Effect of combining Gold Nanoparticles with Diode or Er. Cr:YSGG Laser on the Bond Strength of Etch- and- Rinse Adhesive to Dentin Surface

doi:10.21203/rs.3.rs-4956628/v1

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Research Article

Effect of combining Gold Nanoparticles with Diode or Er. Cr:YSGG Laser on the Bond Strength of Etch- and- Rinse Adhesive to Dentin Surface

https://doi.org/10.21203/rs.3.rs-4956628/v1

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Background

The aim of this work is to study the effect of different types of laser and gold nanoparticles on the bond strength of etched and adhesive dentin surface.

Methods

Sixty human molars were collected; the crowns were removed and a cavity (2x3 mm) was prepared on the buccal and lingual surfaces. Then, the teeth were sectioned perpendicularly to the longitudinal axis. The samples were divided according to the adhesive technique used and the hardness was tested by Vickers hardness tester, the roughness was tested by using universal testing machine and the depth of penetration was tested by Scanning electric microscope.

Results

Compared with those in the control group, the hardness in the groups treated with the laser was significantly greater. Moreover, for roughness, group C1 exhibited greater roughness than did the other groups. With respect to the depth of penetration, Group A0 and Group C0 demonstrated the greatest depth of penetration, while Group B0 and Group D0 demonstrated the lowest depth of penetration.

Conclusions

After applying the adhesive, the laser beam improved the diffusion of the material into the dentinal tubules in the presence of gold nanoparticles and increased the hardness and roughness of the dental structure.

Gold nanoparticles

bond strength

composite resin

diode laser

Cr:YSGG laser

Dental restorations depend on the bonding qualities of tooth resin-based materials¹. Although various studies have demonstrated excellent immediate and short-term bonding of dental adhesives², the long-term stability of the bond remains a crucial concern³. A stable bond is achieved by fully impregnating the dentin with particles of resin monomers, resulting in a uniformly thick and dense hybrid layer⁵. The combination of the dentin organic matrix and other components such as residual hydroxyapatite crystallites, resin monomers, and the solvent forms this hybrid layer. Aging or the breakdown of the hybrid layer may have an impact on each of these distinct parts. There are two types of degradation: exposed collagen fibril degradation (disorganization) and resin degradation (hydrolysis)⁶.

Collagen degradation is mostly caused by an increase in the water content of the bonded interface, which can result from the breakdown of the hybrid layer. There are various methods for producing metal nanoparticles and nanostructures through photo-induced synthesis. These methods can be used to obtain monometallic and bimetallic nanoparticles as well as composite materials. Among these methods, direct photoreduction of AuCl₄ in aqueous solution⁴ or polymer matrices⁸ produces gold nanoparticles. Because of their powerful absorption and scattering capabilities, gold nanoparticles are important components in nanoscience and nanotechnology because of their strong localized plasmonic resonance ^9–10.

Due to their biocompatibility, gold nanoparticles, which can be fabricated with excellent colloidal stability, can be used for bio-imaging and targeted delivery to specific cells^11–12. Different gold nanostructures, such as nanoshells and nanorods, can be used to tune plasmonic resonance over a broad spectral range. Researchers have explored the use of gold nanoparticles within the biomedical sector, including reducing the collagen pore size, decreasing the biodegradation of collagenase, and creating many cross-linked bonds with the collagen structure¹³.

The quality of dentin bonding agents has significantly increased recently¹⁴. Effective dental tissue preparation is crucial for bonding to dentin because it is more challenging than bonding to enamel due to the higher water content and the presence of a smear layer¹⁵. A two-step etch and rinse protocol bonding system has been introduced to facilitate the bonding process, which recommends combining the primer and bonding agent ¹⁶. Following acid etching of the tooth surface, the adhesive agent increases the surface porosity ¹⁷. The ability of monomers to penetrate pores determines the adhesive system's performance¹⁸. Acid etching removes the smear layer, demineralizes the intertubular dentin, and exposes the dentinal tubules^19–20−21.

However, bonding agents cannot penetrate the pores, resulting in gaps between the composite and dentin²². To improve bond strength, methods such as NaOCl application and laser irradiation can deproteinize the dentin surface²³. The collagen network is removed selectively by laser, which improves resin penetration. There are various methods available to increase the bond strength of total-etch adhesive systems ²⁴. One such technique is dentin surface deproteinization, which may be accomplished chemically by using laser radiation or NaOCl. The dentin surface is deproteinized using laser by selectively eliminating the collagen network while leaving the mineralized tissue intact ²⁵. According to Dayem, laser irradiation is a better option than the use of NaOCl for deeper penetration of resin and removal of the collagen network²⁶.

