Iodoform-Blended Portland Cement for Dentistry

Abstract

Portland cement-based formulations blended with radiopacifying agents are popular endodontic materials for various root filling and pulp capping applications. Iodoform (CHI₃) is an alternative candidate radiopacifier whose impact on the setting, bioactivity, antimicrobial properties and cytotoxicity of white Portland cement were evaluated in this study. Isothermal conduction calorimetry and ²⁹Si magic angle spinning nuclear magnetic resonance spectroscopy (MAS NMR) showed that 20 wt% iodoform had no significant impact on the kinetics of cement hydration with respect to the formation of the major calcium silicate hydrate (C-S-H) gel product (throughout the 28-day observation). Conversely, transmission electron microscopy demonstrated that iodine was incorporated into the ettringite (Ca₆Al₂(SO₄)₃(OH)₁₂·26H₂O) product phase. Both iodoform-blended and pure Portland cements exhibited comparable biocompatibility with MG63 human osteosarcoma cells and similar bioactivity with respect to the formation of a hydroxyapatite layer upon immersion in simulated body fluid. By virtue of their high alkalinity, both cements inhibited the growth of Staphylococcus aureus, Pseudomonas aeruginosa and Escherichia coli. However, in all cases, iodoform enhanced the antimicrobial effect and significantly reduced the minimum bactericidal concentration of the cement. In conclusion, iodoform offers antimicrobial advantages in Portland cement-based formulations where oral biofilm formation threatens the success of root filling materials and dentine substitutes. The reactivity with the calcium aluminosulfate components of the hydrating cement matrix warrants further research to understand the long-term stability of the cement matrix in the presence of iodoform.

1. Introduction

Commercial calcium silicate dental materials based upon Portland cement and its constituents are popular options for a variety of dentine substitution, root-end filling and pulp capping indications [1,2,3,4,5]. These cements are ‘bioactive’ in that they are capable of forming hydroxyapatite on their surfaces in vivo to support bone, dentine, cementum, periapical tissue and pulp healing [1,2,3,4,5].

The composition and properties of Portland cement-based endodontic materials are widely reported in the current literature [1,2,3,4,5]. Briefly, Portland cement comprises five phases; alite (tricalcium silicate, Ca₃SiO₅), belite (β-dicalcium silicate, Ca₂SiO₄), aluminate (tricalcium aluminate, Ca₃Al₂O₆), ferrite (tetracalcium aluminoferrite, Ca₂(Al/Fe)₂O₅), and gypsum (calcium sulfate dihydrate, CaSO₄·2H₂O) that react with water to form an adhesive paste that sets into a hardened mass within a few hours and continues to gain compressive strength over a period of weeks [1,2,3,4,5]. Alite and belite hydrate to form a nonstoichiometric nanoporous calcium silicate hydrate (C-S-H) gel matrix and hexagonal crystals of calcium hydroxide (aka portlandite). Aluminate and gypsum react with water to form ettringite (AFt, 6CaO·Al₂O₃·3SO₃·32H₂O) which subsequently decomposes to the thermodynamically more stable monosulfate (AFm, 4CaO·Al₂O₃·SO₃·13H₂O) phase [5]. Ferrite reacts similarly to produce Fe-substituted AFt and AFm phases [5]. It should be noted that hydraulic calcium silicate dental cements differ from industrial ordinary Portland cements in that their heavy metal content is lower and the particle sizes are smaller [1,2,3,4,5]. Also, some calcium silicate dental cements, such as Biodentine^® and Bioaggregate™, are exclusively formulated from alite and belite and do not contain aluminate, ferrite, and gypsum [1,2,3,4,5].

Endodontic materials are required to possess a minimum radiopacity equivalent to 3 mm Al [6], which is achieved by dry-blending the cement with radiopaque barium sulfate or metal oxide compounds of bismuth, zirconium, tantalum, or niobium [1,2,3,4,5]. A range of alternative candidate radiopacifying agents, including TiF₄, CaWO₄, Yb₂O₃, YbF₃ and CHI₃, has also been proposed [7,8,9,10,11,12]. Of these, CHI₃ (iodoform) is a common constituent of commercial calcium hydroxide-based pulp capping formulations (e.g., Vitapex^® (Neo Dental International Inc., Federal Way, WA, USA) and Metapex (Meta Biomed, Colmar, PA, USA)). Iodoform is also added to epoxy resin endodontic sealers to confer radiopacity and antimicrobial properties [13,14,15].

In vitro, animal and human studies indicate that iodoform is adequately biocompatible and sufficiently radiopaque at 20 wt% addition to Portland cement to comply with the current regulatory standards for root filling materials (i.e., ISO 6876:2012 [6] and ANSI/ADA specification #57 [16]) [7,17,18,19,20,21,22,23]. At present, very little is known of the impact of iodoform on the complex hydration and setting reactions of Portland cement. Accordingly, the objectives of this study were to evaluate the effect of 20 wt% addition of iodoform on the hydration, bioactivity, antimicrobial properties and cytotoxicity of white Portland cement (WPC).

The impact of iodoform on the kinetics of the early hydration and setting reactions of the WPC (up to 70 h) were monitored by isothermal conduction calorimetry. The microstructures of the cements were observed by transmission electron microscopy (TEM) with energy dispersive X-ray spectroscopy (EDX) prior to and following the major exothermic reactions (at 3 and 6 h). The longer term development of the hydrated phases within the pure and iodoform-blended cement pastes was evaluated by powder X-ray diffraction analysis (XRD) and ²⁷Al and ²⁹Si magic angle spinning nuclear magnetic resonance spectroscopy (MAS NMR) at 7, 14 and 28 days. The bioactivities of the cements were determined in vitro by immersion in simulated body fluid and a pseudo-second-order kinetic model was used to compare the rates of formation of hydroxyapatite on their surfaces [24,25]. The impact of iodoform on the biocompatibility of the cement was assessed using human MG63 osteosarcoma cells and its influence on antimicrobial properties was evaluated using the common pathogens Staphylococcus aureus, Pseudomonas aeruginosa and Escherichia coli.

