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Biomaterials Research

, 22:35 | Cite as

Calcium release and physical properties of modified carbonate apatite cement as pulp capping agent in dental application

  • Myrna Nurlatifah Zakaria
  • Arief Cahyanto
  • Ahmed El-Ghannam
Open Access
Research article
  • 110 Downloads

Abstract

Background

Carbonate apatite (CO3Ap) and silica-calcium phosphate composite (SCPC) are bone substitutes with good prospect for dental application. SCPC creates a hydroxyapatite surface layer and stimulate bone cell function while, CO3Ap induce apatite crystal formation with good adaptation providing good seal between cement and the bone. Together, these materials will add favorable properties as a pulp capping material to stimulate mineral barrier and maintain pulp vitality. The aim of this study is to investigate modification of CO3Ap cement combined with SCPC, later term as CO3Ap-SCPC cement (CAS) in means of its chemical (Calcium release) and physical properties (setting time, DTS and pH value).

Methods

The study consist of three groups; group 1 (100% calcium hydroxide, group 2 CO3Ap (60% DCPA: 40% vaterite, and group 3 CAS (60% DCPA: 20% vaterite: 20% SCPC. Distilled water was employed as a solution for group 1, and 0.2 mol/L Na3PO4 used for group 2 and group 3.

Samples were evaluated with respect to important properties for pulp capping application such as pH, setting time, mechanical strength and calcium release evaluation.

Results

The fastest setting time was in CO3Ap cement group without SCPC, while the addition of 20% SCPC slightly increase the pH value but did not improved the cement mechanical strength, however, the mechanical strength of both CO3Ap groups were significantly higher than calcium hydroxide. All three groups released calcium ions and had alkaline pH. Highest pH level, as well as calcium released level, was in the control group.

Conclusion

The CAS cement had good mechanical and acceptable chemical properties for pulp capping application compared to calcium hydroxide as a gold standard. However, improvements and in vivo studies are to be carried out with the further development of this material.

Keywords

Carbonate apatite Silica-calcium phosphate composite CO3Ap-SCPC cement Pulp capping 

Background

Silica-calcium phosphate composite (SCPC) and carbonate apatite (CO3Ap) are bioceramics material that has been intensively studied for bone repair [1, 2, 3, 4, 5, 6, 7, 8]. CO3Ap is a full transformed cement with high solubility to be replaced by new bone formation, oscteoclastic bone resorption followed by new bone formation was observed in implanted CO3Ap granules in bone defect [1, 9]. Fabrication of carbonate apatite cement from vaterite and dicalcium phosphate anhydrous (DCPA; CaHPO4) powder mixed with various sodium phosphate solutions: NaH2PO4, Na2HPO4, and Na3PO4 showed that transformation rate of cement to form CO3Ap was affected by the solutions pH. Therefore, 0.2 mol/L Na3PO4 solution with pH 12.3for fastest CO3Ap transformation rate compared to the others was used in this present study [2]. One of the advantages of CO3Ap cement is that it can set in the physiological condition through a dissolution-precipitation reaction. After mixing with Na3PO4 solution, the vaterite and DCPA dissolved to supply Ca2+, PO43−, and CO32− ions, which play important role in mineralized tissue regeneration as well as in dentinogenesis [10, 11].

SCPC withdrew Ca2+ ions from it surrounding to its surface which provides Ca2+ ions for osteoblast activity, by facilitating osteoblast to differentiate to mature bone-forming cells [7, 12]. SCPC has been implanted to alveolar bone socket after tooth extraction and after 6 months a bone core was taken for histological evaluation followed by an implant placement. Histomorphometric analysis showed good regeneration of new vital bone and radiographic assessment immediately after extraction compared to 6 months after extraction and grafted by SCPC granules showed a minimum changed in alveolar ridge dimensions [6]. An in vitro study demonstrated that SCPC exhibited a controlled release of silicon and phosphate ions in cell culture media delivering a natural stimulus for bone-cell differentiation [13, 14].