Some researchers have proposed using laser irradiation of the adhesive prior to its polymerization to enhance its bonding to dentin. This can help the bonding agent penetrate better into the dentinal tubules²⁷. Several studies have shown that irradiating the surface with laser after applying an adhesive agent can also improve penetration and increase bond strength^28–29. We employed a two-step adhesive in this study that included an acid etchant and a primer-bonding agent, and we assessed the impact of diode laser and Er,Cr:YSGG laser radiation on bond strength prior to etching, subsequent to etching and primer-bonding agent application. We evaluated the effect of laser irradiation on the deproteinization of etched dentin and monomer penetration depth and its impact on the bond strength of the composite to dentin.

Different microscopy techniques are utilized to analyze the interface between dentin and bonding agents and assess which bonding technique results in fewer gaps and voids in cavity fillings. These microscopy techniques include stereomicroscopy, scanning electron microscopy (SEM), transmission electron microscopy (TEM), and confocal laser scanning microscopy (CLSM) ^30–31.

In this research, we utilized a two-step adhesive that contained an acid etchant and primer-bonding agent infused with gold nanoparticles. We then evaluated the impact of diode laser and Er,cr:YSGG laser irradiation before and after bonding to measure the bond strength and depth of the gold nanoparticles inside the dentinal tubules.

1. Preparation of the Dental Bonding Agent:

There are dental bonding agents available from 3M ESPE that work in two steps. First, an etching and adhesive solution are used to remove the surface of dentin with phosphoric acid and completely eliminate any smear layer. Then, gold nanoparticles are added to the bond as a final coating that is free of solvents. Sigma Aldrich supplied the gold precursor (HAuCl4·3H2O) that was used in this study. The gold precursor was stored in a glove box with a dry argon environment because of its hygroscopic nature. A tiny quantity of acetone was used to dissolve it, and then it was mixed in equal amounts with the bonding solution in a glove box. The mixture was stirred for 20 minutes and then ultrasonicated for 5 minutes.

2. Sample size:

It was calculated based on a previous study³⁵.Based on a recent study, it was found that the response of matched pairs follows a normal distribution with a mean of 17.43 and a standard deviation of 1.33. If we assume a mean difference of 1.5, the minimum sample size required to achieve a probability (power) of 0.8 with a Type I error probability of 0.05 is 8. To meet this requirement, the total sample size was increased to 10 per group. Sample size calculations were performed using P.S. power version 3.1.6 with an independent t- test.

3. Tooth Preparation:

Sixty human molars were collected, and until the experiment started, they were kept in distilled water. Under water lubrication, the crowns were carefully cut using an Isomet 1000 diamond saw. Subsequently, cavities measuring 3 × 3 mm were prepared on the buccal and lingual surfaces of each tooth. Next, the teeth were cut perpendicular to their longitudinal axis. Finally, the sectioned teeth were assigned randomly to different groups, each corresponding to a specific adhesive technique to be employed in the subsequent stages of the experiment.

Control group: acid etching + bonding + light curing

A0: acid etching + (bond + gold nanoparticles) + Er,Cr:YSGG laser.

B0: acid etching + Er,Cr:YSGG laser + (bond + gold nanoparticles) + light curing.

A1: acid etching+ (bond + gold nanoparticles) + Er,Cr:YSGG laser + composite + light curing.

B1: acid etching + Er,Cr:YSGG laser + (bond + gold nanoparticles) + light curing + composite resin + light curing.

C0: acid etching+ (bond + gold nanoparticles) + diode laser.

D0 acid etching + diode laser + (bond + gold nanoparticles) + light curing.

C1 acid + (bond + gold nanoparticles) + diode laser + composite + light curing.

D1 acid + diode laser + (bond + gold nanoparticles) + light curing + composite resin + light curing.

Diode laser (Lasotronix Smart^m PRO laser, Elektoniczna 2A, 05-500 Piaseczna, Poland) with a wavelength of 980 nm and 1W power in a continuous mode and a fiber tip size of 400 µm was used to irradiate the dentin surface. A handpiece was used to transmit the diode laser energy at a speed of 1 mm/second for 20 seconds while maintaining a distance of 2 mm from the target point. Irradiation was performed in a circular motion.

The dentin surface was irradiated in the Dental Materials Laboratory of the Oral and Dental Research Institute, National Research Centre of Egypt using the Biolase I plus, 2780 nm, Er,Cr;YSGG device (BIOLASE, Inc 27042 Towne Centre Drive, Suite 270 Foothill Ranch, CA 92610 − 2811 USA), energy of 300 mJ, a frequency of 10 Hz and a water spray 30%, air 70%. The handpiece was used in non-contact mode, 2 mm away from the surface with a perpendicular beam to the dentin surface and an irradiation duration of 30 secs.

