35, 785–796. [Google Scholar] [CrossRef]
  20. Stötzel, C.; Müller, F.A.; Reinert, F.; Niederdraenk, F.; Barralet, J.E.; Gbureck, U. Ion Adsorption Behaviour of Hydroxyapatite with Different Crystallinities. Colloids Surf. B Biointerfaces 2009, 74, 91–95. [Google Scholar] [CrossRef] [PubMed]
  21. Wang, L.; Hu, C.; Shao, L. The Antimicrobial Activity of Nanoparticles: Present Situation and Prospects for the Future. Int. J. Nanomed. 2017, 12, 1227–1249. [Google Scholar] [CrossRef] [Green Version]
  22. Chernousova, S.; Epple, M. Silver as Antibacterial Agent: Ion, Nanoparticle, and Metal. Angew. Chem.-Int. Ed. 2013, 52, 1636–1653. [Google Scholar] [CrossRef]
  23. Shanmugam, S.; Gopal, B. Copper Substituted Hydroxyapatite and Fluorapatite: Synthesis, Characterization and Antimicrobial Properties. Ceram. Int. 2014, 40, 15655–15662. [Google Scholar] [CrossRef]
  24. Jacobs, A.; Renaudin, G.; Forestier, C.; Nedelec, J.M.; Descamps, S. Biological Properties of Copper-Doped Biomaterials for Orthopedic Applications: A Review of Antibacterial, Angiogenic and Osteogenic Aspects. Acta Biomater. 2020, 117, 21–39. [Google Scholar] [CrossRef]
  25. Mouriño, V.; Cattalini, J.P.; Boccaccini, A.R. Metallic Ions as Therapeutic Agents in Tissue Engineering Scaffolds: An Overview of Their Biological Applications and Strategies for New Developments. J. R. Soc. Interface 2012, 9, 401–419. [Google Scholar] [CrossRef] [Green Version]
  26. Kircheva, N.; Dudev, T. Gallium as an Antibacterial Agent: A DFT/SMD Study of the Ga3+/Fe3+ Competition for Binding Bacterial Siderophores. Inorg. Chem. 2020, 59, 6242–6254. [Google Scholar] [CrossRef] [PubMed]
  27. Kelson, A.B.; Carnevali, M.; Truong-Le, V. Gallium-Based Anti-Infectives: Targeting Microbial Iron-Uptake Mechanisms. Curr. Opin. Pharmacol. 2013, 13, 707–716. [Google Scholar] [CrossRef] [PubMed]
  28. Qiu, C.; Lu, T.; He, F.; Feng, S.; Fang, X.; Zuo, F.; Jiang, Q.; Deng, X.; Ye, J. Influences of Gallium Substitution on the Phase Stability, Mechanical Strength and Cellular Response of β-Tricalcium Phosphate Bioceramics. Ceram. Int. 2020, 46, 16364–16371. [Google Scholar] [CrossRef]
  29. Kurtjak, M.; Vukomanović, M.; Krajnc, A.; Kramer, L.; Turk, B.; Suvorov, D. Designing Ga(III)-Containing Hydroxyapatite with Antibacterial Activity. RSC Adv. 2016, 6, 112839–112852. [Google Scholar] [CrossRef]
  30. Wren, A.W.; Jones, M.C.; Misture, S.T.; Coughlan, A.; Keenan, N.L.; Towler, M.R.; Hall, M.M. A Preliminary Investigation into the Structure, Solubility and Biocompatibility of Solgel SiO2-CaO-Ga2O3 Glass-Ceramics. Mater. Chem. Phys. 2014, 148, 416–425. [Google Scholar] [CrossRef]
  31. Lemire, J.A.; Harrison, J.J.; Turner, R.J. Antimicrobial Activity of Metals: Mechanisms, Molecular Targets and Applications. Nat. Rev. Microbiol. 2013, 11, 371–384. [Google Scholar] [CrossRef]
  32. Kaneko, Y.; Thoendel, M.; Olakanmi, O.; Britigan, B.E.; Singh, P.K. The Transition Metal Gallium Disrupts Pseudomonas Aeruginosa Iron Metabolism and Has Antimicrobial and Antibiofilm Activity. J. Clin. Investig. 2007, 117, 877–888. [Google Scholar] [CrossRef]
  33. Kurtjak, M.; Vukomanović, M.; Suvorov, D. Antibacterial Nanocomposite of Functionalized Nanogold and Gallium-Doped Hydroxyapatite. Mater. Lett. 2017, 193, 126–129. [Google Scholar] [CrossRef]
  34. Rzhepishevska, O.; Ekstrand-Hammarström, B.; Popp, M.; Björn, E.; Bucht, A.; Sjöstedt, A.; Antti, H.; Ramstedt, M. The Antibacterial Activity of Ga3+ Is Influenced by Ligand Complexation as Well as the Bacterial Carbon Source. Antimicrob. Agents Chemother. 2011, 55, 5568–5580. [Google Scholar] [CrossRef] [PubMed] [Green Version]
  35. Rubenis, K.; Zemjane, S.; Vecstaudza, J.; Bitenieks, J.; Locs, J. Densification of Amorphous Calcium Phosphate Using Principles of the Cold Sintering Process. J. Eur. Ceram. Soc. 2021, 41, 912–919. [Google Scholar] [CrossRef]
  36. Smits, K.; Grigorjeva, L.; Millers, D.; Kundzins, K.; Ignatans, R.; Grabis, J.; Monty, C. Luminescence Properties of Zirconia Nanocrystals Prepared by Solar Physical Vapor Deposition. Opt. Mater. 2014, 37, 251–256. [Google Scholar] [CrossRef]