The pulp is a loose connective tissue in the central of a tooth, with various cells including fibroblast, odontoblast, immune cells, undifferentiated mesenchymal cells, sensory nerves and blood vessels [15]. It plays a pivotal part in maintaining the vitality of the tooth for regenerative, sensory, and nutritive function. If an injury to the enamel or dentin occurs, the pulp will protect itself by pumping immune cells to injured area, as well as stimulating the odontoblast to form a reparative or reactive dentin in order to block the irritants, preventing harm to reach to the pulp and maintain a vital and healthy pulp with no irreversible pulp inflammation [15, 16, 17, 18]. However, the pulp can be injured due to enamel and dentin fracture, or progressive dental caries resulting pulp exposure, causing irreversible inflammation and eventually causing pulp necrosis. This will act as a port of entry for bacteria to colonize the pulp space inducing periapical lesion (periapical abscess, cyst, granuloma), therefore in these kind of situation, root canal treatment will be the only treatment choice besides tooth extraction [16, 17].

Treatment choice for exposed dental pulp to save its vitality is called pulp capping. Pulp capping is a treatment by placing a biocompatible material on the exposed pulp to stimulate the formation of mineralized dentinal bridge or reparative dentin prior the definite restoration. The gold standard material for this purpose is calcium hydroxide [Ca(OH)2] which has been used from the early 1920s, for its biocompatibility and ability to stimulate hard tissue formation as well as antibacterial effect [17]. The liberation of hydroxyl and calcium ions is believed to be the basic mechanism for its high pH contributing to antibacterial effect and activation of alkaline phosphates (ALP) involved in hard tissue formation [16, 17, 18, 19, 20]. Some drawbacks concerning this compound including its high solubility, degradation of material over time, weak dentinal barrier formation, poor adhesion property to tooth structure, and long uncontrolled chronic inflammation to the pulp [19, 21, 22, 23, 24].

The tooth and bone, are principally similar in their structure, in which they are mainly composed of hydroxyapatite [Ca10(PO4)6(OH)2] crystal, carbonate-substituted as the major part of their inorganic constituent. Pondering the same major component of dentin and bone, we proposed the used of CO3Ap and SCPC as novel pulp capping materials that are biocompatible, bioactive and able to set in the physiological environment to induced mineralization over the expose pulp and maintain the pulp vitality. Our previous study has already evaluated the different ratio of CO3Ap and SCPC for the best formula for this purpose [22]. The present study is a sequel of previous one, to evaluate the physical properties (pH, setting time, DTS) and Ca2+ ions release of the new CO3Ap-SCPC cement as new pulp capping material.

Methods

Preparation of CO3Ap and SCPC powders

The CO3Ap powder composed in this study consists of DCPA (J.T. Baker Chemical Co., NJ, USA) and vaterite. The DCPA powder was grinded to reduce the particle size to 0.4 μm using a planetary ball mill (Fritsch 8 6560, Idar-Oberstein, Germany) with 95% ethanol for 1 h and drying for 3 h. The vaterite powder was prepared according to the previous report [25]. In brief, 50 g of Ca(OH)2 was put into 500 mL of methanol and 25 mL of distilled water. The CO2 gas was blown at a rate of 1 L/min for 120 min into the suspension and the temperature was set at 20 °C. The obtained particles were collected and dried at 110 °C. The average particle size of vaterite powder was approximately 0.7 μm. The SCPC used to modified the CO3Ap consists of 19.49% SiO2, 20.34% P2O5, 40.68% CaO and 19.49% Na2O (in mol %) as it demonstrated favorable physiochemical and bioactivity properties of Si-rich SCPC [13]. The powder metallurgy technique was employed to prepare the SCPC powders. The powders were mixed in polyethylene bottles over a roller for 24 h, then calcinated at 800 °C (Thermolyne 30,400, Barnstead International, Dubuque, IA) for 1 h, and then ground to the size average of 90–150 μm.

Preparation of Ca(OH)2 powder

In this study, a commercial Ca(OH)2 powder (Merck, Darmstadt, Germany) was employed as a control. Sample manipulation was done as the manufacturer instruction.

