Apatite-forming ability (bioactivity) of ProRoot MTA
Transcript of Apatite-forming ability (bioactivity) of ProRoot MTA
Apatite-forming ability (bioactivity) of ProRoot MTA
M. G. Gandolfi1, P. Taddei2, A. Tinti2 & C. Prati1
1Laboratory of Biomaterials and Oral Pathology, Endodontic Clinical Section, Department of Odontostomatological Science,
University of Bologna; and 2Department of Biochemistry, University of Bologna, Bologna, Italy
Abstract
Gandolfi MG, Taddei P, Tinti A, Prati C. Apatite-forming
ability (bioactivity) of ProRoot MTA. International Endodontic
Journal, 43, 917–929, 2010.
Aim Apatite-forming ability, considered as an index of
bioactivity (bond-to-bone ability), was tested on Pro-
Root MTA cement after immersion in phosphate-
containing solution (DPBS).
Methodology Disk samples were prepared and
immersed in DPBS for 10 min, 5 h, 1 and 7 days.
The cement surface was studied by attenuated total
reflectance Fourier transform infrared (ATR-FTIR)
spectroscopy, by micro-Raman spectroscopy and by
environmental scanning electron microscope with
energy dispersive X-ray (ESEM-EDX) analyses. The pH
of the storage solution was also investigated.
Results Spectroscopic analyses revealed calcium
phosphate bands after 5-h immersion in DPBS. After
1 day, an even coating composed of apatite spherulites
(0.1–0.8 micron diameter) was observed by ESEM/EDX.
After 7 days, its thickness had increased. Apatite
nucleation had already occurred after 5-h immersion.
At this time, the presence of portlandite (i.e. Ca(OH)2,
calcium hydroxide) on the cement surface was also
observed; at longer times, this component was released
into the medium, which underwent a remarkable pH
increase.
Conclusions The study confirms the ability of
ProRoot MTA to form a superficial layer of apatite
within hours. The excellent bioactivity of ProRoot MTA
might provide a significant clinical advantage over the
traditional cements used for root-end or root-perfora-
tion repair.
Keywords: apatite-forming ability, bioactivity,
calcium carbonate (calcite), calcium hydroxide (port-
landite), calcium-silicate cements, carbonate apatite,
dicalcium silicate (belite), Portland cement, ProRoot
MTA, tricalcium silicate (alite).
Received 14 December 2009; accepted 1 May 2010
Introduction
A material can be considered bioactive if it evokes a
positive response from the host (BSI 2007), and a
bioactive material must be able to elicit a biological
response at the interface and induce the formation of a
bond between tissue and the material (Hench & West
1996).
The concept of bioactivity is closely correlated with
biointeractivity, i.e. the ability to exchange information
within a biological system (BSI 2007). This means that
a bioactive material reacts chemically with body fluids
in a manner compatible with the repair processes of the
tissue.
An artificial material can bind to living bone by the
formation of a bone-like apatite layer on its surface in
the body environment (Kokubo & Takadama 2006) or
by biofunctionalization (i.e. chemical and/or physical
modifications of the surface of a non-biological
material to make it biointeractive) (Kumar 2005,
BSI 2007, Schiephake & Scharnweber 2008). Few
materials directly bond to living bone without the
formation of detectable apatite on their surfaces
Correspondence: Dr. Maria Giovanna Gandolfi, DBiol, DSc,
MSc, PhD, Biomaterials Designer, Manager of Research,
Laboratory of Biomaterials and Oral Pathology of Endodontic
Clinical Section, Department of Odontostomatological Sciences
- University of Bologna, Via San Vitale 59, Bologna, Italy
(Tel.:+39 051 2088 184; e-mail: mgiovanna.gandolfi@
unibo.it).
doi:10.1111/j.1365-2591.2010.01768.x
ª 2010 International Endodontic Journal International Endodontic Journal, 43, 917–929, 2010 917
whereas most do so through the absorption of
biological molecules such as proteins. The examina-
tion of apatite formation on a material in simulated
body fluid (SBF) is a commonly accepted method to
predict its in vivo bone bioactivity (Kokubo & Takad-
ama 2006), although the use of SBF for bioactivity
testing may lead to false-positive and false-negative
results (Boher & Lemaitre 2009), and many materials
will not form an apatite layer in the laboratory but
will be bioactive in vivo and vice versa.
ProRoot MTA (Dentsply Maillefer, Tulsa, OK, USA)
has been extensively studied and has provided inter-
esting results in both laboratory (Torabinejad et al.
1995a,b) and in vivo tests (Holden et al. 2008, Pace
et al. 2008, Saunders 2008, Mente et al. 2009).
ProRoot MTA has demonstrated a wide range of
clinical applications including root-end filling and root
perforation repair.