  37. Meredith, D.O.; Eschbach, L.; Wood, M.A.; Riehle, M.O.; Curtis, A.S.G.; Richards, R.G. Human Fibroblast Reactions to Standard and Electropolished Titanium and Ti-6Al-7Nb, and Electropolished Stainless Steel. J. Biomed. Mater. Res.-Part A 2005, 75, 541–555. [Google Scholar] [CrossRef]
  38. Indrani, D.J.; Soegijono, B.; Adi, W.A.; Trout, N. Phase Composition and Crystallinity of Hydroxyapatite with Various Heat Treatment Temperatures. Int. J. Appl. Pharm. 2017, 9, 87–91. [Google Scholar] [CrossRef] [Green Version]
  39. Matsumoto, T.; Tamine, K.I.; Kagawa, R.; Hamada, Y.; Okazaki, M.; Takahashi, J. Different Behavior of Implanted Hydroxyapatite Depending on Morphology, Size and Crystallinity. J. Ceram. Soc. Jpn. 2006, 114, 760–762. [Google Scholar] [CrossRef] [Green Version]
  40. Ślósarczyk, A.; Paszkiewicz, Z.; Paluszkiewicz, C. FTIR and XRD Evaluation of Carbonated Hydroxyapatite Powders Synthesized by Wet Methods. J. Mol. Struct. 2005, 744–747, 657–661. [Google Scholar] [CrossRef]
  41. Michelot, A.; Sarda, S.; Audin, C.; Deydier, E.; Manoury, E.; Poli, R.; Rey, C. Spectroscopic Characterisation of Hydroxyapatite and Nanocrystalline Apatite with Grafted Aminopropyltriethoxysilane: Nature of Silane–Surface Interaction. J. Mater. Sci. Vol. 2015, 50, 5746–5757. [Google Scholar] [CrossRef] [Green Version]
  42. Pajor, K.; Pajchel, Ł.; Zgadzaj, A.; Piotrowska, U.; Kolmas, J. Modifications of Hydroxyapatite by Gallium and Silver Ions—Physicochemical Characterization, Cytotoxicity and Antibacterial Evaluation. Int. J. Mol. Sci. 2020, 21, 5006. [Google Scholar] [CrossRef]
  43. Melnikov, P.; de Fatima Cepa Matos, M.; Malzac, A.; Rainho Teixeira, A.; de Albuquerque, D.M. Evaluation of In Vitro Toxicity of Hydroxyapatite Doped with Gallium. Mater. Lett. 2019, 253, 343–345. [Google Scholar] [CrossRef]
  44. Zhang, T.; Xiao, X. Hydrothermal Synthesis of Hydroxyapatite Assisted by Gemini Cationic Surfactant. J. Nanomater. 2020, 2020, 5006. [Google Scholar] [CrossRef]
  45. In, Y.; Amornkitbamrung, U.; Hong, M.H.; Shin, H. On the Crystallization of Hydroxyapatite under Hydrothermal Conditions: Role of Sebacic Acid as an Additive. ACS Omega 2020, 5, 27204–27210. [Google Scholar] [CrossRef] [PubMed]
  46. Blumenthal, N.C.; Cosma, V.; Levine, S. Effect of Gallium on the in Vitro Formation, Growth, and Solubility of Hydroxyapatite. Calcif. Tissue Int. 1989, 45, 81–87. [Google Scholar] [CrossRef] [PubMed]
  47. Tite, T.; Popa, A.C.; Balescu, L.M.; Bogdan, I.M.; Pasuk, I.; Ferreira, J.M.F.; Stan, G.E. Cationic Substitutions in Hydroxyapatite: Current Status of the Derived Biofunctional Effects and Their in Vitro Interrogation Methods. Materials 2018, 11, 2081. [Google Scholar] [CrossRef] [PubMed] [Green Version]
  48. Vrchovecká, K.; Pávková-Goldbergová, M.; Engqvist, H.; Pujari-Palmer, M. Cytocompatibility and Bioactive Ion Release Profiles of Phosphoserine Bone Adhesive: Bridge from In Vitro to In Vivo. Biomedicines 2022, 10, 736. [Google Scholar] [CrossRef]
  49. Mocanu, A.; Cadar, O.; Frangopol, P.T.; Petean, I.; Tomoaia, G.; Paltinean, G.-A.; Racz, C.P.; Horovitz, O.; Tomoaia-Cotisel, M. Ion Release from Hydroxyapatite and Substituted Hydroxyapatites in Different Immersion Liquids: In Vitro Experiments and Theoretical Modelling Study. R. Soc. Open Sci. 2021, 8, 201785. [Google Scholar] [CrossRef]
  50. Koppala, S.; Swamiappan, S.; Gangarajula, Y.; Xu, L.; Sadasivuni, K.K.; Ponnamma, D.; Rajagopalan, V. Calcium Deficiency in Hydroxyapatite and Its Drug Delivery Applications. Micro Nano Lett. 2018, 13, 562–564. [Google Scholar] [CrossRef]
  51. Minandri, F.; Bonchi, C.; Frangipani, E.; Imperi, F.; Visca, P. Promises and Failures of Gallium as an Antibacterial Agent. Future Microbiol. 2014, 9, 379–397. [Google Scholar] [CrossRef]
  52. Silhavy, T.J.; Kahne, D.; Walker, S. The Bacterial Cell Envelope. Cold Spring Harb. Perspect. Biol. 2010, 2, a000182. [Google Scholar] [CrossRef]