Preparation of the samples

The powder cement ratio divided into 3 groups: group 1 (100% Ca(OH)2) as a control, group 2 (60% DCPA: 40% vaterite), and group 3 (60% DCPA: 20% vaterite: 20% SCPC). Distilled water was used as solution for group 1, and 0.2 mol/L Na3PO4 used for group 2 and group 3.

Setting time

All group samples were prepared at liquid-to-powder (L/P) ratios of 0.5. Setting time of all samples were measured according to the method set in ISO 1566 for dental zinc phosphate cement. In this method, a cement is considered to set when a 400 g weight loaded onto a Vicat needle with a tip diameter of 1.0 mm fails to make a perceptible circular indentation on the surface of the cement. The standard requires the cement to be maintained at a temperature of 37 °C and 100% relative humidity to simulate the clinical condition. In the present study, the specimen was placed on Teflon mold for setting time measurement. Mean setting time (n = 5) was obtained, and the standard deviation was used as an evaluation of standard uncertainty.

pH measurement

pH was observed using pH meter (pH -207, Lutron Co., Taipei, Taiwan). Before measurement, pH meter was calibrated by a buffer solution of pH 4 and 7. After calibrated, pH solution was measured by putting the electrode inside the tube with a sample and deionized water for 0.5, 1, 24, 72 and 168 h.

Calcium released

The calcium released was examined using spectrophotometer UV/VIS (Spectronic Camspec Ltd., Leeds, UK). The set cement sample was put into a tube filled with 10 mL of deionized water at 37 °C. The stored water was measured for Ca2+ ions analysis for 0.5, 1, 24, 72 and 168 h.

The formula to measure calcium released was below:
$$ Calcium\ \left(\frac{mmol}{L}\right)=\frac{\mathrm{Abs}.\mathrm{Test}}{\mathrm{Abs}.\mathrm{Std}}x\ Standard $$

Mechanical strength measurement

The mechanical strength of the samples was examined in terms of diametral tensile strength (DTS). Each group was mixed with the different aqueous solution, at liquid to powder ratio of 0.5 and set at 37 °C and 100% of relative humidity for 72 h. The paste was put into a Teflon mold (6 mm in diameter × 3 mm in height), both ends of the mold were covered with glass slides then clamped. The molds were placed inside a plastic container with distilled water to maintain 100% relative humidity. The plastic container was placed into an incubator and kept at 37 °C for 72 h. The samples were removed from the mold after completion of treatment times and immersed in the 99% ethanol for 3 min then dried at 80 °C for 3 h. Then, the samples were crushed using a universal testing machine (LRX Plus; Llyod Instruments, Ltd., West Sussex, UK) with 5.6 kN of preload stress at a crosshead speed of 1 mm/min. DTS values were taken as the average of at least 5 samples.

Results

Table 1 summarizes the setting time comparison between Ca(OH)2, CO3Ap and CAS. The Ca(OH)2 was mixed with distilled water as a control, CO3Ap and CAS was mixed with 0.2 mol/L Na3PO4, respectively. The setting time of each group were statistically different where the CO3Ap group had the fastest setting time (13.08 ± 0.05 min) followed by CAS and Ca(OH)2.
Table 1

Comparison of calcium hydroxide, carbonate apatite and carbonate apatite-SCPC on setting time evaluation (n = 5)

Liquid

Powder

Setting time (minutes)

L/P 0.5

Distilled water

Calcium hydroxide

38.05 ± 0.12

Na3PO4

Carbonate apatite*

13.08 ± 0.05

Carbonate apatite-SCPC**

26.93 ± 0.21

n = 5; */** p < 0.05

The mean pH value and standard deviations recorded for three different material group at the various period of time are plotted in Fig. 1. In this study, calibration of pH was conducted using buffer solution before pH measurement and were similar as buffer control. The Ca(OH)2 revealed higher pH values than other samples at all period of time evaluation (p < 0.05). The pH values of CO3Ap and CAS were similar to each other and the pH values in these both groups gradually decreased until near neutral at 168 h.
Fig. 1

pH values for three different materials in various period of time. At least 5 samples were measured for pH. Errors bars indicate the standard deviation