2. Results

2.1. Isothermal Conduction Calorimetry

The rates of heat evolution (per gram of cement powder) of the pure (WPC) and iodoform-blended (WPC-I) white Portland cement are plotted in Figure 1 and compare well with those of other Portland cement-based mixes reported in the literature [26,27,28,29,30]. The setting of Portland cements is governed by a complex sequence of exothermic dissolution and precipitation reactions, during which the initial heat evolved within the first 24 h is principally dictated by the formation of ettringite and the hydration of alite (which reacts more rapidly and is more abundant than belite).

On mixing with water, the wetting of the cement grains, dissolution of hydroxide, sulfate and aluminate species, and the initial precipitation of early hydrates gave rise to a strongly exothermic signal within the first few minutes. This initial signal was not recorded in the thermograms shown in Figure 1, as the calorimeter required 15 min to equilibrate. The thermograms of WPC and WPC-I commenced during the ‘induction’ (or dormant) period which persisted up to 1 h 30 min after mixing, during which the dissolution and precipitation reactions were slow and heat evolution was low [28]. The subsequent intense exotherm, observed after approximately 2 h 45 min for both samples, was attributed to renewed ettringite formation and generated maximum heat flows of 25.8 ± 0.9 and 23.7 ± 0.9 mW g⁻¹ for WPC and WPC-I, respectively. The ensuing acceleration phase was denoted by an increase in heat flow that was largely dictated by the rate of precipitation of the C-S-H gel. The respective maximum rates of heat evolution during the acceleratory period for WPC and WPC-I were 5.1 ± 0.7 kg⁻¹ (4 h 40 min after mixing) and 5.0 ± 0.7 W kg⁻¹ (5 h after mixing). The deceleratory stage which followed was characterised by a steady reduction in hydration rate as the cement matrix consolidated and the reactions became diffusion controlled [28].

2.2. Transmission Electron Microscopy

TEM bright field images were taken of WPC and WPC-I to evaluate any differences in the microstructures of the cements immediately after the exotherm arising from renewed ettringite formation (at 3 h) and after the maximum heat evolution during the acceleratory period (at 6 h) (Figure 2). After 3 h, the cement microstructures of both WPC and WPC-I were characterised by fibrillar C-S-H gel intermixed with lath-like crystals of ettringite of varying sizes (Figure 2). The ettringite crystals in the unblended WPC sample were considerably smaller and more numerous than those of the iodoform-blended paste after curing for 3 h. Six hours after mixing, following the maximum heat flow during the acceleratory period, an increase in the proportion and density of the C-S-H gel was observed and the ettringite crystals were of similar sizes and dimensions in both cement pastes (~100 nm in width with aspect ratios greater than 10).

Atomic ratio plots of I/Ca against Al/Ca from TEM-EDX analysis of the ettringite phase in the iodoform-blended cement pastes at 3 and 6 h (WPC-I-3 h and WPC-I-6 h, respectively) are shown in Figure 3. These data indicate that some iodine was released from the iodoform and nonstoichiometrically incorporated into the ettringite phase (as evidenced by the low linear correlation between I/Ca and Al/Ca). No correlation was observed between I/Ca and Si/Ca for the C-S-H gel phase, indicating that iodine was not taken up into the structure of the C-S-H gel to any appreciable extent. However, the variable I/Ca ratio indicates that iodoform, and/or possibly other released iodine species, were adsorbed onto the C-S-H gel phase.

2.3. Powder X-ray Diffraction Analysis

Powder XRD patterns are shown in Figure 4 of the pure and iodoform-blended cement pastes after hydration for 7, 14 and 28 days. These qualitative powder XRD data show that the reflections for alite and belite persisted throughout the 28-day observation period, yet diminished in intensity, indicating that the cements were not fully hydrated within 28 days. The evolution of the very strong reflections of portlandite (at 18.1, 28.8, 34.2, and 47.2°) is clearly observed in the diffractograms of both WPC and WPC-I, and ettringite is evident from the weaker peaks at 9.1, 15.8, and 22.9° [25]. The major C-S-H gel product was poorly crystalline, and its presence is denoted by cambers in the baseline in the 2θ ranges 10–15° and 25–35° [27].

The relative intensities of the reflections of iodoform in the XRD patterns of sample WPC-I (at 23.5, 26.1, 28.7, and 44.7°) diminished as a function of time (Figure 4b). Reflections from iodoform indicate that this phase was present as discreet crystallites within the cement matrix rather than individually dispersed molecules. As hydration progressed, the reduction in intensity of the iodoform reflections may have arisen from the dissolution and dispersion of the crystallites as the microstructure of the cement developed or could indicate that the iodoform was undergoing chemical reaction in the alkaline environment within the cement matrix. Throughout the 28-day observation period, no evidence was found for the formation of any additional iodine-bearing constituents, or any other phases that are atypical of Portland cements hydrated under ambient conditions.

2.4. ²⁷Al and ²⁹Si Magic Angle Spinning Nuclear Magnetic Resonance Spectroscopy

²⁷Al and ²⁹Si MAS NMR techniques are sensitive to the local chemical environment of the aluminate and silicate tetrahedra within the anhydrous and hydrated product phases of Portland cements [26,27,29,31,32,33,34]. These techniques are complementary to XRD for the structural determination of poorly crystalline and amorphous phases as they do not rely on long-range molecular order.

²⁷Al MAS NMR spectroscopy is used to determine the coordination environment of aluminium species in cements. Aluminium in octahedral coordination, such as those in the AFt and AFm phases, gives rise to resonances in the approximate chemical shift range 20 to −10 ppm; whereas tetrahedral aluminate species, such as those substituted into alite, belite and C-S-H gel, resonate between 100 and 50 ppm [34]. Signals arising from the anhydrous aluminate and ferrite phases are not present in the ²⁷Al MAS NMR spectra of Portland cements as they are extensively line-broadened. The intensity of the resonances in the ²⁷Al MAS NMR spectra are not directly proportional to the relative concentrations of the aluminium species from which they arise owing to the quadrupolar nature of the ²⁷Al nucleus [34].