  53. Gasser, V.; Kuhn, L.; Hubert, T.; Aussel, L.; Hammann, P.; Schalk, I.J. The Esterase PfeE, the Achilles’ Heel in the Battle for Iron between Pseudomonas Aeruginosa and Escherichia Coli. Int. J. Mol. Sci. 2021, 22, 2814. [Google Scholar] [CrossRef]
  54. Ballardini, A.; Montesi, M.; Panseri, S.; Vandini, A.; Balboni, P.G.; Tampieri, A.; Sprio, S. New Hydroxyapatite Nanophases with Enhanced Osteogenic and Anti-Bacterial Activity. J. Biomed. Mater. Res. Part A 2018, 106, 521–530. [Google Scholar] [CrossRef] [PubMed]
  55. Kircheva, N.; Dudev, T. Competition between Abiogenic and Biogenic Metal Cations in Biological Systems: Mechanisms of Gallium‘s Anticancer and Antibacterial Effect. J. Inorg. Biochem. 2021, 214, 111309. [Google Scholar] [CrossRef] [PubMed]
  56. Lessa, J.A.; Parrilha, G.L.; Beraldo, H. Gallium Complexes as New Promising Metallodrug Candidates. Inorg. Chim. Acta 2012, 393, 53–63. [Google Scholar] [CrossRef]
  57. Gómez-Cerezo, N.; Verron, E.; Montouillout, V.; Fayon, F.; Lagadec, P.; Bouler, J.M.; Bujoli, B.; Arcos, D.; Vallet-Regí, M. The Response of Pre-Osteoblasts and Osteoclasts to Gallium Containing Mesoporous Bioactive Glasses. Acta Biomater. 2018, 76, 333–343. [Google Scholar] [CrossRef] [PubMed]
Jfb 14 00051 g001 550
Figure 1. X-ray diffraction patterns of the synthesized powders with different amounts of gallium (A) before and (B) after steam sterilization at 121 °C for 20 min.
Figure 1. X-ray diffraction patterns of the synthesized powders with different amounts of gallium (A) before and (B) after steam sterilization at 121 °C for 20 min.
Jfb 14 00051 g001
Jfb 14 00051 g002 550
Figure 2. FTIR spectra of the synthesized powders with different amounts of gallium (a) before and (b) after steam sterilization at 121 °C for 20 min.
Figure 2. FTIR spectra of the synthesized powders with different amounts of gallium (a) before and (b) after steam sterilization at 121 °C for 20 min.
Jfb 14 00051 g002
Jfb 14 00051 g003 550
Figure 3. TEM images of synthesized GaHAp powders with different amounts of gallium: (a) HAp (b) 2 GaHAp; (c) 4 GaHAp; (d) 6.3 GaHAp; (e) 8 GaHAp.
Figure 3. TEM images of synthesized GaHAp powders with different amounts of gallium: (a) HAp (b) 2 GaHAp; (c) 4 GaHAp; (d) 6.3 GaHAp; (e) 8 GaHAp.
Jfb 14 00051 g003
Jfb 14 00051 g004 550
Figure 4. Ga3+ ion release from GaHAp paste with different amounts of gallium as a function of a time. Release overtime was performed in DMEM media at 37 °C (n = 3 ± SD).
Figure 4. Ga3+ ion release from GaHAp paste with different amounts of gallium as a function of a time. Release overtime was performed in DMEM media at 37 °C (n = 3 ± SD).
Jfb 14 00051 g004
Jfb 14 00051 g005 550
Figure 5. Bacterial growth of P. aeruginosa and S. aureus in the presence of Ga(NO3)3·4.2H2O. (a) P. aeruginosa and (b) S. aureus were grown in TSB with different concentrations of Ga(NO3)3·4.2H2O (from 0 µg/mL to 450 µg/mL Ga(NO3)3·4.2H2O ). The optical density (OD) at 600 nm was measured over 18 h using a plate reader.
Figure 5. Bacterial growth of P. aeruginosa and S. aureus in the presence of Ga(NO3)3·4.2H2O. (a) P. aeruginosa and (b) S. aureus were grown in TSB with different concentrations of Ga(NO3)3·4.2H2O (from 0 µg/mL to 450 µg/mL Ga(NO3)3·4.2H2O ). The optical density (OD) at 600 nm was measured over 18 h using a plate reader.
Jfb 14 00051 g005
Jfb 14 00051 g006 550
Figure 6. P. aeruginosa growth in the presence of GaHAp powder suspensions in TSB at (a) 1 mg/mL (b) 2 mg/mL, and (c) 4 mg/mL. The represented OD600 was obtained by subtracting the initial OD600_oh (starting time = 0 h) from the measured OD600_x h at specific time points.
Figure 6. P. aeruginosa growth in the presence of GaHAp powder suspensions in TSB at (a) 1 mg/mL (b) 2 mg/mL, and (c) 4 mg/mL. The represented OD600 was obtained by subtracting the initial OD600_oh (starting time = 0 h) from the measured OD600_x h at specific time points.
Jfb 14 00051 g006