The surface of dentin was subjected to 15 seconds of acid etching using 35% phosphoric acid supplied by 3M Dental Products (St. Paul, MN, USA), followed by a 15 second water wash and a tissue paper blot. According to the manufacturer's instructions, by using a microbrush, two layers of bonding with gold nanoparticles were applied, and the surface remained wet for 15 seconds and gently air-dried for 5 seconds. Then, the sample was cured with LED light curing unit (Kerr, Orange, CA, USA) with an output power of 1200 mW/cm2 for 10 seconds. The samples were tested by scanning electron microscopy to determine whether the gold nanoparticles penetrated the dentinal tubules.

Following a 20-second curing period, an A3 shade composite (3M ESPE St Paul, USA) was applied using a plastic tube measuring 2 mm in height and internal diameter. The samples were light cured for 40 seconds by a light curing unit (Arialux, Apa-dana Tak, Iran) with an intensity of 500 Mw/cm2. The samples were prepared for examination using a universal testing machine for the purpose of measuring bond strength. (SANTAM, SMT-20, Tehran, Iran).

Test procedure:

Using a Vickers diamond indenter and a 20X objective lens, a digital display Vickers microhardness tester (Model HVS-50, Laizhou Huayin Testing Instrument Co., Ltd., China) was used to measure the specimen surface microhardness. For fifteen seconds, the specimen surface was subjected to a 100 g force.

Each specimen had three indentations created on its surface, evenly spaced around a circle and separated by no more than 0.5 mm from one another. Using a built-in scaled microscope, the diagonal length of the indentations was measured, and the Vickers values were converted into microhardness values.

1. Microhardness calculation:

The microhardness was obtained using the following equation: HV = 1.854 P/d2

where HV is the Vickers hardness in kgf/mm², P is the load in kgf and d is the length of the diagonal in mm.

2. Roughness methodology:

Optical methods tend to fulfill the need for quantitative characterization of surface topography without contact³².

Technique: The following image acquisition equipment was used to capture the images:

1) Vertically positioned at a distance of 2.5 cm from the samples, a USB digital microscope with a built-in camera (U500x Digital Microscope, Guangdong, China) with 3 Mega Pixels of resolution. The axis of the lens and the light source make an angle of approximately 90 degrees.

2) Eight LED lights, with a color index of nearly 95%, were used to produce illumination. The lamps were controlled by a control wheel.

3) Using a fixed magnification of 90X, the photos were captured at maximum quality and linked to a suitable personal computer. A resolution of 1280 × 1024 pixels was used to record each image.

To define and standardize the region of roughness measurement, digital microscope pictures were cropped to 350 × 400 pixels using Microsoft Office Picture Manager.

WSxM software 33 was used to analyze the cropped pictures; all boundaries, sizes, frames, and measured parameters were represented in pixels.

Consequently, system calibration was carried out to translate the pixels into exact real-world units. The process of calibration involved comparing a scale produced by the program with an object of known size, in this case, a ruler.

Subsequently, a three-dimensional representation of the specimens' surface profile was produced. For every specimen, three 3D photos were taken, one in the center and one on each of the sides at a size of 10 µm by 10 µm. The average height (Ra), given in µm, was calculated using WSxM software and is likely an accurate indicator of surface roughness³⁴.

Statistical analysis:

SPSS 16 ® (Statistical Package for Scientific Studies), Graph Pad Prism, and Windows Excel were used to perform the statistical analysis, which was then displayed in four tables and four charts. The Shapiro‒Wilk and Kolmogorov‒Smirnov tests for normality were applied to the provided data, and the results showed that the data were normally distributed. Hence, one-way ANOVA was used to compare data across four distinct groups, and Tukey's post hoc test was used for multiple comparisons.

Hardness:

A comparison between the different groups revealed a significant difference between them (P = 0.0001), as the control group (18.97 ± 0.79) had the lowest hardness, while there was no significant difference between all the other groups, as shown in Table (1) & Figure (1).

Table (1): Comparison of hardness among all groups using one-way ANOVA:

Hardness	Maximum	Minimum	Mean	Standard Deviation	P value One Way ANOVA test
Control group	18.12	20.01	18.97 ^a	0.79	0.0001*
Gr_A1	58.16	56.78	57.33 ^b	0.53
Gr_B1	57.90	56.30	57.20 ^b	0.71
Gr_C1	58.27	56.53	57.90 ^b	0.68
Gr_D1	58.32	56.98	57.31 ^b	0.74

Ns: nonsignificant difference at P > 0.05.