The ²⁷Al MAS NMR spectrum of the anhydrous cement and those of WPC and WPC-I following hydration for 7, 14 and 28 days are presented in Figure 5. In these spectra, ‘spinning side bands’ are harmonics that result from the modulation of the magnetic field at the spinning frequency and are denoted by asterisks.

The spectrum of anhydrous white Portland cement (labelled WPC in Figure 5a) comprises a broad asymmetric resonance at approximately 82 ppm that arose from isolated aluminate tetrahedra substituted into alite and belite [35]. As hydration proceeded, unresolved resonances of octahedral aluminate species in ettringite (AFt) and monosulfate (AFm) appeared at 13.2 and 11.0 ppm, respectively, along with a third octahedral aluminate signal at 5.0 ppm assigned to an amorphous aluminate hydrate phase [36]. Between 7 and 28 days, the reduction in the intensity of the AFt signal relative to that of AFm is indicative of the progressive conversion of ettringite to the more thermodynamically stable monosulfate phase.

The ²⁷Al MAS NMR spectra of the hydrating WPC-I sample (Figure 5b) resemble those of the unblended WPC paste (Figure 5a) with respect to the presence of signals arising from substituted aluminate tetrahedra in the C-S-H gel phase and octahedral aluminate in the AFt, AFm and amorphous aluminate hydrate phases. However, the AFt signals in the spectra of the iodoform-blended cement are more intense than those of the plain WPC paste and the rate of conversion of ettringite to monosulfate is slower.

²⁹Si MAS NMR spectroscopy is used quantitatively to determine the degree of hydration of the silicate phases in Portland cements, and also to estimate the mean length of the aluminosilicate chains (MCL) and the extent of aluminium substitution (i.e., Al/Si ratio) in the C-S-H gel [26,27,29,31,32,33,34]. In Portland cements, unpolymerised isolated Q⁰ silicate tetrahedra (in alite and belite) appear in the range −65 to −75 ppm, dimeric and chain-end Q¹ species in the C-S-H gel resonate between −78 and −82.5 ppm; and signals arising from mid-chain Q² tetrahedra in the C-S-H gel have a chemical shift range of −84 to −87.5 ppm [34]. Substitution of Al for Si in a neighbouring tetrahedron increases the chemical shift by approximately 5 ppm, such that mid-chain Q²(1Al) species are located in the range −81 to −83 ppm. A more detailed description of the formation, structure and analysis of the C-S-H gel phase in Portland cement-based endodontic materials is provided in reference 29.

The ²⁹Si MAS NMR spectrum of the anhydrous cement and those of WPC and WPC-I after hydration for 7, 14 and 28 days are presented in Figure 6. The spectrum of anhydrous white Portland cement (labelled WPC in Figure 6a) features a sharp Q⁰ signal at −72.5 ppm arising from the isolated silicate tetrahedra in belite superimposed over a broad resonance in the chemical shift range −68 to −78 ppm from the nine crystallographically discrete Q⁰ silicate environments in alite that are unresolved in the MAS NMR spectra of Portland cements [35].

As hydration progressed, resonances corresponding to Q¹, Q²(1Al) and Q² species in the silicate chain structure of the C-S-H gel product began to develop at the expense of the Q⁰ signals from alite and belite (Figure 6). Owing to the nature of the overlapping signals from the various Qⁿ species in hydrating Portland cements, spectral deconvolution was required prior to quantitative analysis (as outlined in Section 4.5).

The relative proportions of the various Qⁿ species, degree of hydration, mean aluminosilicate chain length and Al/Si ratio of the C-S-H gel of WPC and WPC-I following hydration for 7, 14 and 28 days are presented in

Table 1. Composition, degree of hydration, mean aluminosilicate chain length (MCL) and Al/Si ratio of the C-S-H gel of WPC and WPC-I following hydration for 7, 14 and 28 days.

Sample	Time (Day)	Q0(H) (%)	Q1 (%)	Q2(1Al) (%)	Q2 (%)	Hydration (%)	MCL	Al/Si
WPC	7	4.48	29.10	9.17	17.02	59.8	4.1	0.077
	14	2.23	40.19	10.25	15.96	68.6	3.6	0.075
	28	1.38	41.13	9.84	17.79	70.1	3.6	0.070
WPC-I	7	0.95	37.77	8.68	14.85	62.3	3.5	0.070
	14	1.06	39.13	7.08	19.34	66.6	3.5	0.053
	28	0.36	42.73	7.99	18.92	70.0	3.5	0.057

. These data indicate that the incorporation of 20 wt% iodoform in the Portland cement mixture had no significant impact on the rate of hydration with respect to the development of the C-S-H gel phase, with both cements achieving a degree of hydration of ~70% within 28 days. However, the mean aluminosilicate chain length of the C-S-H gel phase in WPC-I was shorter than that of the unblended WPC paste at 7 days, and WPC-I’s Al/Si ratio was also lower than that of WPC at 14 and 28 days.

2.5. In Vitro Bioactivity

Certain bioactive silicate glasses, ceramics and cements have been shown to form chemically stable, mechanically-compliant interfaces with living bone and dental tissues in vivo [24,25,37]. The interface usually develops via the precipitation of a layer of substituted hydroxyapatite (HA), Ca₅(PO₄)₃(OH), from the constituent ions in human body plasma. The HA-layer is similar in structure to the mineral component of bone and provides a focus for the attachment and growth of viable cells which then begin to regenerate the defective host tissue.