As stated by the patent (US Patent Number,
5,769,638;1995) (Torabinejad & White 1995), Pro-
Root MTA (Mineral Trioxide Aggregate) is a hydraulic
calcium-silicate cement derivative of a type I ordinary
Portland cement with 4 : 1 proportions of bismuth
oxide added for radiopacity. Portland cement is the
active ingredient in white MTA (Torabinejad & White
1995). The active ingredients (clinker particles) of
ProRoot MTA are similar to those reported for other
Portland-based cements (Camilleri et al. 2005, Santos
et al. 2005, Camilleri 2007, 2008, Gandolfi et al.
2007), modified to improve radiopacity (Camilleri &
Gandolfi 2010), handling and setting time.
The bioactivity of Portland cements in phosphate-
buffered solutions has been reported recently when
immersed in phosphate solutions (Sarkar et al. 2005,
Tay et al. 2007, Coleman et al. 2009, Gandolfi et al.
2009a).
In this study, the bioactivity of ProRoot MTA was
investigated as a function of soaking time in a
phosphate solution (Dulbecco’s Phosphate Buffered
Saline, DPBS). Environmental scanning electron
microscopy connected to energy dispersive X-ray
(ESEM-EDX), FTIR and micro-Raman analyses were
performed to analyse the formation of apatite as an
index of bioactivity of the cement.
The study was aimed at gaining insight into the
bioactivity of ProRoot MTA as a function of short
soaking times (up to 7 days) in phosphate solution. The
hypothesis was that ProRoot MTA possesses early-stage
bioactivity with the ability to form apatite within a
few hours after immersion in phosphate-containing
solution.
Materials and methods
Sample preparation
The cement (ProRoot MTA, Dentsply Maillefer – lot n.
08003395) was mixed with water and placed on a
plastic coverslip of 13 mm diameter (Thermanox Plas-
tic, Nalgene Nunc Thermo Scientific, Rochester, NY,
USA) to obtain standard disks. Mechanical vibration
was used to obtain a flat, regular surface. The exposed
surface area of the disks was 1.9 ± 0.1 cm2 with a
thickness of approx. 0.9 mm. Immediately after prep-
aration, the samples were placed in DPBS (Dulbecco’s
Phosphate Buffered Saline) at 37 �C.
DPBS (Dulbecco’s Phosphate Buffered Saline; Lonza,
Lonza Walkersville Inc, Walkersville, MD, USA, cat.
n.BE17-512) is a physiological-like buffered (pH 7.4)
Ca and Mg-free solution with the following composition
(mM): K+ (4.18), Na+ (152.9), Cl) (139.5), PO43)
(9.56, sum of H2PO4) 1.5 mmol L)1 and HPO4
2)
8.06 mmol L)1).
In DPBS, the release of calcium ions from the
cements was the limiting parameter in the precipitation
reaction, and the large amount of phosphate represents
the continuous replenishment of phosphate ions from
tissue fluids. A commercial medium was selected
because of standardized and its availability. The end-
point times were 10 min (freshly prepared samples),
5 h, 1 and 7 days.
ESEM-EDX analysis
Samples were examined with an Environmental Scan-
ning Electron Microscope (ESEM, Zeiss EVO 50; Carl
Zeiss, Oberkochen, Germany) connected to a secondary
electron detector for Energy Dispersive X-ray analysis
(EDX; Oxford INCA 350 EDS, Abingdon, UK) computer-
controlled software Inca Energy Version 18, using an
accelerating voltage of 20–25 kV. The elemental anal-
ysis (weight % and atomic %) of samples was performed
applying the ZAF correction method. At 25-kV accel-
eration, the X-ray electron beam penetration of ESEM-
EDX (inside a material with a density of about
3 g cm)3) proved to be 2.98 micrometers, and conse-
quently the volume excited and involved in the
emission of characteristic X-rays from the constituting
elements was considered to be 10 micrometers3.
Cement disks were placed directly onto the ESEM stub
and examined without preparation (the samples were
not coated for this analysis). All samples were initially
analysed at low-vacuum conditions (9.9 Torr, 500 Pa),
Bioactivity of ProRoot MTA Gandolfi et al.
International Endodontic Journal, 43, 917–929, 2010 ª 2010 International Endodontic Journal918
100% relative humidity (RH) and 4 �C. After the initial
examination, each sample was inspected at higher
vacuum (2.9 Torr, 74 Pa), 40% RH and 4 �C.
Micro-Raman and ATR/FTIR spectroscopy
Micro-Raman spectra were obtained using a Jasco NRS-
2000C instrument (Jasco Inc., Easton, MD, USA)
connected to a microscope with 20 · magnification.
In these conditions, the laser spot size (i.e. the excita-
tion source) was a few microns. All the spectra were
recorded in back-scattering conditions with 5 cm)1
spectral resolutions using the 488-nm line (Innova
Coherent 70; Coherent Inc., Santa Clara, CA, USA)
with a power of 50 mW. A 160-K-frozen charge-
coupled detector (CCD) (Princeton Instruments Inc.,
Trenton, NJ, USA) was used.
