Introduction
Dental hard tissues are organised in a three-dimensional and hierarchical manner and exhibit anisotropic mechanical properties [
1‐
3]. Enamel and dentine also have heterogeneity of structure, and the variation in structure and mechanical properties may influence the direction of crack progression [
4].
Laser radiation of dental hard tissues usually results in the observation of cracks. Previous studies using scanning electron microscope (SEM) imaging explored the presence of cracks formed with high laser powers, CO
2 lasers or when irradiated in a dry environment [
5,
6], and are therefore not clinically applicable. Yamada et al. [
7] reported that the irradiation of dentine with a CO
2 laser resulted in cracks that were mostly in the peritubular dentine. Burkes et al. [
8] stated that enamel tissue following Er:YAG laser radiation showed cracks in a dry environment, but no cracks were seen in the wet condition.
The orientation of collagen fibres appears to be particularly significant for the overall dental tissue strength and damage resistance [
9,
10]. In the peritubular dentine, the collagen fibres are arranged parallel to the long axis of dentinal tubules, whereas, in the intertubular dentine, the fibres are perpendicular to the dentinal tubules. X-ray diffraction studies have been used to study the structure of collagen fibres, but are difficult to relate to function as they show no preferred orientation of the apatite crystals, with a lack of alignment between crystals in adjacent fibrils. Therefore, fracture behaviour in dentine may be dominated by the collagen fibril direction rather than the orientation of the apatite crystals [
11].
The thermo-physical characteristics of a tooth vary between the enamel and dentine and even in the individual dental layer; they are anisotropic and inhomogeneous [
12]. The thermal conductivity of heterogeneous substances like a human tooth is greatly influenced by its structure and composition [
13]. Lin et al. [
12] reported that the thermal conductivity of human dentine expressed a weak anisotropy, which might be attributed to the presence of dentinal tubules. The literature reports various values of thermal behaviour of enamel and dentine, which may be attributed to the different design of experiments and scales. However, they agree that the thermal conductivity and diffusivity of dentine are less than that of enamel [
12,
14‐
16].
Tissue interactions with pulsed lasers can be characterised by the thermal relaxation time,
τr given by
\( {\tau}_r=\frac{1}{4\chi {\mu}_a^2} \), where
χ is the thermal diffusivity and
μa is the absorption coefficient. The thermal diffusivity is also given by
\( \chi =\frac{\kappa }{C\rho} \), where
κ is the thermal conductivity,
C the thermal heat capacity and
ρ is the density. Table
1 shows the values of these parameters for dentine, enamel and water. As can be seen in each case, the thermal relaxation time is much less than the pulse length of the laser used (~ 800 μs), and hence, the interaction is thermally driven and there can be some thermal damage to the surrounding tissue.
Table 1
Values of different parameters of enamel, dentine and water
Thermal diffusivity (mm2 s−1) | 0.4 | 0.2 | 0.13 |
Thermal conductivity (W m−1 K−1) | 0.8 | 0.5 | 0.6 |
Absorption coefficient (mm−1) | 154 | 307 | 1280 |
Absorption depth (μm) | 6.5 | 3.3 | 0.8 |
Thermal relaxation time (μs) | 26 | 13 | 1 |
However, the X-ray nano-CT allows high-resolution examination of cracks at the nanoscale, revealing the extent of nano-cracks due to laser irradiation in dental hard tissues. Using the ZEISS Xradia 810 Ultra X-ray microscope, we were able to achieve spatial resolution down to 50 nm [
17]. Nano-CT offers the requisite three-dimensional (3D) spatial resolution for studying dentinal tubules and canaliculi [
18]. It is a technique that permits reconstruction of the 3D internal structure of an object without any preparation, by acquiring X-ray projections from different viewing angles ranging from 0 to 180°. Then, the artefact-free 3D structure of the object can be acquired using a reconstruction algorithm [
19,
20].
The aim of this work was to examine the effect of Er:YAG laser radiation on the 3D ultrastructure of moist human enamel and dentine. Using a laser allowed a defined amount of energy to be applied to the material surfaces in a defined direction. The thermo-mechanical effects and ablative effects of the energy parameters used in the experiments were carefully defined. The amount of ablated tissue following laser radiation was evaluated using a confocal microscope technique, and subsurface nano-cracks were characterised using nano-CT. The null hypothesis to be tested is that there is no difference in the effect of Er:YAG laser between enamel and dentine tissues.
Discussion
Previous studies of irradiation damage in dental tissues have been performed with approaches unable to observe the 3D structure such as transmission electron microscope (TEM) and SEM imaging. These techniques only permit localised observation of the surface [
17].