A semi-quantitative evaluation of bioactivity can be obtained in vitro by the rate of formation of a layer of HA on the surface of a material immersed in simulated body fluid (SBF), an acellular solution whose ionic concentration approximates to that of human body plasma [24]. Materials that elicit the precipitation of a superficial layer of HA within 4 weeks of exposure to SBF at 37 °C are considered to be bioactive. Since the precipitation of HA on the surface of Portland cement-based materials is known to commence within a few hours [25], in the present study, its formation on the surface of WPC and WPC-I was monitored by FTIR after immersion in SBF for 3, 6 and 24 h. The corresponding supernatant solution concentrations of P, Ca, Si and I were determined by ICP analysis. The concentration of phosphorus was also measured at various intervals for up to 7 days to enable the rates of HA deposition onto WPC and WPC-I to be compared using a simple kinetic model [25].

FTIR spectra of the WPC and WPC-I cements prior to and following immersion in simulated body fluid (SBF) for up to 24 h are presented in Figure 7 and the corresponding concentrations of Ca, P and Si in the supernatant SBF liquors are plotted in Figure 8. In the FTIR spectra of WPC and WPC-I prior to immersion in SBF, stretching vibrations of the C-S-H gel gave rise to the broad combination band centred at 980 cm⁻¹ upon which are superimposed vibrations from carbonate and sulfate groups at 870 and 1120 cm⁻¹, respectively [25,30]. The unresolved doublet at 1490 cm⁻¹ is attributed to calcium carbonate which formed via atmospheric carbonation of the alkaline calcium-bearing cement components. The calcium carbonate was insufficiently crystalline or abundant to be detected by XRD analysis (Figure 4). The broad bands at 3450 and 1660 cm⁻¹ are respectively assigned to the stretching and bending modes of free and bound water within the cement matrix and also to the hydroxyl groups of the hydration products. Stretching of the non-hydrogen bonded hydroxyl group in portlandite produced the sharp signal at 3670 cm⁻¹ in both cements, and the very weak sharp signals of iodoform are also present in the spectrum of WPC-I at 2980, 1260, 1060 and 868 cm⁻¹.

The absence of the characteristic O-H stretching signal of portlandite at 3670 cm⁻¹ in both WPC and WPC-I following immersion in SBF for 3 h denotes the rapid dissolution of this phase (Figure 7). The concomitant appearance of a P-O bending band at ~600 cm⁻¹ is indicative of the formation of amorphous hydroxyapatite which became progressively more crystalline by 24 h, as evidenced by its partial resolution into a doublet (at 570 and 605 cm⁻¹) [25]. The deposition of hydroxyapatite also broadened and shifted the Si-O stretching signal by the superposition of the P-O stretching modes at 960, 1060 and 1100 cm⁻¹ (which do not appear as discrete bands in these spectra) [25,30].

The concentrations of Ca, P and Si species in the supernatant SBF solutions as functions of contact time with WPC and WPC-I are plotted in Figure 8a,b, respectively. These data are consistent with the FTIR spectra (Figure 7) and reflect the rapid dissolution of portlandite from the cement matrix and the simultaneous uptake of HPO₄²⁻ ions during the precipitation of hydroxyapatite. The release of soluble silicate species was also observed from both cements within 3 h which continued with time. The extents of calcium and silicate dissolution from WPC were significantly higher than those of WPC-I; however, these values are not statistically different if the lower cement-content of the iodoform-blended paste is taken into consideration. The initial uptake of HPO₄²⁻ ions at 3 and 6 h was also moderately higher for the unblended paste, although there was no difference in the HPO₄²⁻ concentrations of the SBF solutions in contact with WPC and WPC-I after 24 h. In addition to the release of calcium ions and silicate species, up to 5.8 ppm of iodine were released from WPC-I into the SBF within 24 h, which corresponded to 4.6% of the total iodine present in the blended cement (Figure 8c). The speciation of the released iodine was not determined during this study, so it is not certain whether it is present as iodoform (which has a solubility of 100 ppm in water), elemental iodine, free iodide ions or a combination of species.

Many calcium silicate-based bioactive glasses and ceramics exhibit an induction period on exposure to SBF prior to the deposition of hydroxyapatite which may last for several days [24,37]. During this latent stage, ion-exchange processes take place between the material and solution that increase the calcium ion concentration of the SBF and enhance its supersaturation with respect to hydroxyapatite. The dissolution of calcium ions also promotes the hydration of the silicate surface and the formation of silanol (Si-OH) bonds that provide nucleation sites for HA precipitation [37]. No such induction period is observed for Portland cement-based materials as the rapid dissolution of portlandite and abundance of pre-existing silanol groups presented by the C-S-H gel effect the efficient precipitation of hydroxyapatite [25,30].

The absence of an induction period enables the application of a simple kinetic model to compare the rates of hydroxyapatite formation between different Portland cement-based materials [25]. Accordingly, the removal of HPO₄²⁻ ions from the SBF solution during the precipitation of hydroxyapatite onto the surfaces of WPC and WPC-I are fitted to the simple pseudo-second-order model in Figure 9. Using this model, a linear plot of the ratio of time to uptake of solute (t/q_t) against time indicates pseudo-second-order adsorption [25]. In both cases, the squares of the correlation coefficients, R², are greater than 0.999 which confirms the soundness of the relationships between the experimental data points and the theoretically fitted regression curves. The apparent pseudo rate constants for WPC and WPC-I, 3.92 (± 0.59) × 10^-4 and 2.86 (± 0.43) × 10⁻⁴ g mg⁻¹ min⁻¹, respectively, are not statistically different (p = 0.066) indicating that the presence of 20 wt% iodoform had no significant impact on the in vitro bioactivity of the cement paste. This difference is even less significant if the lower cement content of the iodoform blended sample is taken into consideration.

2.6. Antimicrobial Activity

Microbial infection, particularly the formation of multispecies biofilms on implanted materials, is the principal cause of failure in dental treatments. Current strategies to defend dental materials from biofilm accumulation by the addition of antimicrobial additives and fillers are comprehensively reviewed in reference [38]. The microbiota of dental biofilms is exceptionally complex and, in addition to the characteristic oral microorganisms, other facultative pathogenic bacteria (e.g., S. aureus, P. aeruginosa and E. coli) are commonly detected in bone and dental implant-centred infections [39]. The eradication of S. aureus, P. aeruginosa and E. coli is problematic owing to their persistent biofilm forming capabilities. These microorganisms secrete a protective polysaccharide layer that defends against the immune response and antibiotic therapy, which may require surgical revision.

