Introduction
In orthodontic treatment, the acceleration of tooth movement is often desired to reduce the treatment duration. However, after the completion of orthodontic treatment, it is crucial to stabilize the tooth position and prevent tooth relapse. This process heavily relies on effective regulation of fiber and bone remodeling in the periodontal tissue. Enhancing periodontal remodeling has long been a challenging aspect of orthodontic treatment.
Previous research has primarily focused on pharmacological approaches to modulate periodontal tissue remodeling. Chemically modified tetracycline-3 (CMT-3) [
1] has shown promise in stabilizing tooth position by improving the bone density in the mesial and distal alveolar bone. Raloxifene [
2] has demonstrated the ability to inhibit osteoclast formation and promote bone volume. Aspirin [
3] has been found to reduce the expression of TNF and IFN in the serum and periodontal ligament induced by orthodontic force. Orthodontic relapse can be mitigated by inhibiting the differentiation of CD
4+ T cells and Th1 cells. Atorvastatin [
4] has been shown to decrease tooth movement by upregulating OPG protein expression in the periodontal tissue and reducing the number of osteoclasts. While drug therapy offers advantages in terms of reduced invasiveness, it may also lead to serious systemic adverse reactions. Therefore, researchers have turned their attention to exploring physical methods. Low-level laser therapy (LLLT) has gained popularity in the field of dentistry due to its excellent penetration capability and safety profile [
5].
Varella [
6] conducted a study demonstrating that LLLT can accelerate the movement of canine teeth. Abdehameed [
7] obtained similar results, showing that combining LLLT with micro-osteoperforations in canines could achieve the fastest movement speed. Kau [
8] and Timothy [
9] utilized pulsed LED devices in early-stage orthodontic treatment, resulting in an increased tooth movement speed of 1.12 mm/week compared to the control group's 0.49 mm/week. During the retention period following orthodontic treatment, researchers had reported that LLLT promotes the expression of MMP mRNAs, reduces the immunoreactivity of TIMP-1, thereby enhancing the immunoactivity of Col-I collagen, promoting the synthesis of periodontal fibers over degradation, and ultimately stabilizing teeth with fixed retainers [
10]. Convisar [
11] and Salehi [
12] found that LLLT reduced tooth relapse by stimulating tissue remodeling and increasing bone density. In contrast to sagittal tooth movement, rotated tooth movements were more complex and prone to relapse. Clinical and animal experiments had shown that LLLT can significantly reduce the relapse of rotated teeth [
13].
As a novel physical stimulation therapy for regulating tooth movement, the molecular mechanisms of LLLT are not yet fully understood. However, several hypotheses have been proposed. The mitochondrial theory [
14] suggests that LLLT activates cytochrome c oxidase (CCO) at the end of the respiratory chain, leading to increased electron transfer and more ATP synthesis. The reactive oxygen species (ROS) theory [
15] proposes that LLLT enhances oxidative potential, promotes ROS synthesis, and increases cellular redox activity, subsequently activating downstream pathways. According to the theory of calcium ions (Ca
2+) theory [
16], LLLT increases cell membrane permeability, resulting in an influx of Ca
2+. Ca
2+ can then transmit signals through CCO and nuclear factor-κB (NF-κB). As an important second messenger, Ca
2+ participates in the mechanotransduction, influencing the cell's response to stimuli. Recent research has shown that Ca
2+ is not only involved in mechanochemical signal transduction, but also plays a role in mediating the biological effects of LLLT, as blocking Ca
2+ channels diminishes these effects [
17].
Our previous studies demonstrated that LLLT could significantly reduce the retention period in rats and promote tooth stability [
18]. Based on the aforementioned information, we hypothesize that LLLT can accelerate the speed of tooth movement during orthodontic treatment and reduce tooth relapse during the fixed retention period. To further investigate this, we examined the effects of LLLT on collagen and bone remodeling induced by hPDLCs under mechanical force and aimed to explore the possible underlying mechanisms.
Materials and methods
Cell culture
hPDLCs were isolated from the premolars extracted during orthodontic treatment from 12–17 years old teenagers. Informed consent was obtained from both the patients and their guardians, and the study was conducted under the guidance and approval of the ethics committee of Tianjin Stomatology Hospital. Tissue culture methods were employed to isolate hPDLCs, which were then cultured and passaged in 75cm2 culture flasks. The complete culture medium consisted of 10% FBS (Gibco, USA) and 1% penicillin–streptomycin (Gibco, USA). The cells were incubated in a humidified atmosphere with 5% CO2 at 37 °C. Passage 3 cells were used for subsequent experiments.