IR spectra were recorded on a Nicolet 5700 FTIR
(Thermo Electron Scientific Instruments Corp., Madi-
son, WI, USA), equipped with a smart orbit diamond
attenuated total reflectance (ATR) accessory and a
deuterated triglycine sulphte (DTGS) detector; the
spectral resolution was 4 cm)1, and the number of
scans was 64 for each spectrum. The ATR area had
2 mm diameter. The IR radiation penetration was
about 2 microns.
To minimize the variability deriving from possible
sample inhomogeneity, at least five spectra were
recorded on five different points on the upper surface
of each specimen. Raman and IR spectra were also
recorded on unhydrated cement powder. The Raman
spectra were recorded on wet cement samples (i.e.
when maintained in their storage media).
pH measurements
The pH of the soaking solution DPBS was measured
with a Denver Intrument Basic pH meter (New York,
NY, USA) equipped with a Hamilton liquid–glass
electrode and ±0.01 resolution. The electrode was
inserted into the soaking solutions at room temperature
(24 �C). Each measurement was repeated three times.
Results
SEM-EDX analyses
ESEM-EDX analysis showed different surface morpho-
logies depending on the soaking time. EDX and the
elemental analysis on unhydrated cement powder
(Fig. 1) revealed Ca (calcium), Si (silicon), S (sulphur),
Al (aluminium), O (oxygen) and Bi (bismuth) and the
absence of P (phosphorus).
Freshly prepared samples (Fig. 2) had an uneven
surface with irregular granules. EDX and the elemental
analysis displayed high Ca Si, S, Al and Bi peaks. The
map of elements (Fig. 3) showed the distribution of O,
Al, Si, Ca, Bi and S on the freshly prepared cement.
After 1 day of storage in DPBS, the outer surface
was amorphous and irregular, with many visible
deposits composed of aggregates of apatite nano-
spherulites (Fig. 4a,d). Elongated structures (needle-
like crystals of ettringite) were occasionally disclosed.
Many spherulites (0.1–0.8 microns) precipitated on
the cement surface were packed to form clusters of
spheroidal bodies randomly distributed on the cement
surface. EDX and the elemental analysis showed Ca,
(a) (b) (c)
Figure 1 Morphology of unhydrated powder of ProRoot MTA. (a) Particles of different sizes are well visible. (b) EDX on marked
area revealed Ca, Si, S, O, Bi and Al and the absence of P in the cement composition. (c) Elemental analysis of marked area.
Gandolfi et al. Bioactivity of ProRoot MTA
ª 2010 International Endodontic Journal International Endodontic Journal, 43, 917–929, 2010 919
Si and P peaks, suggesting the presence of calcium
phosphate deposits (Fig. 4b,c). Punctual microanaly-
ses on spherulite clusters detected high Ca and P
peaks (Fig. 4e,f). Si was absent from the surface,
suggesting its accumulation mainly in the subsurface
calcium silicates hydrate (CSH) phase and a certain
release into the solution. The high O peak is
ascribable to the presence of water, Cl and Na
(traces) to the soaking medium. The Ca/P ratio from
the microanalysis of the area (Ca/P 1.89) was higher
than that obtained from the punctual microanalysis
(Ca/P 1.32), because the ratio value was affected and
increased by the contribution of calcium from
calcium carbonate (detectable by Raman and FTIR
but not by EDX).
After 7 days in DPBS, apatite deposits formed a layer
evenly distributed on the entire surface (Fig. 5a). At
high magnification, the deposits appeared to be
composed of aggregates of spherulites (Fig. 5c,d).
Punctual microanalyses and the elemental analysis
on spherulites showed Ca and P (Fig. 5e,f).
The Ca/P ratio from the elemental analysis of
punctual EDX on apatite spherulites increased over
the soaking time (Ca/P 1.32 after 1 day and 1.98 after
7 days) indicating the maturation of a carbonated-
apatite phase, where carbonate ions replaces phosphate
ions in the apatite structure (carbonate ion can
substitute both for OH in the apatite channel (type A
CAp) and for the phosphate ion (type B CAp).
Micro-Raman analyses
Several chemical modifications were observed on the
cement surface during ageing (Fig. 6). Band assign-
ments (Table 1) were made in accordance with the
literature (Taddei et al. 2009a,b).
(a)
(d) (e) (f)
(b) (c)
Figure 2 ProRoot MTA surface observed under environmental scanning electron microscope with energy dispersive X-ray 10 min
after preparation. (a,d) The surface appeared covered by particles of different sizes. (b) EDX on area displayed the presence of Ca, Si,
S, Bi, O and traces of Na, K and Al. (c) Elemental analysis of area. (e) Punctual EDX on marked formation displayed the presence of
Ca, Si, S, Bi, O and traces of K, Na and Al. (f) Elemental analysis of area.