Means with different superscript letters are significantly different at P < 0.05

Means with the same superscript letters are not significantly different at P > 0.05

Roughness:

A comparison between the different groups revealed a significant difference between them (P = 0.001), as the control group (0.09 ± 0.03) demonstrated the lowest roughness, followed by Gr_A1 (0.19 ± 0.07), Gr_B1 (0.23 ± 0.03) and Gr_D1 (0.24 ± 0.02), with no significant difference between them, while Gr_C1 (0.26 ± 0.03) demonstrated the highest roughness, with a non-significant difference from that of Gr_D1 as shown in table (2) & figure (2).

Table (2): Descriptive results of roughness and comparisons among all groups using one-way ANOVA:

Ra (µm)	Maximum	Minimum	Mean	Standard Deviation	P value One Way ANOVA test
Control	0.05	0.12	0.09 a	0.03	0.0001*
Gr_A1	0.23	0.05	0.19 b	0.07
Gr_B1	0.29	0.19	0.23 b	0.03
Gr_C1	0.29	0.22	0.26 c	0.03
Gr_D1	0.27	0.21	0.24 bc	0.02

*Significant difference at P ≤ 0.05.

Means with different superscript letters are significantly different at P < 0.05

Means with the same superscript letters are not significantly different at P > 0.05

Depth of penetration:

A comparison between different groups revealed a significant difference between them (P < 0.0001), as Group A0 (37.03 ± 5.00) and Group C0 (41.0 ± 5.04) demonstrated the greatest depth of penetration, with no significant difference between them, while Group B0 (24 ± 4.76) and Group D0 (26 ± 4.92) demonstrated the lowest depth of penetration, with no significant difference between them, as shown in Table (3) & Figure (3).

Table (3): Descriptive results of penetration depth and comparisons among all groups using one-way ANOVA:

Depth of penetration	Maximum	Minimum	Mean	Standard Deviation	P value One Way ANOVA test
Group A0	44.90	31.99	37.03 ^a	5.00	< 0.0001*
Group B0	31.14	19.81	24.00 ^b	4.76
Group C0	48.99	35.45	41.20 ^a	5.04
Group D0	33.60	21.52	26.01 ^b	4.92

*Significant difference at P ≤ 0.05

Means with different superscript letters are significantly different at P < 0.05

Means with the same superscript letters are not significantly different at P > 0.05

Through complete adhesive impregnation of the dentin substrates, long lasting bonds are achieved in dental restorative procedures. The development of a homogenous hybrid layer is what maintains the stability of the bonded interface³⁵. When a tooth is prepared with a dental bur, it forms a smear layer of debris in the dentin. This layer can then be treated or removed using an adhesive system, resulting in a hybrid layer made of collagen fibers, resin bonds, a dentin surface structure, and an intertubular structure. An adhesive layer develops over the hybrid layer, and resin tags are inserted into the tubules underneath the hybrid layer³⁶.

A new hybrid material combining gold nanoparticles and polymers was created using photo-induced gold reduction along with current dental bonding agents. These metallic nanoparticles acted as contrast agents, enabling the clear characterization of adhesive and hybrid layers that were previously difficult to distinguish in samples lacking nanoparticles. There is potential to explore additional contrast agents to better identify dental bonding materials beneath layers of restorative materials in the future¹³.

Gold nanoparticles offer versatility because they can be tailored with specific functionalities on their surface. In biomedical research, gold nanoparticles have shown promise in reducing collagen pore size and inhibiting collagenase biodegradation by creating multiple cross-links within the collagen structure. Several studies have demonstrated the effectiveness of crosslinking type I collagen and gold nanoparticles in biomedical applications³⁷. Type I collagen plays a vital role as a primary component and structural foundation in the organic matrix of dentin. Therefore, finding ways to decrease or avoid the breakdown of the network of collagen is crucial for improving the stability of bonds in dental contexts³⁸.

Our study findings indicated that when a (diode, Er,Cr: YSGG) laser beam is applied after the bonding system, as observed in groups A0 and D0, there is increase in the penetration depth. This increase is attributed to the hot stream generated by the laser system during irradiation. The gold nanoparticles absorb some of the laser light, converting it into thermal energy, which is then transferred to the surrounding bonding material due to the photothermal properties of the AuNPs, as noted by Mazen et al³⁹. Furthermore, Franke et al⁴⁰ explained how heat plays a role in enhancing the penetration depth of adhesive systems, consequently improving the bond strength. This localized heat can aid in the transformation of the adhesive, which is consistent with our study's findings.