The results of the in vitro antibacterial assays are listed in

Table 2. Cell viability data for control cultures and those containing WPC or WPC-I.

Bacterium: Cement Concentration	Control	WPC	WPC-I
S. aureus: 5 mg cement cm−3
Mean (cfu cm−3)	4.70 × 109	5.36 × 107	2.08 × 107
St. Dev. (cfu cm-3)	1.43 × 109	2.83 × 107	1.45 × 107
Observed |t|	-	9.63	8.23
S. aureus: 10 mg cement cm−3
Mean (cfu cm−3)	4.70 × 109	4.44 ×107	1.08 × 106
St. Dev. (cfu cm−3)	1.43 × 109	5.10 × 106	1.45 × 105
Observed |t|	-	6.47	8.27
S. aureus: 15 mg cement cm−3
Mean (cfu cm−3)	4.70 × 109	1.68 × 105	No growth
St. Dev. (cfu cm−3)	1.43 × 109	8.80 ×104	-
Observed |t|	-	6.53	-
P. aeruginosa: 5 mg cement cm−3
Mean (cfu cm−3)	1.03 × 109	3.66 × 108	8.13 × 108
St. Dev. (cfu cm−3)	3.20 × 108	2.00 ×108	5.10 × 108
Observed |t|	-	4.5	0.89
P. aeruginosa: 10 mg cement cm−3
Mean (cfu cm−3)	1.03 × 109	2.17 × 107	No growth
St. Dev. (cfu cm−3)	3.20 × 108	2.70 × 106	-
Observed |t|	-	8.93	-
P. aeruginosa: 15 mg cement cm−3
Mean (cfu cm−3)	1.03 × 109	No growth	No growth
St. Dev. (cfu cm−3)	3.20 × 108	-	-
Observed |t|	-	-	-
E. coli: 5 mg cement cm−3
Mean (cfu cm−3)	4.95 × 108	2.11 × 107	No growth
St. Dev. (cfu cm−3)	2.26 × 108	1.77 × 107	-
Observed |t|	-	7.23	-
E. coli: 10 mg cement cm−3
Mean (cfu cm−3)	4.95 × 108	No growth	No growth
St. Dev. (cfu cm−3)	2.26 × 108	-	-
Observed |t|	-	-	-
E. coli: 15 mg cement cm−3
Mean (cfu cm−3)	4.95 × 108	No growth	No growth
St. Dev. (cfu cm−3)	2.26 × 108	-	-
Observed |t|	-	-	-

Critical |t| = 2.35 at p = 0.05 and (n − 1) degrees of freedom.

for control cultures of S. aureus, P. aeruginosa and E. coli and those incubated with 5, 10 or 15 mg of cement per cm³. These data demonstrate that, by virtue of its high alkalinity, the unblended cement inhibited the growth of all three bacteria with the greatest antimicrobial effect against E. coli.

These data also demonstrate that the incorporation of iodoform enhanced the antimicrobial properties of the cement against both the Gram-positive (i.e., S. aureus) and Gram-negative (i.e., P. aeruginosa and E. coli) bacteria at 10 and 15 mg cement cm⁻³ in the case of S. aureus, 10 mg cement cm⁻³ for P. aeruginosa, and at 5 mg cement cm⁻³ for E. coli (Table 2).

The minimum inhibitory and minimum bactericidal concentration ranges for the cements with and without iodoform are summarised in

Table 3. Minimum inhibitory and minimum bactericidal concentration ranges for WPC and WPC-I.

Bacterium		S. Aureus	P. Aeruginosa	E. Coli
Minimum inhibitory range (mg cm−3)	WPC	10–15	10–15	5–10
	WPC-I	10–15	5–10	0–5
Minimum bactericidal range (mg cm−3)	WPC	>15	10–15	5–10
	WPC-I	10–15	5–10	0–5

. The minimum inhibitory concentration (MIC) is the lowest concentration of a substance that will inhibit the visible growth of a microorganism following overnight incubation. The minimum bactericidal concentration (MBC) is the lowest concentration that will prevent microbial growth after subculture [40]. The MBC is also defined as the lowest concentration of a substance that reduces the viability of the initial bacterial inoculum by > 99.9%, which is the criterion upon which the MBC ranges for WPC and WPC-I have been determined [40]. These data demonstrate that the incorporation of iodoform reduced the MIC range of the cement for P. aeruginosa and E. coli, but not for S. aureus (Table 3). Moreover, in all cases, iodoform was found to significantly reduce the MBC of the cement (Table 3).

2.7. Biocompatibility

Human osteosarcoma cells are commonly employed for the initial biocompatibility appraisal of biomaterials for dental and orthopaedic tissue treatment [41,42]. In the present study, the cytocompatibility of WPC and WPC-I towards MG63 human osteosarcoma cells was assessed using an MTT assay [41,42]. The results of this in vitro biocompatibility assessment are presented in

Table 4. MG63 osteosarcoma MTT assay data for WPC and WPC-I.

Property	WPC	WPC-I
Mean Absorbance (arb)	1.09	0.88
Standard Deviation (arb)	0.37	0.12
95% Confidence limits (arb)	± 0.36	± 0.12
Observed |t|	1.09
Critical |t|	2.35

. These data indicate that cell viability was approximately 20% greater for the cultures incubated with WPC versus WPC-I, but this difference is not statistically significant at p = 0.05.

3. Discussion

Portland cement-based dental materials require the addition of a radiopacifying agent to facilitate their radiographic distinction from the anatomical tissues of the tooth and periradicular structures [1,2,3,4,5]. Originally, 20 wt% bismuth oxide was added to the first commercial Portland cement-based root filling material, ProRoot™ MTA (Dentsply Sirona, York, PA, USA), to confer radiopacity. This compound is now widely acknowledged to discolour teeth, delay setting, retard hydration, and to reduce the strength and durability of the resulting cement matrix [1,2,3,4,5,26,29].