Bioactivity of ProRoot MTA Gandolfi et al.
International Endodontic Journal, 43, 917–929, 2010 ª 2010 International Endodontic Journal920
The spectrum of the MTA unhydrated powder
showed the presence of alite (tricalcium silicate,
Ca3SiO5 sometimes formulated as 3CaO Æ SiO2) and
belite (dicalcium silicate, Ca2SiO4, sometimes formu-
lated as 2CaO Æ SiO2), calcium sulphate prevalently as
anhydrite (CaSO4), calcium carbonate (CaCO3) as
calcite and aragonite and bismuth oxide. No phosphate
band was detected in the unhydrated powder.
Freshly prepared samples showed the hydration of
alite, belite and anhydrite with formation of ettringite
(3CaO Æ Al2O3 Æ 3CaSO4 Æ 31H2O) and gypsum
(CaSO4Æ2H2O). The CSH phase (i.e. the hydration
product of alite and belite) had weak Raman bands,
detectable only at long storage times (Taddei et al.
2009a,b). The bands of anhydrite, alite and belite were
still observable. Calcium carbonate in different crystal-
line phases (calcite, aragonite, vaterite) was revealed.
The cements stored for 5 h in DPBS had apatite
deposits, although not well distributed over the entire
cement surface; anhydrite had disappeared.
At increasing storage times, the deposit became
progressively thicker and more homogeneous. After
one day, the band typical of an HPO42) -containing
apatite appeared; this result is consistent with a Ca/P
ratio of 1.32.
After 7 days of storage in DPBS, a calcite/aragonite
and B-type hydroxycarbonate apatite (HCA) coating
was present on the entire surface, and the cement
bands were significantly reduced in intensity because of
the increased thickness of the deposit.
The portlandite (i.e. calcium hydroxide, Ca(OH)2)
band at 360 cm)1 was never detected because of the
overlapping of the strong bands of bismuth oxide.
FTIR analyses
The spectrum of the MTA unhydrated powder con-
firmed the Raman results. Band assignments (Table 2
and Fig. 7) were made in accordance with the litera-
ture (Taddei et al. 2009a).
Figure 3 Map of the elements detected on the surface of freshly prepared ProRoot MTA. Calcium is present on the entire external
surface. Bismuth oxide particles are homogeneously distributed. The oxygen peak represents an index of water presence on fresh
samples.
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After 5 h in DPBS, the cement surface showed the
formation of ettringite, portlandite, CSH phase and an
apatite deposit; the bands of calcium carbonate (as
calcite, aragonite, vaterite), belite and alite were still
observable.
After 1 day, the bands typical of the cement compo-
nents were no longer detected in the spectrum; the
bands observed were all attributable to the presence of
B-type HCA and calcium carbonate deposit thicker
than 2 lm (penetration depth of the IR radiation) and
homogeneously distributed on the surface (all five
spectra recorded were coincident).
After 7 days, an even coating of more mature B-type
HCA was present; calcium carbonate was revealed in
higher amounts and in different chemical phases
(mainly calcite and aragonite).
pH measurements
The pH of the soaking solution DPBS was 7.4. After
immersion of the ProRoot MTA sample, the pH of DPBS
increased and attained alkaline values: pH approx. 9.9
after 10 min and pH approx. 11.3 from 5 h until
7 days.
Discussion
This study clearly demonstrated that ProRoot MTA
cement possesses high bioactivity and showed that
surface morphology and chemical composition are
rapidly modified by immersion in phosphate solution.
The significant finding of this study is that apatite
formation (revealed by the fast formation of calcium
(a)
(d) (e) (f)
(b) (c)
Figure 4 ProRoot MTA surface observed after 1 day of storage in DPBS. (a) Cement surface observed at low vacuum. Many
deposits composed of apatite spherulites were visible on cement surface. Elongated needle-like ettringite crystals (hydrated calcium-
aluminium-sulphate) and round-shaped calcium-silicate particles (alite, belite) were present on the surface. (b) EDX on area
displayed O, Ca, P and traces of Al, Na, Cl. No Si were noticed. The high O peak is ascribable to the presence of water. (c) Elemental
analysis of the area marked in picture a. (d) Cement surface observed at low vacuum (300 Pa) showing the mineral deposits. (e)
Punctual EDX on white deposits displayed O, Ca and P peaks. Cl and Na (traces) are because of the soaking medium. No Si was
detected. (f) Elemental analysis of a white deposit.
Bioactivity of ProRoot MTA Gandolfi et al.
International Endodontic Journal, 43, 917–929, 2010 ª 2010 International Endodontic Journal922
phosphate deposits of apatite nano-spherulites) starts
after 5 h of immersion into a phosphate-containing
solution, and a uniform thickness of the apatite layer is
formed in 7 days.