The irradiated dentine revealed many nanoscale-cracks that were mainly concentrated in the peritubular dentine. Some of them were confined to the mineralised ring of the peritubular dentine. Our cracks also extended into the intertubular dentine. Cracks resulting from laser irradiation are usually the result of elastic waves that are generated in the solid target tissue because of the transient thermal shock produced by the intense and local laser heating, thermal expansion and the ablation product recoiling [
5,
22,
23]. The peritubular area has a higher content of hydroxyapatite than that of intertubular dentine and is brittle and more vulnerable to crack formation with the thermal shock of laser irradiation [
7]. In the three-dimensional view, the cracks can be seen to follow the direction of the mineralised collagen fibres in the inter-tubular dentine but are perpendicular in the peritubular region. The cracks progressed along the tubules (Fig
4).
The crack pattern in our study was localised to the surface, with a mean depth that did not exceed 10 μm and with the cracks appearing somewhat irregular at first look. In another study by Staninec et al. [
24], the cracks were created following irradiation with an Er-Cr-YSGG laser in a dry environment and different laser parameters extending to a depth in the range of 131–300 μm. Another study used a diamond cone indenter to mechanically initiate and propagate cracks in elephant dentine (tusk) and reported that the direction of crack propagation was perpendicular to the dentinal tubule axis [
17]. The explanation for the different results might be attributed to differences in the structure and composition between elephant and human dentine, but also, the method of crack production varied between studies. The tubules of elephant dentine are elliptical and larger than the round tubules of human dentine. The collagen fibrils and the extent of the peritubular dentine in tusks are smaller than those in human dentine. In ivory, the collagen fibrils are oriented perpendicular to the dentinal tubules and parallel to the long axis of the tooth [
25]. In tusk, some of the tubules are filled with carbonated hydroxyapatite which is unlike the case with human dentine. The tubules are arranged over each other axially to form microlaminae. The shape, position and orientation of dentinal tubules into microlaminae are variable for each type of ivory and they can be straight or form wavy structures. The orientation of the tubules can also be different between the adjacent microlaminae [
26].
During laser irradiation, a local rise in temperature is distributed in a non-uniform way throughout the enamel and dentine. Attrill et al. [
27] reported that the temperature excursion was directly related to the total delivered energy, which is only applicable during continuous irradiation. A critical temperature threshold of 5.6 °C was defined as the temperature that is safe for pulp tissue in the presence of water using different parameters. They also showed that a quantifiable estimate of temperature increase can be calculated by following the linear regression equation:
$$ \varDelta {T}_{\mathrm{max}}=0.032E-0.57\kern0.48em \left(\mathrm{with}\kern0.17em \mathrm{water}\right) $$
where Δ
Tmax is the peak temperature increment (°C) and
E is the cumulative energy input (J).
According to this equation, the temperature rise in our study is 0.87 °C, but this describes the overall temperature increase of the tissue. The instantaneous localised temperature increase will be much higher than this. It is known that the interaction mechanism of Er:YAG laser radiation on hard tissues is mediated by rapid heating of water, which creates enormous subsurface pressures leading to explosive removal of material [
28]. This mechanism might be a source of the cracks seen in our study. As seen in Fig.
4, cracks are clear in the irradiated dentine which has a higher water content than enamel tissue. Water has the highest absorption coefficient and it is therefore likely that any water present will drive the interaction. In this study, the dentine was kept moist during exposure and as such the tubules would be expected to be filled with water during irradiation. The mechanism for crack propagation is proposed to be due to the rapid expansion of water vapour in the dentinal tubules leading to micro explosion pressure and the formation of the radial cracks, which propagate through the peritubular dentine and into the intertubular dentine. The cracks are more prominent in peritubular dentine since it is denser and more brittle than intertubular dentine. Forein et al. [
9] investigated the interaction of human dentine mineral nanoparticles and collagen fibres under humidity-driven stress with heating up to 125 °C. Forein et al. showed (as in our experiment) that the nano-composite structure of dentine hinders the propagation of cracks and diverts them in directions orthogonal to the mineralised inter-tubular collagen layers. The tubules may disrupt propagation of the crack through the dentine, disrupting its spread and directing it along the length of the tubule, which is less damaging to the overall performance of the tooth.
According to Table
1, this goes some way to explaining the different results observed between enamel and dentine with the same amount of laser energy used on both. In this study, the nano-CT of irradiated enamel does not show cracks similar to that of the irradiated dentine. Also, the different structure leads to a varied dissipation of heat. In addition, despite also being kept moist during irradiation, the enamel will not contain internal volumes of water in the same way that the tubules in dentine can. Therefore, the null hypothesis was rejected.
The rapid expansion of water in the dentinal tubules is considered to be responsible for crack initiation in the peritubular region and at the interface between peritubular and intertubular regions in dentine. The cracks progress along the interface region then propagate into the intertubular matrix, thus propagating along planes parallel to that of the tubules.
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