Iodoform is adequately biocompatible with the various dental tissues and has also seen longstanding service as an antimicrobial radiopaque admixture in calcium hydroxide and resin-based root filling and pulp capping materials [7,8,13,14,15,17,20,21,22,23]. Radiographic studies indicate that 20 wt% replacement iodoform in Portland cement formulations is sufficient to comply with the regulatory radiographic standards for root filling materials [7,18,19,22], yet very little work has been carried out on the impact of iodoform on the complex hydration chemistry of the cement matrix [8].

A recent study reports that 20 wt% iodoform reduced the initial and final setting times of white Portland cement from 150 to 121 min and 200 to 165 min, respectively [8]. Despite this finding, the current research did not identify any significant changes in heat evolution during the first 70 h of white Portland cement hydration in the presence of 20 wt% iodoform, other than a modest reduction in the exotherm arising from renewed ettringite formation (Figure 1). Initial and final setting times of Portland cements do not directly coincide with any specific chemical reactions or calorimetric events, although both setting times are anticipated to fall within the acceleration phase as the plastic cement matrix becomes rigid and begins to develop mechanical strength [28]. In this study, the reported initial and final setting times were both found to occur at the beginning of the acceleration phase (Figure 1) [8].

The reduced exotherm associated with renewed ettringite formation in the iodoform-blended cement may have arisen from the chemical incorporation of iodine species in this phase, as indicated by TEM-EDX. The TEM-EDX data showed a correlation between the I/Ca and Al/Ca molar ratios of ettringite at 3 and 6 h (Figure 3). This is also tentatively supported by the marked increase in the size of the ettringite crystals after 3 h in the iodoform-blended sample relative to that of the pure cement paste (Figure 2). Furthermore, the notable reduction in the relative intensity of the XRD reflections of iodoform in sample WPC-I between 7 and 28 days (Figure 4b) may also indicate that the iodoform is undergoing chemical reaction within the alkaline environment of the cement matrix. The reactivity of iodoform in the cement system is not unexpected, as halogenoalkanes are acknowledged to participate in nucleophilic substitution of the halide for hydroxide ions under mild alkaline conditions in aqueous media [43].

Despite its reactivity within the cement matrix, iodoform was found to have no impact on the rate of hydration with respect to the major C-S-H gel product phase (Table 1). However, it did reduce the substitution of Al for Si in the C-S-H structure at 14 and 28 days. Presumably, the delayed conversion of ettringite to monosulfate in the iodoform-blended cement reduced the concentration of soluble aluminate species available for incorporation into the C-S-H gel during this timeframe.

The two most common radiopacifiers in commercial Portland cement-based dental materials, zirconium oxide (ZrO₂) and bismuth oxide (Bi₂O₃), are known to remain intact and not react or combine with any of the cement phases [29,30,44,45]. However, despite its lack of chemical reactivity, numerous studies have consistently observed that bismuth oxide prolongs setting times [9,29], retards hydration [29,44] and alters the calorimetric behaviour [29] of Portland cement. The specific mechanism of interference of Bi₂O₃ in cement hydration is not known, although it is speculated to arise from poor electrostatic interactions with the cement constituents [29]. There are conflicting reports in the literature that zirconium oxide retards [46], accelerates [45] and has no effect on the setting of Portland cements [7,9]. These discrepancies are attributed to differences in particle size and processing history of the ZrO₂ and variations in composition and water:cement ratio of the cement formulations. Conversely, nanoparticulate ZrO₂ is generally accepted to reduce setting times and accelerate hydration via a mechanism known as the ‘filler effect’ [47]. In spite of the chemical reactivity of iodoform, it appears to have less of an impact on the heat evolution and kinetics of hydration than the nominally inert Bi₂O₃ and ZrO₂ commercial radiopacifiers.

The high alkalinity of Portland cement-based dental materials is considered to impart modest antimicrobial activity. Recent studies have been carried out to enhance the antimicrobial properties of these materials by the incorporation of antibiotic compounds such as chlorhexidine, doxycycline and cetrimide [48,49,50,51]. To date, no studies have been conducted to investigate any changes to the chemistry and microstructure of the cements in the presence of these small organic molecules, so a direct comparison with the results obtained here for the incorporation of iodoform is not currently possible. However, 0.2 wt% chlorhexidine is reported to have a significantly negative impact on calcified bridge formation in the direct pulp capping of dog’s teeth [48]. The minimal reduction in cytocompatibility (Table 4) and bioactivity (Figure 7, Figure 8 and Figure 9) observed for the iodoform-blended cement may represent potential advantages worthy of further histological investigation.

The specific mechanisms by which iodoform exerts microbial disinfection are unclear; although, it has been proposed that free iodine is released which oxidatively denatures bacterial proteins and also reacts with unsaturated lipids to disrupt the cell membrane [52]. A previous ‘zone of inhibition’ study [8] demonstrated that 20 wt% iodoform significantly enhanced the intrinsic antimicrobial effect of Portland cement against S. aureus, P. aeruginosa and E. coli, indicating that antimicrobial iodine species are released from the cement matrix to diffuse through the agar medium. The present research has also confirmed the release of iodine species from the blended cement in SBF (Figure 8) and has shown that the minimum bactericidal concentration of the blended cement is significantly lower than that of pure Portland cement against all three pathogens (Table 3).

From a clinical perspective, the enhanced antimicrobial activity with no significant concomitant reduction in bioactivity or cytotoxicity associated with the incorporation of iodoform in Portland cement is clearly advantageous. Whether the observed compositional changes in the AFt, AFm and C-S-H phases and ongoing dissolution of iodine species would have a significant impact on the durability of the cement matrix is unknown. Hence, some caution is warranted for long-term clinical applications of iodoform-blended Portland cements. This notwithstanding, a recent 24-month clinical trial with radiographic assessments on Portland cement mixed with either 20 wt% ZrO₂ or iodoform for primary molar pulpotomies showed no statistically significant differences in the outcomes between the two radiopacifiers indicating satisfactory clinical performance [22].