Figure 2 presents the mean Ca2+ ions released and standard deviations provided by three different materials as a function of time. The Ca(OH)2 released 0.81 mmol/L Ca2+ ions in the first 0.5 h and increased significantly to 125.20 mmol/L at 168 h. The Ca2+ ions released for CO3Ap group showed stable results in all the period of time. While, CAS had higher Ca2+ ions released in the first 0.5 h (1.84 mmol/L). However, the Ca2+ ions released on CAS group gradually decreased until 0.01 mmol/L at 24 h.
Fig. 2

The concentration of Calcium released from the set of three different materials. At least 5 samples were measured for calcium released. Errors bars indicate the standard deviation

Figure 3 shows the mean of DTS values of three different materials after setting at 37 °C, 100% relative humidity for 72 h. The mean DTS values of CO3Ap (4.16 ± 1.36 MPa) and CAS (3.92 ± 1.07 MPa) were statistically higher than Ca(OH)2 (0.21 ± 0.47 MPa). However, there was no statistical significance on DTS values between CO3Ap and CAS.
Fig. 3

Diametral tensile strength values of the set three different materials after 72 h. At least 5 samples were measured for DTS evaluation. Errors bars indicate the standard deviation

Discussion

The setting of the CO3Ap cement lies on dissolution-precipitation reaction. After mixing with 0.2 mol/L Na3PO4 solution, the powder will dissolve and supply Ca2+, PO43− and CO32− ions. As the solution gets supersaturated, precipitation occurs and forms CO3Ap crystals and the cement will set [1, 9, 10]. As shown in Table 1 the setting time for CO3Ap cement without the addition of SCPC is significantly higher than CO3Ap and Ca(OH)2 cement. The CO3Ap cement consists of higher percentage of vaterite that has high solubility thus enabling precipitation of CO3Ap in a shorter time. This was also one of the reasons for employing vaterite instead of calcite in this study. On the other hand, SCPC added in group 3 were in the form of granules that do not dissolve in short time, they do release Ca, P, Na, and Si ions but they do not have the ability to set.8 This was also the reason why we combine the SCPC with CO3Ap instead of using pure SCPC for pulp capping purpose.

To achieve a favourable cement to be applied as pulp capping agent, adequate setting time and the ability to set in a moist environment with the presence of blood or blood clot will give the best result, because the material will hold place without being washed out. This is one of Ca(OH)2 drawback, because it is easy to get dissolved and have a poor adhesive ability to tooth structure. An ideal pulp capping material should have the ability to adapt and adhere to the tooth structure, providing tight seal to prevent microleakage and bacterial penetration [17, 26].

The longest setting time for Ca(OH)2 relates on the high solubility and could also relate to its larger particle size (37 μm), compared to DCPA (0.3–0.5 μm) and vaterite (0.6–0.9 μm). The Ca(OH)2 setting mechanism is based on acid–base reaction between Ca(OH)2 and 1-methyl trimethylene disalicylate, forming an amorphous calcium-disalicylate salt, with Ca2+ ions intercalated with disalicylate molecules. For faster setting time, commercially Ca(OH)2 products added accelerator in the form base and catalyst paste, enabling more predictable and faster setting time, however, this approach did not solve the adhesive problem. Meanwhile, the addition of SCPC to CO3Ap cement slightly decreased the mechanical strength with no significant difference. In line with our previous study, the addition of 10 and 20% of SCPC did not gave significant difference and had better mechanical strength compared to 10 and 40% addition of SCPC. The bioactive silicate functional groups of SCPC appeared to bind the CO3Ap components in the CAS cement and formed a more compact and dense structure as seen in the SEM analyses [22].