Jfb 14 00051 g007 550
Figure 7. S. aureus growth inhibition induced by GaHAp powder suspensions in TSB at (a) 1 mg/mL (b) 2 mg/mL, and (c) 4 mg/mL concentrations. The represented OD600 was obtained by subtracting the initial OD600_oh (starting time = 0 h) from the measured OD600_x h at specific time points.
Figure 7. S. aureus growth inhibition induced by GaHAp powder suspensions in TSB at (a) 1 mg/mL (b) 2 mg/mL, and (c) 4 mg/mL concentrations. The represented OD600 was obtained by subtracting the initial OD600_oh (starting time = 0 h) from the measured OD600_x h at specific time points.
Jfb 14 00051 g007
Jfb 14 00051 g008 550
Figure 8. Metabolic activity of human fibroblasts (hTERT-BJ1) exposed to different concentrations of Ga(NO3)3·4.2H2O solutions, where PC—positive control. Negative control results were omitted from the graphs as the values were approximately 0%. (One-way ANOVA single factor with Tukey’s multiple comparison test, n = 3; ns > 0.05; **** p < 0.001).
Figure 8. Metabolic activity of human fibroblasts (hTERT-BJ1) exposed to different concentrations of Ga(NO3)3·4.2H2O solutions, where PC—positive control. Negative control results were omitted from the graphs as the values were approximately 0%. (One-way ANOVA single factor with Tukey’s multiple comparison test, n = 3; ns > 0.05; **** p < 0.001).
Jfb 14 00051 g008
Jfb 14 00051 g009 550
Figure 9. Metabolic activity of human fibroblasts (hTERT-BJ1) exposed to GaHAp powder suspensions at different concentrations (1, 2, and 4 mg/mL) obtained using the direct test: (a) day 1; (b) day 3, and (c) day 7. PC—positive control (ANOVA test, n = 3).
Figure 9. Metabolic activity of human fibroblasts (hTERT-BJ1) exposed to GaHAp powder suspensions at different concentrations (1, 2, and 4 mg/mL) obtained using the direct test: (a) day 1; (b) day 3, and (c) day 7. PC—positive control (ANOVA test, n = 3).
Jfb 14 00051 g009
Jfb 14 00051 g010 550
Figure 10. Metabolic activity of human fibroblasts (hTERT-BJ1) exposed to Ga3+ released from GaHAp paste obtained using the indirect test. (One-way ANOVA single factor with Tukey’s multiple comparison test, n = 3; ns > 0.05; * p < 0.005; **** p < 0.001).
Figure 10. Metabolic activity of human fibroblasts (hTERT-BJ1) exposed to Ga3+ released from GaHAp paste obtained using the indirect test. (One-way ANOVA single factor with Tukey’s multiple comparison test, n = 3; ns > 0.05; * p < 0.005; **** p < 0.001).
Jfb 14 00051 g010
Table
Table 1. Ga contents, particle sizes (dBET), densities, and SSAs of the synthesized products before and after sterilization.
Table 1. Ga contents, particle sizes (dBET), densities, and SSAs of the synthesized products before and after sterilization.
SampleTheoretical Ga Content (wt%)Gallium Content (wt%)Before SterilizationAfter Sterilization
SSA (m2/g)ρ (g/cm3)dBET (nm)SSA (m2/g)ρ (g/cm3)dBET (nm)
HAp--71 ± 72.77 ± 0.0431 ± 350 ± 22.94 ± 0.0141 ± 2
2 GaHAp21.6 ± 0.195 ± 52.85 ± 0.0622 ± 178 ± 32.86 ± 0.0827 ± 1
4 GaHAp43.3 ± 0.4117 ± 42.80 ± 0.0618 ± 188 ± 52.92 ± 0.0923 ± 1
6.3 GaHAp6.35.5 ± 0.1109 ± 22.83 ± 0.0120 ± 189 ± 42.92 ± 0.0523 ± 1
8 GaHAp86.9 ± 0.5102 ± 52.79 ± 0.0321 ± 1104 ± 32.84 ± 0.0420 ± 1
Table
Table 2. Crystallite sizes of the synthesized products calculated using the Debye–Scherrer equation.
Table 2. Crystallite sizes of the synthesized products calculated using the Debye–Scherrer equation.
SamplePlane (hkl)Before SterilizationAfter Sterilization
FWHMCrystallite Size (nm)FWHMCrystallite Size (nm)
HAp[002]0.27431.10.21938.9
2 GaHAp[002]0.34724.50.28430.0
4 GaHAp[002]0.38422.20.27930.5
6.3 GaHAp[002]0.38322.20.30927.6
8 GaHAp[002]0.37222.90.31627.0
Disclaimer/Publisher’s Note: The statements, opinions and data contained in all publications are solely those of the individual author(s) and contributor(s) and not of MDPI and/or the editor(s). MDPI and/or the editor(s) disclaim responsibility for any injury to people or property resulting from any ideas, methods, instructions or products referred to in the content.