4. Materials and Methods

4.1. Materials and Sample Preparation

The oxide and calculated Bogue compositions (i.e., proportions of phases present) of the white Portland cement (ex. Lafarge, Gravesend, UK) used in this study were provided by the manufacturer and are listed in

Table 5. Composition of white Portland cement.

Major Oxide Components		Minor Oxide Components		Major Crystalline Phases
Formula	Mass (%)	Formula	Mass (%)	Formula	Mass (%)
CaO	69.2	MgO	0.49	Ca3SiO5	65
SiO2	25.0	P2O5	0.43	Ca2SiO4	22
Al2O3	1.76	Fe2O3	0.33	Ca3Al2O6	4.1
SO3	2.00	SrO	0.14	Ca2(Al/Fe)O5	1.0

. All other reagents were purchased from Sigma-Aldrich (Gillingham, UK) and used without further purification or modification.

White Portland cement (WPC) paste samples were prepared by manually mixing 10 g of cement with 3.5 g of distilled water for 5 min with a polypropylene spatula. Samples blended with 20 wt% iodoform (namely, WPC-I) were prepared similarly with partial replacement of 2 g of the WPC by reagent grade CHI₃ at a water:solid ratio of 0.28 (i.e., a water:cement ratio of 0.35). The resulting pastes were sealed in polypropylene containers and cured at 37 °C until required. Prior to analysis by powder XRD, ²⁷Al and ²⁹Si MAS NMR and FTIR, the hydration reactions were stopped by solvent exchange with propan-2-ol. This was achieved by immersion of twenty 2 mm fragments of the pastes in four consecutive 50 cm³ washings of propan-2-ol in a sonic bath for 30 min. The samples were then dried to constant mass in a vacuum desiccator at room temperature.

4.2. Isothermal Conduction Calorimetry

The rates of heat evolution during hydration of samples WPC and WPC-I were measured by isothermal conduction calorimetry using a Thermometric 2277 TAM calorimeter (Thermometric AB, Stockholm, Sweden) at 37.5 °C (i.e., body temperature). In triplicate, approximately 0.05 g of accurately weighed freshly mixed cement paste were placed in the calorimeter. Power data were collected every second for 70 h, and the rate of heat evolution per unit gram of cement powder was then calculated by dividing the power data by the original mass of white Portland cement in the paste.

4.3. Transmission Electron Microscopy with Energy Dispersive X-Ray Analysis

TEM-EDX analysis of the early hydration products of WPC and WPC-I after hydration for 3 and 6 h at 37 °C in sealed polypropylene containers were obtained by dispersing the sample in methanol prior to deposition onto a carbon film grid. Bright field images were obtained using a JEOL JEM200CX microscope at 200 kV equipped with a Gata Orius SC200 digital camera (JEOL, Tokyo, Japan).

4.4. Powder X-ray Diffraction Analysis

Powder XRD analysis was carried out on specimens WPC and WPC-I after 7, 14 and 28 days of hydration. Diffraction patterns were obtained using a Bruker D8 diffractometer (Bruker AXS, Karlsruhe, Germany) with Cu Kα = 1.5406 Å, a step size of 0.019 ° in the 2θ range from 5 to 50 ° and a measuring time of 1 s per step. Phase identification was carried out using Powder Diffraction Files (PDF^®) on DIFFRAC.EVA software (Bruker AXS, Karlsruhe, Germany).

4.5. ²⁷Al and ²⁹Si Nuclear Magnetic Resonance Spectroscopy

²⁷Al and ²⁹Si MAS NMR spectra were collected using a JEOL JNM-ECX 300 MHz spectrometer (JEOL (UK) Ltd., Welwyn Garden City, UK). Single pulse ²⁷Al MAS NMR spectra were referenced to the aluminium hexaquo-ion, [Al (H₂O)₆], and obtained with a pulse delay of 0.5 s, an acquisition time of 0.01024 s and 8000 scans. Single pulse ²⁹Si MAS NMR spectra were referenced to tetramethylsilane (TMS) and obtained with a pulse delay of 5 s, an acquisition time of 0.02048 s, and 65,000 scans. The free induction decay profiles were processed by Delta software (provided by JEOL) to obtain spectra which were then analysed using Igor Pro software (WaveMetrics Inc., Portland, OR, USA).

The ²⁹Si MAS NMR spectra were analysed by a method reported by Love et al. [31]. The signal from unreacted alite that obscures the resonances of the hydrated monomers and dimers was subtracted from the spectrum prior to deconvolution. This was accomplished by adjusting the intensity of the anhydrous WPC spectrum to match the intensity of the alite signal in the hydrated spectrum. The adjusted WPC spectrum was then subtracted from that of the hydrated sample prior to deconvolution using iterative fitting of the Q⁰(H), Q¹, Q² and Q²(1Al) ²⁹Si resonances to Voigt lineshapes. The concentrations of the various Qⁿ species, degree of hydration, mean silicate chain length (MCL) and Al/Si ratio were then calculated from the subtracted and deconvoluted spectra [32,33]. The formulae for the calculations of degree of hydration, MCL and Al/Si ratio are given below [31,33], where Qⁿ represents the intensity of the ²⁹Si MAS NMR signal corresponding to the relevant silicate species:

$$Degree of hydration= \frac{Q^0 \left(H\right)+ Q^1+ Q^2+ Q^2 \left(1Al\right)}{Q^0+ Q^0 \left(H\right)+ Q^1+ Q^2+ Q^2 \left(1Al\right)} \times 100\%$$

(1)

$$MCL= \frac{Q^1+ Q^2+ \frac{3}{2} Q^2 \left(1Al\right)}{\frac{1}{2} Q^1}$$

(2)

$$Al/Si= \frac{\frac{1}{2} Q^2 \left(1Al\right)}{Q^1+ Q^2+ Q^2 \left(1Al\right)}$$