The pH evaluation showed a trend of pH value that slowly decreases over time in both CO3Ap cement group with or without SCPC, whereas Ca(OH)2 have a relatively stable pH level until 168 h observation. This showed that, after precipitation and the formation of the CO3Ap crystal, pH decreases, though did slightly elevate at 168 h evaluation and tend to be at neutral level. However, the addition of SCPC to CO3Ap cement did not gave any significant effect on the pH level. This is completely different compared to the Ca(OH)2 group that still have relatively high pH level (above 11) for all evaluation time. The relatively high pH for Ca(OH)2 group are closely related to the dissolution of Ca2+ and OH ions after the powder was manipulated with distilled water. Alkaline pH of the dental material is strongly associated with its antimicrobial effect because the alkaline environment will interfere bacterial proliferation [17, 26, 27, 28]. Alkaline pH also contribute to the increase expression of bone morphogenetic protein-2 (BMP-2), alkaline phosphatase (ALP), and promotes the formation of calcified nodules favoring the tissue environment to stimulate the healing process [18, 25, 27].

Ca2+ ions also play an important role in the formation of the dentinal bridge. Ca2+ ions stimulate the recruitment and proliferation of undifferentiated cells from the pulp and activate stem cells and odontoblast to form reparative dentin or dentinal bridge to protect an exposed pulp [27, 29]. Moreover, it enhances pyrophosphatase activity, sustaining dentin mineralization and dentinal bridge formation [30]. The bioactivity of a material is affected by the nature structure and surface of the material responsible for water sorption, material solubility and its permeability water diffusion (i.e., porosity) [27]. As expected, the significant difference was observed between the CO3Ap and CAS cement to Ca(OH)2 cement that rapidly dissolves. The high solubility of Ca(OH)2 make less effective for application in the presence of blood which typically occurs in exposed pulp, especially in heavily inflamed ones. In general, slow release bioactivity is beneficial to have a balance between material resorption to regeneration, this would probably be hard to achieve in Ca(OH)2 and could be the reason for its weak and tunnel defects on their dentinal bridge formation. However, over stabilization can also result in pointless ionic dissolution.

Conclusion

Based on our findings of acceptable setting time, alkaline pH and calcium release, together with previous study on its ability to form reparative dentin in animal study, the novel CAS cement can be considered as a good candidate for pulp capping treatment. Nevertheless, further evaluation on improving the properties still awaits.

Notes

Acknowledgments

The authors grateful of the services and facilities of the Integrated Laboratory of Faculty of Dentistry, Universitas Padjadjaran, Indonesia, and in collaborative research with the University of North Carolina at Charlotte, USA.

Funding

This study was supported by the research grant from LPPM and Faculty of Medicine, Program Study of Dentistry, Universitas Jenderal Achmad Yani, Indonesia No. 225/UNJANI/XI/2015.

Availability of data and materials

Not applicable.

Authors’ contributions

MNZ performed the setting time, pH, calcium released and was a major contributor in writing the manuscript, AC performed the diametral tensile strength evaluation and analyzed all the results data. AE has synthesized the SCPC powder which used in this study. All authors read and approved the final manuscript.

Ethics approval and consent to participate

Not applicable.

Consent for publication

Not applicable.

Competing interests

The authors declare that they have no competing interests.

Publisher’s Note

Springer Nature remains neutral with regard to jurisdictional claims in published maps and institutional affiliations.