Additionally, Maenosono et al²⁸ reported that post-bonding laser irradiation increases the penetration depth and bond strength by inducing heat within the adhesive, creating a reinforced substrate that improves the dentin-adhesive bond strength. The absorption of heat by gold nanoparticles, along with the low viscosity of the primer, contributes to enhanced primer penetration depth, thereby augmenting the penetration of the bonding agent⁴⁴.

In contrast, our study showed that when a (diode / Er,Cr: YSGG) laser beam was applied before the bonding agent, the penetration depth and bonding strength decrease. These findings are consistent with previous studies conducted by Ramos, Firat and Gurgan^20,16,43. Furthermore, Souza¹⁷ suggested that the high heat generated by laser caused the solvent of adhesive systems to evaporate prematurely, hindering penetration into dentin tubules. Similarly, Chen⁴⁴and Ramos²⁰ noted that laser systems operating at different power levels could create granular layers on the dentin surface, disrupting the bonding process and resulting in reduced penetration depth.

The hardness, which measures a material's resistance to indentation, is directly linked to its vulnerability to deformation and fracture. Understanding micromechanical properties such as the microhardness of irradiated human teeth is essential for improving clinical approaches for treating tooth fractures and predicting susceptibility to fracture⁴⁵.

The average hardness determined in our study falls within previously reported values³⁵, typically ranging from 50 to 57. Notably, both the diode and Er,Cr:YSGG laser irradiation increased the hardness compared to that of the control group, with the degree of increase depending on the laser's power output. This increase in hardness could be attributed to changes in the mineral content and composition of irradiated dental hard tissues⁴⁶, which is supported by the established correlation between the mechanical properties and the mineral content of the tooth structure. Additionally, the irradiated dentin exhibited heightened hardness, likely due to processes such as melting, charring, and recrystallization, despite some incident energy being dispersed or reflected off the targeted dentinal surface⁴⁷.

Previous research has explored the impact of lasers on surface roughness⁴⁸. However, our research aimed to compare the impact of two types of lasers on surface roughness. The results revealed significant disparities in surface roughness among the tested groups, with notably greater values observed in group C1 than in group A1. In our investigation, the surface roughness of the control group ranged from (0.09 ± 0.03), which differs from findings reported in other studies (e.g., 1.45 ± 0.03). Following Er,Cr:YSGG laser treatment, there was a reduction in surface roughness, consistent with the observations of Hossain et al. (2002), who noted an increase in surface roughness after Er,Cr:YSGG irradiation⁴⁹.

The application of a diode laser led to an increase in surface roughness in group C1 (0.26 ± 0.03). This outcome may be attributed to the accumulation of heat at the surface due to the low absorption of infrared radiation. This thermal effect could result in the formation of microspaces as a consequence of the loss of carbonate, water, and organic matrix from the surface irradiated by laser^50,51.

The energy density of laser is calculated by multiplying the power density by the total duration of laser irradiation⁵². Therefore, increasing the power of diode laser could increase the energy density. Consequently, the heightened energy density could lead to a greater thermal load from diode laser irradiation. This increased energy density might explain the notable increase in surface roughness observed after diode laser irradiation relative to that of the control group.

In our study, we discovered that the Er,Cr:YSGG laser produced less surface roughness than did the diode laser. However, it is important to note that differences in surface roughness between laser systems may differ among various studies due to factors such as laser device properties, energy density, and evaluation techniques⁵³.

Ana et al.⁵⁴ reported that using Er,Cr:YSGG laser on root surfaces led to cleaner canals due to their photo-vaporization property, which effectively breaks down dental tissues ^55,56. Similarly, Mohamed et al.⁵⁷ supported our findings by noting that Er,Cr:YSGG laser caused less roughening than other tested lasers, making them preferable for dental treatment.

Applying a laser beam after adhesive application enhances its penetration into dentinal tubules, especially when gold nanoparticles are present. This not only increases the hardness of the dental structure but also influences surface roughness.

ANOVA: Analysis Of Variance

AuCl₄: gold cation tetracholoride

AuNPs: Gold nano particles

CLSM: confocal laser scanning microscopy

Er,Cr:YSGG laser: Erbium Chromium: Yytrium- Scandium – Gallium- Garnet HAuCl₄·3H₂O: Gold chloride, Tetrachloroauric(III) acid Trihydrate

HV: Vickers Hardness

LED: Light- Emitting Diode

NaOCl: Sodium Hypochlorite

SEM: scanning electron microscopy

SPSS: Statistical Package for Scientific Studies

TEM: transmission electron microscopy

Ethics approval and consent to participate: Approved by the Research Ethical Committee (REC), with approval reference: NILES-EC-CU 23/12/28

Consent for publication: “Not applicable”

Availability of data and materials: Available

Competing interests: "The authors declare that they have no competing interests"

Funding: This research received no external funding.