hPDLCs Tensile stress model and LLLT irradiation
The experiment utilized a cell tensile stress loading device that was independently developed by Tianjin University of Technology. Once the cells adhered to the wall, tensile stress was applied at a frequency of 0.5 Hz and an elongation of 2% for a duration of 2 h per day, spanning a total of 2 days in both Group T and Group LT. An 808 nm GaAlAs diode laser with an output power of 48 mW, along with a fiber probe featuring a spot area of 0.785 cm2, was employed. The distance between the bottom of the silicone chamber and the laser source was maintained at 3 cm. An energy density of 2.45 J/cm2 was applied with an exposition time of 40 s. Laser irradiation was conducted in Group LT, one hour after the application of force loading, which followed the same protocol as Group L was in accordance with.
Flow cytometry
For cell cycle detection, a cell cycle detection kit (Beyotime, China) was utilized following the manufacturer's instructions. Initially, hPDLCs were seeded in silicone chambers at a density of 3 × 106 cells per chamber. To synchronize the cell cycle, the cells were pre-treated with a culture medium containing 2% FBS for 16 h. After the experimental treatment, the cells were collected and fixed overnight with 70% ethanol at -20 °C. The next day, the cells were washed twice with cold PBS and stained with a PI working solution (containing 100 μg/mL RNase A, 40 μg/mL PI, and 0.1% Triton X-100) at room temperature for 0.5 h in the dark. DNA content analysis was performed using a flow cytometer (Becton Dickinson, USA), and the data obtained was analyzed using the Flow Jo program.
Real-time PCR
hPDLCs (5 × 10
6/chamber) were seeded in a silicone chamber. After experimental treatment, the culture medium was removed, and the cells were collected for total RNA extraction using the SteadyPure Universal RNA Extraction Kit (Accurate Biology, China), according to the manufacturer's instructions. A cDNA reverse transcription was then conducted with Evo M-MLV RT Premix (Accurate Biology, China). Real-time PCR was performed with a Light Cycler/Light Cycler 480 Real-Time PCR System (Roche Diagnostics, Switzerland) using TB Green™ Premix Ex Taq™ I (Takara, Japan). Relative quantification was achieved by the comparative 2
−ΔΔCt method. Designed primer sequences were taken from the NCBI website. All primers were synthesized in Shengong, Shanghai. The sequences are listed in Table
1.
GAPDH | F:5’-GCACCGTCAAGGCTGAGAAC-3’ R:5’-TGGTGAAGACGCCAGTGGA-3’ |
Runx2 | F:5’-GAGATTTGTGGGCCGGAGTG-3’ R:5’-CCTAAATCACTGAGGCGGTC-3’ |
OCN | F:5’-CTCACACTCCTCGCCCTATTG-3’ R:5’-GCTTGGACACAAAGGCTGCAC-3’ |
NFATC1 | F:5’-CCATGAAGTCAGCGGAGGAA-3’ R:5’-GAGGTCTGAAGGTTGTGGCA-3’ |
c-FOS | F:5’-GTCTCCAGTGCCAACTTCAT-3’ R:5’-CAGCCATCTTATTCCTTTCC-3’ |
CTSK | F:5’-CAGAATGGGAAGGTAGAGC-3’ R:5’-AACTGGAAGGAGGTCAGG-3’ |
MMP-1 | F:5’-AGAGCAGATGTGGACCATGC-3’ R:5’-TTGTCCCGATGATCTCCCCT-3’ |
MMP-2 | F:5’-ACCAGCTGGCCTAGTGATGAT-3’ R:5’-AAGGTGTTCAGGTATTGCATGT-3’ |
MMP-9 | F:5’-CGCAGACATCGTCATCCAGT-3’ R:5’-AACCGAGTTGGAACCACGAC-3’ |
TIMP-1 | F:5’-ATTCCGACCTCGTCATCAGG-3’ R:5’-GCATCCCCTAAGGCTTGGAA-3’ |
TIMP-2 | F:5’-TAGTGATCAGGGCCAAAGCG-3’ R:5’-CTCAGGCCCTTTGAACATCTTT-3’ |
Col-I | F:5’-CCCTGAACTCTGCACCAAGT-3’ R:5’-GGGGTGGTAGAGTGGATGGA-3’ |
Col-III | F:5’-CCAGGAGCTAACGGTCTCAG-3’ R:5’-CAGGGTTTCCATCTCTTCCA-3’ |
Weston blot assay and antibodies
The proteins of hPDLCs were harvested with a RIPA lysis buffer (Beyotime, China), and the protein concentration was measured using a BCA protein assay kit (Solarbio, China). Proteins were separated on SDS–PAGE (8–20% gel) and transferred to PVDF membranes. The membranes were blocked for 0.5 h with a blocking reagent, and then were washed and incubated with a primary antibody at 4 °C overnight. After several washes, the membranes were incubated with secondary antibodies (Beyotime, China) at room temperature for 1 h. ECL solution A and solution B (Beyotime, China) were mixed to image the membranes in a darkroom (Bio-Rad ChmiDoc, USA). The primary antibodies were listed in the following manner: GAPDH (ABclonal,1:5000,USA), NFATC1 (ABclonal,1:1000,USA), TIMP-1 (ABclonal,1:1000,USA),TIMP-2 (ABclonal,1:1000,USA), MMP-1 (ABclonal,1:1000,USA),MMP-2 (ABclonal,1:1000,USA), Runx2 (ABclonal,1:1000,USA),MMP-9 (ABclonal,1:1000,USA), COL-I (ABclonal,1:1000,USA), COL-III (ABclonal,1:1000,USA), c-Fos (CST, 1:1000, US), OCN (CST, 1:1000), CTSK (Abcam,1:1000).