Recent studies have demonstrated the capacity of
calcium-silicate cements (Sarkar et al. 2005, Zhao et al.
2005, Bozeman et al. 2006 Coleman et al. 2007 and,
2009, Huan & Chang 2007, Tay & Pashley 2008, Ding
et al. 2009, Gandolfi et al. 2009a) to induce the
formation of apatite deposits. It has been reported that
the formation of CSH and HCA layer is used to define
the laboratory behaviour of the material (Hench &
West 1996, Rehman et al. 2000, Saravapavan et al.
2003, Orefice et al. 2009).
At first, Sarkar et al. (2005) immersed a non-
specified MTA in a phosphate-buffered saline solution
for 3 days and 2 weeks and showed the formation of
apatite by XRD analyses in the precipitates recovered
from the soaking solution. Then, Bozeman et al. (2006)
reported the formation of apatite on white and grey
MTA immersed for 40 days in a calcium-free PBS. No
previous study investigated either the apatite-forming
ability of ProRoot MTA at the early stages of hydration
or the kinetics formation of bone-like apatite (HCA) on
ProRoot MTA.
It was subsequently proved that apatite deposits
form on modified calcium silicate/tetrasilicate cements
(Gandolfi et al. 2009a, Taddei et al. 2009a,b, Torrisi
et al. 2010), white Portland cement (Coleman et al.
2009), tricalcium-silicate cements (Liu & Chang
2009) and experimental dicalcium-silicate cements
(Ding et al. 2009, Chen et al. 2009). In particular, the
bioactivity of a white Portland cement previously
cured for 28 days and ground then immersed in
simulated body fluid has been demonstrated using
FTIR spectroscopy and SEM-EDX (Coleman et al.
2009). The apatite-forming ability of a novel dical-
cium-silicate cement prepared by sol-gel method using
(a)
(d) (e) (f)
(b) (c)
Figure 5 ProRoot MTA after 7 days of storage in DPBS observed at 300 Pa. (a) Cement surface was covered by a layer of
aggregated apatite spherulites. The deposits are evenly distributed on the entire surface. (b) EDX showed Ca, P, O and Cl peaks and
traces of Na. (c,d) At higher magnification, clusters of apatite spherulites were well visible, and the morphology of apatite
spherulites (diameter 0.5–2 microns) is well visible. (e) Punctual EDX on the marked spherulite displayed the presence of Ca and P
peaks. (f) Elemental analysis of the marked globular formation.
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ª 2010 International Endodontic Journal International Endodontic Journal, 43, 917–929, 2010 923
orthosilicate and calcium nitrate after 1–90 days in
Hanks’ solution (Ding et al. 2009) or after 1–30 days
of immersion in Kokubo solution (Chen et al. 2009)
was demonstrated using XRD, FTIR and SEM-EDX
techniques.
In bioactivity studies, micro-Raman and IR spectros-
copy are complementary techniques able to detect
silicate, sulphate, carbonate, hydroxyl and phosphate
vibrational modes, allowing the hydration process of
the cement as well as apatite deposition to be followed.
IR spectroscopy is more sensitive than Raman spec-
troscopy in identifying the CSH phase and portlandite
in the presence of bismuth oxide; on the other hand,
the latter technique detects the alite/belite bands at
longer times than the former. Micro-Raman configu-
ration allows the detection of changes in chemical
composition on a microscale, as the laser spot (i.e. the
excitation source) size is a few microns. ESEM-EDX
(Environmental Scanning Electron Microscopy con-
nected to Energy Dispersive X-ray analysis) analysis
has been used to study calcium-silicate and calcium-
phosphate bioactive materials (Meredith et al. 1995)
and bone-like calcium phosphate layers.
So, in this study, both ESEM-EDX and micro-Raman
spectroscopy were used to investigate in situ and in
real-time the hydration and the surface morphology of
wet ProRoot MTA in its humid ‘‘natural’’ state with no
sample manipulation and minimal interference from
environmental water (Martinez-Ramirez et al. 2006,
Taddei et al. 2009a,b).
Figure 6 Micro-Raman spectra recorded
on the surface of ProRoot MTA at t = 0
(unhydrated cement), freshly prepared
(10 min) and after 5 h, 1 and 7 days
of storage in DPBS. The bands because
of belite (B), alite (A), anhydrite (An),
gypsum (G), calcite (C), aragonite (Ar),
vaterite (V), ettringite (E), apatite (Ap)
and bismuth oxide (Bi) have been
indicated.
Bioactivity of ProRoot MTA Gandolfi et al.
International Endodontic Journal, 43, 917–929, 2010 ª 2010 International Endodontic Journal924
These techniques allowed the investigation of the
morphology, the microstructure and the elemental
composition of ProRoot MTA and monitoring of the
chemical transformations of its dynamic surface imme-
diately after preparation and after 5 and 24 h and
7 days of soaking in simulated body fluid.