Authors' contributions: DS carried out the practical work, collected the data and was a major contributor in writing the manuscript. MS performed the statistical analysis, participated in writing, editing, plagiarism, final corrections and submission the manuscript. SN participated in writing the manuscript and made final revision. HS carried out final writing and editing, AM participated in plagiarism step and submission. All authors have read and approved the final manuscript before submission.

Acknowledgements: The authors thank the Special Laboratory of Lasers in national research centre

Christoph T. Dental adhesion with resin composites: a review and clinical tips for best practice. Br Dent J. 2022;232:615–9.
Hardan R, Bourgi N, ,Kharouf D, ,Mancino M, Zarow N, Jakubowicz Y, ,Haikel EC. Bond Strength of Universal Adhesives to Dentin: A Systematic Review and Meta-Analysis.2021; 13(5): 1–34.
De Munck J, Van K, Peumans M, Poitevin A, Lambrechts P, Braem M, Van M. A critical review of the durability of adhesion to tooth tissue: methods and results. J Dent Res. 2005;84(2):118–32.
Betancourt D, Baldion P, Castellanos J. Resin-Dentin Bonding Interface: Mechanisms of Degradation and Strategies for Stabilization of the Hybrid Layer. Int J Biomaterials. 2019;3:1–11.
Shuning Z, Xiao W, Jiawei Y, Hongyan C, Xinquan J. Micromechanical interlocking structure at the filler/resin interface for dental composites: a review. Int J Oral Sci. 2023;15(21):1–13.
Lamia S, Isadora M. Degradation and Failure Phenomena at the Dentin Bonding Interface. Biomedicines. 2023;11(5):1–15.
Sakamoto M, Fujistuka M, Majima T. Light as a construction tool of metal nanoparticles: Synthesis and mechanism. J Photochem Photobiol. 2009;10(1):33–56.
Shobha S, Xavier V, Edward P, Mark T, Kyoung-Tae K, Yong-Kyu Y, Augustine U. Paras N. Subwavelength direct laser patterning of conductive gold nanostructures by simultaneous photopolymerization and photoreduction. ACS Nano. 2011;5(3):1947–57.
Jingfang Z, John R, Rossen S. David B.Functionalized gold nanoparticles: synthesis, structure and colloid stability. J Colloid Interface Sci. 2009;331(2):251–62.
Khadiga A, Ying L, Juan X, Caixia K. Recent progress of gold nanostructures and their applications. Phys Chem Chem Phys. 2023;25:18545–76.
Zhang H, Meyerhoff M. Gold coated magnetic particles for solid phase immunoassays: enhancing immobilized antibody binding efficiency and analytical performance. Anal Chem. 2006;78(2):609–16.
Jingyi C, Danling W, Jiefeng X, Leslie A, Andy S, Addie W, Zhi-Yuan L, Hui Z, Younan X, Xingde L. Immunogold nanocages with tailored optical properties for targeted photothermal destruction of cancer cells. Nano Lett. 2007;7(5):1318–22.
Luciano C, Judith V, Nina Y, Suzanne P. Katarzyna S.Collagen cross-Linking with Au nanoparticles. Biomacromolecules. 2008;9(12):3383–8.
Navyasri K, Krishna R, Vineeth G, Sajjan S. An overview of dentin bonding agents. Int J Dent Mater. 2019;1(2):60–7.
Eshrak S, Afrah S, Gaspare P, Gianluca T, Umberto R, Guido M. Classification review of dental adhesive systems: from the IV generation to the universal type. Ann Stomatol. 2017;8(1):1–17.
Firat E, Gurgan S, Gutknecht N. Microtensile bond strength of an etch-and-rinse adhesive to enamel and dentin after Er:YAG laser pretreatment with different pulse durations. Lasers Med Sci. 2012;27:15–21.
De Souza A, Corona S, Dibb R, Borsatto M, Pécora J. Influence of Er:YAG laser on tensile bondstrength of a self-etching system and a flowable resin in different dentin depths. J Dent. 2004;32:269–75.
Eumans M, Kanumilli P, De Munck J, Van L, Lambrechts P, Van M. Clinical effectiveness of contemporary adhesives: a systematic review of current clinical trials. Dent Mater. 2005;21:864–81.
PanelJorge P. Current perspectives on dental adhesion: (1) Dentin adhesion. Japanese Dent Sci Rev. 2020;56(1):190–207.