Share and Cite

MDPI and ACS Style

Mosina, M.; Siverino, C.; Stipniece, L.; Sceglovs, A.; Vasiljevs, R.; Moriarty, T.F.; Locs, J. Gallium-Doped Hydroxyapatite Shows Antibacterial Activity against Pseudomonas aeruginosa without Affecting Cell Metabolic Activity. J. Funct. Biomater. 2023, 14, 51. https://doi.org/10.3390/jfb14020051

AMA Style

Mosina M, Siverino C, Stipniece L, Sceglovs A, Vasiljevs R, Moriarty TF, Locs J. Gallium-Doped Hydroxyapatite Shows Antibacterial Activity against Pseudomonas aeruginosa without Affecting Cell Metabolic Activity. Journal of Functional Biomaterials. 2023; 14(2):51. https://doi.org/10.3390/jfb14020051

Chicago/Turabian Style

Mosina, Marika, Claudia Siverino, Liga Stipniece, Artemijs Sceglovs, Renats Vasiljevs, T. Fintan Moriarty, and Janis Locs. 2023. "Gallium-Doped Hydroxyapatite Shows Antibacterial Activity against Pseudomonas aeruginosa without Affecting Cell Metabolic Activity" Journal of Functional Biomaterials 14, no. 2: 51. https://doi.org/10.3390/jfb14020051

APA Style

Mosina, M., Siverino, C., Stipniece, L., Sceglovs, A., Vasiljevs, R., Moriarty, T. F., & Locs, J. (2023). Gallium-Doped Hydroxyapatite Shows Antibacterial Activity against Pseudomonas aeruginosa without Affecting Cell Metabolic Activity. Journal of Functional Biomaterials, 14(2), 51. https://doi.org/10.3390/jfb14020051

Note that from the first issue of 2016, this journal uses article numbers instead of page numbers. See further details here.

Article Metrics

Back to TopTop