This study clearly demonstrated that ProRoot MTA
cement possesses high bioactivity, as revealed by the
rapid formation of calcium phosphate deposits of
apatite nano-spherulites at ESEM-EDX and the detec-
tion of apatite bands in FTIR and micro-Raman
analyses. ProRoot MTA develops a calcium-phos-
phate-rich layer that contains carbonate ions within
a few hours of immersion in a simulated physiological
solution. After 1 day in DPBS, the deposit appeared
evenly distributed over the entire surface. This study
demonstrated that ProRoot MTA surface morphology
and chemical composition are rapidly modified by
the surrounding environment, i.e. the phosphate
solution.
Table 1 Correlation of the Raman
spectral changes observed for the
ProRoot MTA surface with the stages of
formation of a B-type hydroxycarbonate
apatite (HCA) layer
Wavenumber (cm)1) Vibrational mode Crystal phase
1083 CO32) stretching Calcite/aragonite
1077 CO32) stretching B-type HCA
1070 CO32) stretching Vaterite
1014 SO42) stretching Anhydrite
1005 SO42) stretching Gypsum
1002 HPO42) stretching HPO4
2)-containing apatite
990 SO42) stretching Ettringite
973 SiO44) stretching Belite
960 PO43) symmetric stretching Apatite
854 SiO44) stretching Belite
839 SiO44) stretching Alite/belite
827 SiO44) stretching Alite
711 CO32) bending Calcite
670 SiO44) bending CSH phase
605 and 580 PO43) bending Apatite
CSH, calcium silicate hydrate.
Table 2 Correlation of the IR spectral
changes observed for the ProRoot MTA
surface with the stages of formation of a
B-type hydroxycarbonate apatite (HCA)
layer
Wavenumber (cm)1) Vibrational mode Crystal phase
3640 OH stretching Portlandite
1470-1465 CO32) stretching Aragonite and/or vaterite
and B-type HCA
1415-1410 CO32) stretching Calcite and B-type HCA
1150 and 1130 SO42) stretching Anhydrite/gypsum
1110 SO42) stretching Ettringite
1081 CO32) stretching Aragonite
1025 PO43) asymmetric stretching Apatite
960 PO43) symmetric stretching Apatite
940 SiO44) stretching CSH
910 SiO44) stretching Alite
870 CO32) bending Calcite and/or vaterite
and B-type HCA
870 and 850 SiO44) stretching Belite
850 CO32) bending Aragonite
711 CO32) bending Calcite/aragonite
700 CO32) bending Aragonite
675 and 620 SO42) bending Anhydrite/gypsum
600 and 560 PO43) bending Apatite
595 SO42) bending Anhydrite
510-490 SiO44) bending CxS
445 SiO44) bending CSH
CSH, calcium silicates hydrate; CxS, calcium silicates.
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Recent studies (Weller et al. 2008, Gandolfi & Prati
2010) demonstrated the sealing ability of calcium-
silicate cements used as root sealer in association with
gutta-percha. The formation of apatite may improve
the sealing ability and contribute to filling the marginal
porosities around restorations (Weller et al. 2008).
Moreover, apatite formation on the external surface
may contribute to cement expansion, as demonstrated
by another study with LVDT measurements (Gandolfi
et al. 2009a). Finally, this apatite may contribute to the
bio-remineralization of dentine just around the resto-
rations, an innovative biomechanism recently proposed
(Tay & Pashley 2008).
When immersed in fluids, ProRoot (like other
calcium-silicate cements) rapidly releases calcium ions
and creates an alkaline pH on the external surface
leading to the nucleation and crystallization of HCA on
the cement surface. The Ca/P ratio derived from the
apatite layer increased over soaking time (Ca/P 1.32
after 1 day and 1.98 after 7 days) indicating the
maturation of a carbonated-apatite phase (bone-like
apatite), where carbonate replaces phosphate ions (the
Ca/P ratio increased with increasing carbonate con-
tent).
When clinker grains of ProRoot MTA are mixed with
water (mixing solution), several reactions occur.
According to the literature (Camilleri 2007), the
silicate phase hydrates with formation of CSH and
portlandite. Raman spectra (Fig. 6) showed that alite
hydrates more quickly than belite: in the spectrum of
the freshly prepared cement, the bands attributable to
belite at 839 and 827 cm)1 significantly decreased in
intensity with respect to the belite band at 854 cm)1.
The formation of CSH and portlandite was not revealed
by Raman spectroscopy. In fact, the former is charac-
terized by weak bands, only observable at long storage
times, and the latter cannot be detected because of the
interference of bismuth oxide, which shows strong
bands superimposed on the 360 cm)1 portlandite
component. However, the increase in the pH of the
storage medium (9.9 after 10 min) indicates the release
of portlandite and the occurrence of the hydration
reaction.