(3)

4.6. In Vitro Bioactivity

Simulated body fluid (SBF) was prepared in accordance with the method described in reference 24 and used immediately. 0.15 g of either WPC or WPC-I were contacted with 150 cm³ of SBF in hermetically sealed polypropylene containers at 37 °C for 3, 6, 24, 44, 72 and 168 h. Each analysis was carried out in triplicate. Solution concentrations of Ca, P, Si and I species were analysed by inductively coupled plasma analysis optical emission spectroscopy (ICP-OES) using a TJA Iris simultaneous ICP-OES spectrometer (TJA, MA, USA) and multi-element standards matrix-matched with sodium chloride. The relative standard deviations of the means of the concentrations of the various components were less than 7%. Differences in the concentrations of components in the SBF solutions in contact with WPC and WPC-I were subjected to two-tailed t-tests at p = 0.05. The solid specimens were recovered by filtration after 3, 6 and 24 h, washed once with distilled water, and dried in air at 37 °C for 24 h prior to analysis by FTIR using a PerkinElmer Paragon 1000 FTIR spectrophotometer to confirm the formation of a layer of hydroxyapatite. Spectra were recorded between 4000 and 500 cm⁻¹ using pressed KBr discs.

The uptake of HPO₄²⁻ ions during the precipitation of hydroxyapatite on the surfaces of WPC and WPC-I was modelled using the pseudo-second-order rate expression Equation (4) [25], where k₂ is the apparent pseudo-second-order rate constant (in g mg⁻¹ min⁻¹), q_t is the extent of sorption at time t (in mg g⁻¹), and qe is the extent of sorption at equilibrium (in mg g⁻¹):

$$\frac{t}{q_t}= \frac{1}{k_2{q}_e^2}+ \frac{1}{q_e} t$$

(4)

Estimates of k₂ and q_e for the uptake of HPO₄²⁻ ions by WPC and WPC-I were derived from the intercept and gradient of a linear plots of t/q_t against t. In both cases, the product moment correlation coefficient, R², was estimated as an indication of goodness of fit, and the difference between k₂ values for WPC and WPC-I were tested using a two-tailed t-test at p = 0.05.

4.7. Antimicrobial Activity

Overnight cultures of Staphylococcus aureus (NCIMB 9518), Pseudomonas aeruginosa (NCIMB 8628) and Escherichia coli (NCIMB 9001) were grown in separate McCartney bottles containing 10 cm³ of nutrient broth (Oxoid). Cement samples, WPC and WPC-I, were prepared according to the method described in Section 4.1 and cured for 6 h prior to grinding with a mortar and pestle and passing through a 1 mm sieve. WPC or WPC-I at concentrations of 50, 100 and 150 mg were added separately to McCartney bottles containing 9 cm³ of nutrient broth. These tubes were inoculated with cultures of S. aureus, P. aeruginosa or E. coli to densities of 1.9 × 10⁵, 9.5 × 10⁵ and 4.2 × 10⁴ colony forming units per cm³ (CFU cm⁻³), respectively. Each assay was carried out in triplicate. The cultures were then incubated, with shaking, at 37 °C overnight and duplicate plate counts on nutrient broth (Oxoid) were taken for each assay.

4.8. Biocompatibility

The in vitro biocompatibilities of WPC and WPC-I were evaluated using MG63 human osteosarcoma cells (ECACC code: 86051601) as described in reference [53]. In quadruplicate, WPC and WPC-I cement samples were cast into 24-well plates and sterilised via UV irradiation for 3 h on each side. MG63 cells were harvested from the main culture at low-passage (<10) at confluency of 80–90% and >90% viability. They were suspended in fresh media and added to the cement-containing wells at 1 × 10⁴ cells/well and 2 cm³ total volume. The cells were then incubated for 24 h. An MTT (3-(4,5-dimethyl-2-thiazolyl)-2,5-diphenyl-2H-tetrazolium bromide) analysis was conducted to evaluate the toxicity of the cements. The original media was decanted off and 2 cm³ of fresh media were added per well. Then, 0.4 cm³ of filter-sterilised solution of 25 mg of MTT in 50 cm³ of 0.01 M PBS solution were placed in each well and incubated for four hours at 37 °C and 5% CO₂. The media was decanted off, 2 cm³ of DMSO were added and the plates were incubated at room temperature for 30 min. 0.2 cm³ of each solution was put onto a 96-well plate and the absorbance was read at 540 nm using a Multiskan Ascent microplate photometer plate reader (Thermoelectron Corporation, Thermoscientific, UK). The control consisted of wells with media only whose absorbance was subtracted from those of the wells containing the cements and cells. The absorbance data were subjected to a two-tailed t-test at (n-2) degrees of freedom. The null hypothesis was tested at p = 0.05.

5. Conclusions

Iodoform (CHI₃) is an alternative radiopacifier for Portland cement-based dental materials. Its impact on the setting, bioactivity, antimicrobial properties and cytotoxicity of white Portland cement were evaluated in this study. Isothermal conduction calorimetry and ²⁹Si magic angle spinning nuclear magnetic resonance spectroscopy showed that the addition of 20 wt% iodoform had no significant impact on the kinetics of cement hydration with respect to the formation of the major calcium silicate hydrate (C-S-H) gel product. Transmission electron microscopy with energy dispersive X-ray analysis demonstrated that iodine species were taken up by the ettringite phase. Both pure and iodoform-blended cements inhibited the growth of Staphylococcus aureus, Pseudomonas aeruginosa and Escherichia coli. In all cases, iodoform enhanced the antimicrobial effect and significantly reduced the minimum bactericidal concentration of the cement. Iodoform was found to have no significant adverse effects on in vitro bioactivity or cytotoxicity with respect to human MG63 osteosarcoma cells. However, from a clinical perspective, its potential reactivity and the consequent long-term stability of the cement matrix should be regarded with caution.