References

  1. 1.
    Ishikawa K. Bone substitute fabrication based on dissolution-precipitation reactions. Materials. 2010;3:1138–55.CrossRefGoogle Scholar
  2. 2.
    Cahyanto A, Maruta M, Tsuru K, Matsuya S, Ishikawa K. Fabrication of bone cement that fully transform to carbonate apatite. Dent Mat J. 2015;34(3):394–401.CrossRefGoogle Scholar
  3. 3.
    Cahyanto A, Tsuru K, Ishikawa K. Carbonate apatite formation during the setting reaction of apatite cement. Advances in bioceramics and porous ceramics V. Ceram Eng Sci Proc. 2013;33(6):7–10.Google Scholar
  4. 4.
    Cahyanto A, Tsuru K, Ishikawa K. Transformation of apatite cement to B-type carbonate apatite using different atmosphere. Key Eng Mater. 2016;696:9–13.CrossRefGoogle Scholar
  5. 5.
    Cahyanto A, Toita R, Tsuru K, Ishikawa K. Effect of particle size on carbonate apatite cement properties consisting of calcite (or vaterite) and dicalcium phosphate anhydrous. Key Eng Mater. 2014;631:128–33.CrossRefGoogle Scholar
  6. 6.
    Al-Sabbagh M, Burt J, Barakat A, Kutkut A, El-Ghannam A. Alveolar ridge preservation using resorbable bioactive ceramic composite: a histological study. J Int Acad Perio. 2013;15(3):91–8.Google Scholar
  7. 7.
    Aniket YA, Marriott I, El-Ghannam A. Promotion of pro-osteogenic responses by a bioactive ceramic coating. J Biomed Mater Res A. 2012;100A:3314–25.CrossRefGoogle Scholar
  8. 8.
    El-Ghannam A, Hart A, White D, Cunningham L. Mechanical properties and cytotoxicity of a resorbable bioactive implant prepared by rapid prototyping technique. J Biomed Mater Res Part A. 2013;101A:2851–61.CrossRefGoogle Scholar
  9. 9.
    Ishikawa K, Matsuya S. Bioceramics. In: Milne I, Ritchie RO, Karihaloo B, editors. Comprehensive structural integrity, vol. 9. Oxford: Elsevier; 2003. p. 169–214.CrossRefGoogle Scholar
  10. 10.
    Cahyanto A, Maruta M, Tsuru K, Matsuya S, Ishikawa K. Basic properties of carbonate apatite cement consisting of vaterite and dicalcium phosphate anhydrous. Key Eng Mater. 2013;529-530:192–6.CrossRefGoogle Scholar
  11. 11.
    Leewenburgh S, Layrolle P, Barrère F, de Bruijn J, Schoonman J, van Blitterswijk CA, de Groot K. Osteoclastic resorption of biomimetic calcium phosphate coatings in vitro. J Biomed Mater Res. 2001;56:208–15.CrossRefGoogle Scholar
  12. 12.
    Maeno S, Niki Y, Matsumoto H, Morioka H, Yatabe T, Funayama A, Toyama Y, Taguchi T, Tanaka J. The effect of calcium ion con- centration on osteoblast viability, proliferation and differentiation in monolayer and 3D culture. Biomaterials. 2005;26:4847–55.CrossRefGoogle Scholar
  13. 13.
    Gupta G, Kirakodu S, El-Ghannam A. Effect of exogenous phosphorus and silicon on osteoblast differentiation at the interface with bioactive ceramics. J Biomed Mater Res A. 2010;95A:882–90.CrossRefGoogle Scholar
  14. 14.
    Gupta G, El-Ghannam A, Kirakodu S, Khraisheh M, Zbib H. Enhancement of osteoblast gene expression by mechanically compatible porous Si-rich nanocomposite. J Biomed Mater Res B Appl Biomater. 2007;81:387–96.CrossRefGoogle Scholar
  15. 15.
    Boskey AL, Roy R. Cell culture systems for studies of bone and tooth mineralization. Chem Rev. 2008;108(11):4716–33.CrossRefGoogle Scholar
  16. 16.
    Fouad AF, Levin L. Pulpal Reactions to Caries and Dental Procedures. In: Hargreaves KM, Cohen S, editors. Cohen’s Pathways of The Pulp. 11th ed. Missouri: Mosby Elsevier; 2015. p. 504.Google Scholar
  17. 17.
    Hilton TJ. Key to success with pulp capping: a review of the literature. Oper Dent. 2009;34(5):615–25.CrossRefGoogle Scholar
  18. 18.
    Dhillon H, Kaushik M, Sharma R. Regenerative endodontics—creating new horizons. J Biomed Mater Res Part B. 2016;104B:676–85.CrossRefGoogle Scholar