Based on these findings, it can be hypothesized that:
1 A solid–liquid interface forms on the mineral
particles, and ion dissolution occurs almost immedi-
ately. Ca2+ions rapidly migrate into the mixing solution
and portlandite (i.e. Ca(OH)2) forms.
2 Silicates are attacked by OH) ions (hydrolysis of
SiO44) groups in alkaline environment), and a CSH
phase forms on mineral particles. CSH is a porous, fine-
grained and highly disorganized hydrated silicate gel
layer containing Si-OH silanol groups (Skibsted & Hall
2008) and negative surface charges that may act as
nucleation sites for apatite formation (Oliveira et al.
2003, Li et al. 2007).
3 The CSH contains an excess of calcium hydroxide
(formed by OH) ions from dissociated water molecules
with Ca2+ions from cement particles), as revealed by
the presence of portlandite inside the CSH phase of the
cement surface after 5 h of storage in DPBS. A
continuous flux of excess of portlandite formed in the
CSH structure occurs; portlandite diffuses outward and
passes into the storage solution, and a large increase in
pH occurs (pH approx. 9.9 after 10 min and pH approx.
11.3 since 5 h). Calcium ions in excess diffuse through
the initial CSH layer, causing a supersaturation with
Figure 7 Fourier transform infrared spectra recorded on the
surface of ProRoot MTA at t = 0 (unhydrated cement) and
after 5 h, 1 and 7 days of storage in DPBS. The bands due to
belite (B), alite (A), calcium silicates (CxS), hydrated calcium
silicates (CSH), portlandite (P), anhydrite (An), gypsum (G),
calcite (C), aragonite (Ar), vaterite (V), apatite (Ap) have been
indicated.
Bioactivity of ProRoot MTA Gandolfi et al.
International Endodontic Journal, 43, 917–929, 2010 ª 2010 International Endodontic Journal926
respect to Ca(OH)2; portlandite crystals nucleate
throughout the paste (Taddei et al. 2009a,b) and were
also detectable on the surface. The portlandite release
continues during storage time, as revealed by the pH of
the storage solution which remained constant at 11.3.
4 When exposed to a phosphate-containing solution
such as DPBS, a series of reactions take place on the
surface of ProRoot MTA between calcium from the
cement and phosphate from the solution, namely the
absorption of Ca and P ions on the silica-rich CSH
surface (as a result of local supersaturation) and the
precipitation of a HPO42)-containing apatite, which
matures into a B-type HCA phase at increasing storage
times. The apatite layer fills the superficial porosities
and may expand the mass of the cement.
During surgical procedures, blood and serum may
rapidly contaminate the external surface of cement
immediately after its placement in the root apical
cavity. So, it can be presumed that apatite formation
may occur in the presence of such fluids in vivo
(Holland et al. 2007, Reyes-Carmona et al. 2009). The
continuous flow of blood and biological fluids in the
surgical site constantly provides new phosphate and
may increase the amount of apatite formed on the
cement surface, as recently described by Gandolfi et al.
(2009a).
The cement proved to be a sort of remineralizing
agent and reservoir able to promote apatite deposition;
it can contribute to maintaining a stable seal when
placed in root-end cavities and promotes osteoblast
growth (Camilleri et al. 2005, Camilleri & Pitt Ford
2006, Gandolfi et al. 2008, Gandolfi et al. 2009c). The
previous in vitro studies on cell activity were probably
performed on a bioactive substrate because of the use of
phosphate-rich solutions. On the contrary, the evalu-
ation of mechanical properties, i.e. setting reaction,
flexural strength and sealing tests, should be re-
evaluated considering the effect of phosphate solutions
on material properties (Gandolfi et al. 2009a,b).
The excellent bioactivity (i.e. apatite formation abil-
ity) of ProRoot MTA might give a significant clinical
advantage over the traditional cements used for root-
end or root-perforation repairs and may be correlated
with its optimal biocompatibility, osteconductivity and
osteoinductivity demonstrated in many clinical and
laboratory studies.
Acknowledgement
The authors thank Dr Fabiola D’Amato for the precious
secretariat support.
Declaration
The authors deny any financial affiliations (e.g.
employment, direct payment, stock holdings, retainers,
consultantships, patent licensing arrangements or
honoraria), or involvement with any commercial
organization with direct financial interest in the subject
or materials discussed in this manuscript, nor have any
such arrangements existed in the past 3 years. Any
other potential conflict of interest is disclosed.
References
Bohner M, Lemaitre J (2009) Can bioactivity be tested in vitro
with SBF solution? Biomaterials 30, 2175–9.
Bozeman TB, Lemon RR, Eleazer PD (2006) Elemental analysis
of crystal precipitates from gray and white MTA. Journal of
Endodontics 32, 425–8.
BSI (2007) Terminology for the bio-nano interface. PAS 132,
2007.
Camilleri J (2007) The hydration mechanisms of mineral
trioxide aggregate. International Endodontic Journal 40, 462–
70.