Intracellular ROS, Ca2+ using fluorescence microplate
hPDLCs (3 × 106/well) were seeded in a silicone chambers. The cells were subjected to tensile stress for 1 h, followed by laser irradiation. Immediately after irradiation, the cells were harvested using trypsin. To detect ROS levels, the cells were exposed to DCFH-DA (1 μM) from the ROS detection kit (Beyotime, China). For Ca2+ release detection, Fluo-3/AM (1 μM) from Dojindo Laboratories was used. The cells were incubated at 37 °C for 20 min. After incubation, the cells were washed twice and resuspended in PBS. A total of 100 μl of the cell suspension was added to a fluorescence microplate. The fluorescence intensity was measured using a multifunctional enzyme labeling instrument (Tecan SPARK, Switzerland) with an excitation wavelength of 488 nm and an emission wavelength of 520 nm. Each group was evaluated in triplicate, and the levels of ROS and Ca2+ were represented by fluorescence intensity.
Statistical analysis
Experiments were performed independently at least three times. The results were presented as the mean ± standard deviation and statistically analyzed with a one-way ANOVA, unless noted otherwise specified. A two-tailed P-value < 0.05 was considered statistically significant. Statistical analysis was conducted in SPSS version 20.0 (IBM).
Discussion
Currently, LLLT is widely used in the field of orthodontics, but there is still a need for further research to understand its molecular mechanisms and determine the optimal application parameters. Among the different types of low-level lasers used in oral clinical practice, GaAlAs semiconductor lasers have several advantages, including small size, lightweight, ease of operation, and safe application. These lasers can directly affect deep tissues, promote microvascular expansion, enhance the oxygen-carrying capacity of red blood cells, stimulate various biological processes such as RNA and DNA synthesis, and promote protein secretion. As a result, they can enhance the cellular and molecular responses in tissue repair [
19].
Orthodontic tooth movement (OTM) involves bone resorption on the compression side and new bone formation on the tension side in response to mechanical forces. This process relies on the proliferation and differentiation of various cells [
20‐
22]. PDLCs play a crucial role as they are the primary sensors that respond to mechanical signals and regulate tissue remodeling [
23]. Our results demonstrated that tension stress stimulation led to an increase in hPDLCs entering the DNA synthesis phase, providing a cell reserve for periodontal tissue remodeling. When combined with laser irradiation, more cells progressed through the cell division phase via the G2/M checkpoint, actively participating in periodontal remodeling [
24,
25]. Accumulating evidence suggests that LLLT, when applied at appropriate doses, can promote cell proliferation and differentiation in various cell types, including bone marrow mesenchymal stem cells [
26], stem cells from the apical papilla [
27], and human adipose-derived stem cells [
28].
The results obtained from PCR and Western blot analysis revealed that under tension stress, the expression of bone remodeling factors significantly increased, indicating the active involvement of hPDLCs in osteogenesis and osteoclast remodeling. However, the intervention of LLLT promoted the expression of osteoclast differentiation factors while inhibiting the expression of osteogenic differentiation factors. This observation suggests that there may be an asynchronous bone remodeling process occurring. Bone remodeling induced by mechanical force consists of three stages: bone resorption mediated by osteoclastogenesis, the release of cytokines during the process of bone resorption to induce osteoblast differentiation, and subsequent reversal of bone resorption was reversed, followed by osteoblast-mediated bone formation, ultimately completing the process of bone remodeling process. It is well known that bone resorption mediated by osteoclastogenesis is a rate-limiting step in tooth movement. Therefore, LLLT selectively stimulates the process of osteoclastogenesis, thereby accelerating the speed of the "bone resorption" stage. Previous studies have shown that LLLT significantly increases osteoclast activity during the initial stage of tooth movement, while having no significant effect on osteoblast activity [
29‐
31].