  19. 19.
    Cox CF, Subay RK, Ostro E, Suzuki SH. Tunnel defects in dentin bridges their formation following direct pulp capping. Oper Dent. 1996;21:4–11.Google Scholar
  20. 20.
    Gandolfi MG, Siboni F, Botero T, Bossu M, Riccitiello F, Prati C. Calcium silicate and calcium hydroxide materials for pulp capping: biointeractivity, porosity, solubility and bioactivity of current formulations. J Appl Biomater Funct Mater. 2015;13(1):43–60.Google Scholar
  21. 21.
    Parolia A, Kundabala M, Rao NN, Acharya SR, Agrawal P, Mohan M, Thomas M. A comparative histological analysis of human pulp following direct pulp capping with Propolis, mineral trioxide aggregate and Dycal. Aust Dent J. 2010;55:59–64.CrossRefGoogle Scholar
  22. 22.
    Zakaria MN, Cahyanto A, El-Ghannam A. Basic properties of novel bioactive cement based on silica-calcium phosphate composite and carbonate apatite. Key Eng Mater. 2017;720:147–52.CrossRefGoogle Scholar
  23. 23.
    Zakaria MN, Pauziah NFN, Sabirin IP, Cahyanto A. Evaluation of carbonate apatite in inducing formation of reparative dentin in exposed dental pulp. Key Eng Mater. 2017;758:250–4.CrossRefGoogle Scholar
  24. 24.
    Cahyanto A, Rezano A, Zakaria MN, El-Ghannam A. Synthesis and characterization of a novel SCPC-CO3AP cement for pulp capping application in dentistry. Key Eng Mater. 2017;758:29–33.CrossRefGoogle Scholar
  25. 25.
    Maeda H, Maquet V, Chen QZ, Kasuga T, Jawad H, Boccaccini AR. Bioactive coatings by vaterite deposition on polymer substrates of different composition and morphology. Mat Sci Eng C. 2007;27:741–5.CrossRefGoogle Scholar
  26. 26.
    Zakaria MN. Save the pulp is the essential issues on pulp capping treatment. J Dentomaxillofac Sci. 2016;1(2):301–5.Google Scholar
  27. 27.
    Poggio C, Lombardini M, Colombo M, Beltrami R, Rindi S. Solubility and pH of direct pulp capping materials: a comparative study. J Appl Biomater Funct Mater. 2015;13(2):181–5.Google Scholar
  28. 28.
    Liu L, Pushalkar S, Saxena D, LeGeros RZ, Zhang Y. Antibacterial property expressed by a novel calcium phosphate glass. J Biomed Mater Res B Appl Biomater. 2014;102(3):423–9.CrossRefGoogle Scholar
  29. 29.
    Goldberg M, Smith AJ. Cells and extracellular matrices of dentin and pulp: a biological basis for repair and tissue engineering. Crit Rev Oral Biol Med. 2004;15(1):13–27.CrossRefGoogle Scholar
  30. 30.
    Estrela C, Holland R. Calcium hydroxide: study based on scientific evidences. J Appl Oral Sci. 2003;11(4):269–82.CrossRefGoogle Scholar

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Open AccessThis article is distributed under the terms of the Creative Commons Attribution 4.0 International License (http://creativecommons.org/licenses/by/4.0/), which permits unrestricted use, distribution, and reproduction in any medium, provided you give appropriate credit to the original author(s) and the source, provide a link to the Creative Commons license, and indicate if changes were made. The Creative Commons Public Domain Dedication waiver (http://creativecommons.org/publicdomain/zero/1.0/) applies to the data made available in this article, unless otherwise stated.

Authors and Affiliations

  1. 1.Department of Endodontology and Operative Dentistry, Program Study of Dentistry, Faculty of MedicineUniversitas Jenderal Achmad YaniCimahiIndonesia
  2. 2.Department of Dental Materials Science and Technology, Faculty of DentistryUniversitas PadjadjaranSumedang-JatinangorIndonesia
  3. 3.Department of Mechanical Engineering and Engineering ScienceThe University of North Carolina at CharlotteCharlotteUSA

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