Ramos A, Esteves-Oliveira M, Arana-Chavez V, De Paula E. Adhesives bonded to erbium:yttriumaluminum- garnet laser-irradiated dentin: transmission electron microscopy, scanning electron microscopy and tensile bond strength analyses. Lasers Med Sci. 2010;25:181–9.
Naji K, Davide M, Asâd N, Ammar E, Youssef H, Joseph H. Effectiveness of Etching by Three Acids on the Morphological and Chemical Features of Dentin Tissue. J Contemp Dent Pract.2019: 20(8):915–9.
Mağrur K, Nazmiye D. Development of Dentin Bonding Systems from Past to Present. Bezmialem Sci. 2019;7(4):322–30.
Soares A, Bitter K, Lagrange A, Rack A, Shemesh H, Zaslansky P. Gaps at the interface between dentine and self-adhesive resin cement in post-endodontic restorations quantified in 3D by phase contrast-enhanced micro-CT. Int Endod J. 2020;53:392–402.
Ghonaim A, Abdelmohsen M, Elkassas D, Abo-Al- Azz A. The Effect of Deproteinization of Dentin Surface on the Micro-Shear Bond Strength to Dentin. Med J Cario Univ. 2014;82:31–5.
Dayem R. A novel method for removing the collagen network from acid-etched dentin by neodymium: yttriumaluminum-garnet laser. Lasers Med Sci. 2009;24:93–9.
Dayem RN. Assessment of the penetration depth of dental adhesives through deproteinized acid-etched dentin using neodymium: yttrium-aluminum-garnet laser and sodium hypochlorite. Lasers Med Sci. 2010;25:17–24.
Louis H, Rim B, Naji K, Davide M, Maciej Z, Natalia J, Youssef H, Carlos E. Bond Strength of Universal Adhesives to Dentin: A Systematic Review and Meta-Analysis. Polymers. 2021;13:814.
Maenosono R, Bim J, Duarte M, Palma-Dibb R, Wang L, Ishikiriama S. Diode laser irradiation increases microtensile bond strength of dentin. Braz Oral Res. 2015;29:1–5.
De Alexandre R, Sundfeld R, Giannini M, Lovadino J. The influence of temperature of three adhesive systems on bonding to ground enamel. Oper Dent. 2008;33:272–81.
Ordinola-Zapata R, Bramante C, Graeff M, Del Carpio P, Vivan R, Camargo E. Depth and percentage of penetration of endodontic sealers into dentinal tubules after root canal obturation using a lateral compaction technique: A confocal laser scanning microscopy study. Oral Surg Oral Med Oral Pathol Oral Radiol Endod. 2009;108:450–7.
Gharib S, Tordik P, Imamura G, Baginski T, Goodell G. A confocal laser scanning microscope investigation of the epiphany obturation system. J Endod. 2007;33:957–61.
Ossama B. & Abouelatta. 3D Surface Roughness Measurement Using a Light Sectioning Vision System. Proceedings of the World Congress on Engineering. 2010; 1:1–6.
Fernandez HI, Gomez R, Colchero J, Gomez-Herrero J J., and, Baro A. Rev Sci Instrum. 2007;78:013705.
Kakaboura A, Fragouli M, Rahiotis C. Evaluation of surface characteristics of dental composites using profilometry, scanning electron, atomic force microscopy and gloss-meter. J Mater Sci Mater Med. 2007;18:155–63.
Wael M, Joseph E. The effect of Nd:YAG and Er,Cr:YSGG lasers on the microhardness of human dentin. Lasers Med Sci. 2013;28:151–6.
Sara D, Sepehr S, Mehrdad K, Mohammad A. Mechanical Properties of Dental Adhesives Containing Gold Nano Particles. 5th International Congress on Nanoscience & Nanotechnology.2014, 22–24.
Haidekker MA, et al. Influence of gold nanoparticles on collagen fibril morphology quantified using transmission electron microscopy and image analysis. BMC Med Imag. 2006;6(4):1–7.
Ana K, Renato E, Tymish Y, Shoba S, Earl J, Anderson S, Paras N. In situ gold nanoparticles formation: contrast agent for dental optical coherence tomography. J Biomed Opt. 2012;17(6):1–5.
Mazen A, Viktoriia S, Kelly M, Anatoliy P. Absorption cross section of gold nanoparticles based on NIR laser heating and thermodynamic calculations. Scientifc Rep. 2020;10:18790.
Franke M, Taylor A, Lago A, Fredel M. Influence of Nd:YAG laser irradiation on an adhesive restorative procedure. Oper Dent. 2006;31(5):604–9.
Marimoto A, Cunha L, Yui K, Huhtala M, Barcellos C, Prakki A. Influence of Nd:YAG laser on the bond strength of self-etching and conventional adhesive systems to dental hard tissues. Oper Dent. 2013;38(4):447–55.