It is important to note that the optimal parameters for LLLT can vary depending on the cell type being targeted. As mentioned earlier, the biphasic dose–response relationship of LLLT has been observed in in-vitro research and animal experiments. Moreover, the effective dosage range for different cell types is narrow and difficult to overlap [
32]. Therefore, it is not surprising that the same irradiation parameters can lead to contrasting effects. Additionally, we observed an interesting phenomenon where the expression levels of certain factors did not show consistency between mRNA and protein levels. Karu has reported that the increase in reactive oxygen species (ROS) and cytosolic free calcium ion (Ca
2+) concentration caused by LLLT can trigger conformational changes in proteins [
33]. Furthermore, the biological effects of LLLT depend on the initial redox state of cells [
32]. These factors may partially explain the inconsistent findings in our study, but further investigation is needed to elucidate the specific mechanisms involved.
MMPs (matrix metalloproteinases) play a crucial role in the remodeling of periodontal tissue by degrading the extracellular matrix (ECM) and regulating collagen fibers [
34]. TIMPs (tissue inhibitors of metalloproteinases) are natural inhibitors of MMPs. The balance between MMPs and TIMPs determines the rate of bone matrix degradation [
35]. In our experiment, under tension stress, the expression levels of MMP-1, MMP-2, and MMP-9 mRNA and protein in hPDLCs significantly increased, indicating active ECM remodeling. However, the expression of MMPs did not continue to increase indefinitely. The cells responded quickly with protective effects, leading to an increase in TIMPs expression to prevent excessive degradation of periodontal tissue. After laser intervention, significant differences were observed in protein levels, except for TIMP-2. The expression of both MMPs and TIMPs was more pronounced, suggesting that LLLT accelerated ECM remodeling.
The periodontal ligament consists of cells and extracellular matrix, with collagen fibers accounting for 70% of the protein components. Collagen I and III not only provide a structural framework for periodontal ligament reconstruction, but also participate in the regulation of cell proliferation, migration, and specific gene expression through specific amino acid sequences binding to integrin receptors on the cell surface under mechanical force [
36‐
38]. The expression of Col-I and Col-III significantly increased under tension stress stimulation, and the intervention of LLLT enhanced the regulatory effect of mechanical force on collagen remodeling. Based on the previous experiments, we speculate that LLLT may have a greater promoting effect on TIMPs than MMPs, thereby reducing the degradation of collagen by MMPs and resulting in overall promotion of collagen. We also hypothesize that LLLT may have a greater impact on type III collagen, leading to a decrease in the collagen I/III ratio and an accelerated collagen remodeling process. However, it is important to note that the present study did not specifically examine the changes in the ratio of collagen I/III, and further detailed experiments are needed to clarify this hypothesis.
In summary, our study demonstrated that LLLT can promote the process of periodontal remodeling under tension stress. Previous studies have shown that the level of reactive oxygen species (ROS) determines its biological effects. ROS can act as a beneficial signal to accelerate cell metabolism at low levels, but as a harmful cytotoxic agent at high levels [
39,
40]. Appropriate laser irradiation increases intracellular ROS levels and accelerates cell metabolism [
41]. Based on our results, we speculate that the level of ROS developed by LLLT under tension stress is suitable for hPDLCs, as evidenced by the findings from the cell cycle, PCR, and Western blotting assays. However, we observed that tension stress had little effect on ROS levels, which may be attributed to the short duration of force application time and small deformation [
42,
43].
Following mechanical stimulation, hPDLCs translate mechanical signals into chemical signals through mechanochemical signal transduction, thereby initiating subsequent cascade reactions. Previous research has indicated that Ca
2+ is a second messenger in the process of mechanochemical signal transduction [
44,
45]. Our experiments also confirmed that the tension stress altered the Ca
2+ levels, with a more pronounced effect observed when laser irradiation was combined with tension stress. Changes in Ca
2+ levels were detectable after one hour of force application. Our study suggested that the response of hPDLCs to LLLT was also involves the "Central Hub" of Ca
2+. Recent research has discovered that the extracellular Ca
2+ influx following laser irradiation may represent a novel pathway for activating cellular metabolism [
17]. LLLT increases the level of Ca
2+ in hPDLCs under tension stress, potentially accelerating mechanochemical signal transduction. Additionally, LLLT may exert photobiological stimulation through the increase of Ca
2+. However, the precise mechanisms by which Ca
2+ is involved and transferred from excitation to effect require further investigation.
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