Resaei-Soufi L, Ghanadan K, Moghimbeigi A. The effects of Er:YAG, Nd:YAG, and Diode (940 nm) Lasers irradiation on Microtensile bond strength of two steps self-etch adhesives. Laser Therapy. 2019;28(2):131–7.
Gurgan S, Kiremitci A, Cakir F, Yazici E, Gorucu J, Gutknecht N. Shear bond strength of composite bonded to erbium: yttrium-aluminum-garnet laser-prepared dentin. Lasers Med Sci. 2009;24(1):117.
Chen M, Ding J, He Y, Chen Y, Jiang Q. Effect of pretreatment on Er:YAG laser-irradiated dentin. Lasers Med Sci 2015 (Feb);30(2):753–9.
Lee B, Lin C, Lin F, Li U, Lan W. Effect of Nd: YAG laser irradiation on the hardness and elastic modulus of human dentin. J Clin Laser Med Surg. 2003;21:41–9.
Ludovic R, Steve M, Julia B, Ksenia M, Laurence J, Heiko S, Omar Z, Alaa H, Timothy R. ,Andrei V. Investigation of laser wavelength effect on the ablation of enamel and dentin using femtosecond laser pulses. Scientifc Rep. 2023;13:1–13.
Alyaa J, Saher S. Effect of Er, Cr:YSGG and Diode lasers on surface roughness of enamel around composite restoration: an in vitro study. Int J Dent Med Sci Res. 2021;3(5):1237–43.
Sugsompian K, Tansalarak R, Piyapattamin T. Comparison of the Enamel Surface Roughness from Different Polishing Methods: Scanning Electron Microscopy and Atomic Force Microscopy Investigation. Eur J Dent. 2020;14(2):1–12.
Hossain M, Yukio N, Yoshishige Y, Nobuyuki S. Analysis of Surface Roughness of Enamel and Dentin after Er,Cr:YSGG Laser Irradiation. J Clin Laser Med Surg. 2002;19(6):297–303.
Alaa H, Abduladheem R. The Effect of Diode Laser Irradiation on Surface Roughness of Bleached Enamel: An in Vitro Study. Al– Rafidain Dent J. 2021;21(2):202–14.
Moharam L, Sadony D, Nagi S. Evaluation of diode laser application on chemical analysis and surface microhardness of white spots enamel lesions with two remineralizing agents. J Clin Exp Dent. 2020;12(3):271–6.
Khouja F, Abdelaziz M, Bortolotto T, Krejci I. Intra-pulpal and subsurface temperature rise during tooth irradiation with 808 nm diode laser: an in vitro study. Eur J Paediatr Dent. 2017;18(1):56–60.
Zohre S, Maryam P, Sima S. Relationship between Er,Cr:YSGG laser power and surface roughness of lased radicular dentin. J Dent Res Dent Clin Dent Prospects. 2018;12(2):83–90.
Ana C, Paulo M, João C, Teresa O, Norbert G. Adhesion in Dentin Prepared with Er,Cr:YSGG Laser: Systematic Review. Contemp Clin Dent. 2019;10(1):129–34.
Recai Z, Hüseyin S, İhsan H, Demet A, Arzu Ş. The Roughening Effects of Er:YAG, Nd:YAG, and KTP Laser Systems on Root Dentin Surface. Cumhuriyet Dent J. 2023;26(1):63–8.
Sarah I, Abduladheem R. The efficiency of ErCr:YSGG laser on the debonding of different thicknesses of ceramic veneers. Braz J Oral Sci. 2022;21:1–12.
Mohamed T, Ihab M, Hanaa ZEFFECTOF, Er,Cr, :YSGG LASER VERSUS ACID ETCHING SURFACE TREATMENT ON THE SURFACE ROUGHNESS AND TOPOGRAPHY OF TWO PRESSABLE LITHIUM DISILICATE CERAMICS IN-VITRO STUDY. E D J. 2021;67:1571–81.

No competing interests reported.

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Effect of combining Gold Nanoparticles with Diode or Er. Cr:YSGG Laser on the Bond Strength of Etch- and- Rinse Adhesive to Dentin Surface

Status:

Version 1

Abstract

Background

Methods

Results

Conclusions

Figures

Introduction

Materials and Methods

Test procedure:

1. Microhardness calculation:

2. Roughness methodology:

Statistical analysis:

Results

Hardness:

Means with different superscript letters are significantly different at P < 0.05

Means with the same superscript letters are not significantly different at P > 0.05

Roughness:

Means with different superscript letters are significantly different at P < 0.05

Means with the same superscript letters are not significantly different at P > 0.05

Depth of penetration:

Discussion

Conclusions

Abbreviations

Declarations

References

Additional Declarations

Status:

Version 1