Camilleri J (2008) Characterization of hydration products of
mineral trioxide aggregate. International Endodontic Journal
41, 408–17.
Camilleri J, Gandolfi MG (2010) Evaluation of the radiopacity
of calcium silicate cements containing different radiopacifi-
ers. International Endodontic Journal 43, 21–30.
Camilleri J, Pitt Ford TR (2006) Mineral trioxide aggregate: a
review of the constituents and biological properties of the
material. International Endodontic Journal 39, 747–54.
Camilleri J, Montesin FE, Di Silvio L, Pitt Ford TR (2005) The
chemical constitution and biocompatibility of accelerated
Portland cement. International Endodontic Journal 38, 834–
42.
Chen CC, Ho CC, Chen CHD, Wang WC, Ding SJ (2009) In vitro
bioactivity and biocompatibility of dicalcium silicate
cements for endodontic use. Journal of Endodontics 35,
1554–7.
Coleman NJ, Nicholson JW, Awosanya K (2007) A
preliminary investigation of the in vitro bioactivity of
white Portland cement. Cement and Concrete Research 37,
1518–23.
Coleman NJ, Awosanya K, Nicholson JW (2009) Aspects of the
in vitro bioactivity of hydraulic calcium (alumino) silicate
cement. Journal of Biomedical Material Research 90A, 166–74.
Ding SJ, Shie MY, Wang CY (2009) Novel fast-setting calcium
silicate bone cements with high bioactivity and enhanced
osteogenesys in vitro. Journal of Material Chemistry 19,
1183–90.
Gandolfi MG, Pagani S, Perut F, Ciapetti G, Baldini N,
Mongiorgi R, Prati C (2008) Innovative silicate-based
cements for endodontics: a study of osteoblast-like cell
Gandolfi et al. Bioactivity of ProRoot MTA
ª 2010 International Endodontic Journal International Endodontic Journal, 43, 917–929, 2010 927
response. Journal of Biomedical Material Research 87, 477–
86.
Gandolfi MG, Sauro S, Mannocci F et al. (2007) New tetrasi-
licate cement as retrograde filling material: an in vitro study
on fluid penetration. Journal of Endodontics 33, 1082–5.
Gandolfi MG, Taddei P, Tinti A, Dorigo De Stefano E, Rossi PL,
Prati C (2009a) Kinetics of apatite formation on a calcium-
silicate cement for root-end filling during ageing in physi-
ological-like phosphate solutions. Clinical Oral Investigation
DOI 10.1007/s00784-009-0356-3.
Gandolfi MG, Iacono F, Agee K et al. (2009b) Setting time and
expansion in different soaking media of experimental
accelerated calcium-silicate cements and ProRoot MTA.
Oral Surgery, Oral Medicine, Oral Pathology, Oral Radiology
and Endodontics 108, e39–45.
Gandolfi MG, Ciapetti G, Perut F, Taddei P, Modena E, Rossi
PL, Prati C (2009c) Biomimetic calcium-silicate cements
aged in simulated body solutions. Osteoblasts response and
analyses of apatite coating. Journal of Biomedical Material
Research 7, 160–70.
Gandolfi MG & Prati C (2010) MTA and F-doped MTA
cements used as sealers with warm gutta-percha. Long-term
study of sealing ability. International Endodontic Journal, in
press.
Hench LL, West JK (1996) Biological application of bioactive
glasses. Life Chemistry Reports 13, 187–241.
Holden DT, Schwartz SA, Kirkpatrick TC, Schindler WG
(2008) Clinical outcomes of artificial root-end barriers with
mineral trioxide aggregate in teeth with immature apices.
Journal of Endodontics 34, 812–7.
Holland R, Mazuqueli L, De Souza V, Satomi Murata S, Dezan
E Jr, Suzuki P (2007) Influence of the type of vehicle and
limit of obturation on apical and periapical tissue response
in dogs’ teeth after root canal filling with mineral trioxide
aggregate. Journal of Endodontics 33, 693–7.
Huan Z, Chang J (2007) Self-properties and in vitro bioactivity
of calcium sulphate hemihydrate-tricalcium silicate com-
posite bone cements. Acta Biomaterialia 3, 952–60.
Kokubo T, Takadama H (2006) How useful is SBF in
predicting in vivo bone bioactivity? Biomaterials 27,
2907–15.
Kumar CSSR (2005) Biofunctionalization of nanomaterials.
Nanotechnologies for life sciences 1. Weinheim: Wiley-VCH,
Verlag GmbH & Co. KGaA.
Li X, Shi J, Zhu J et al. (2007) A template route to the
preparation of mesoporous amorphous calcium silicate with
high in vitro bone-forming bioactivity. Journal of Biomedical
Material Research B: Applied Biomaterials 83B, 431–9.
Liu W, Chang J (2009) In vitro evaluation of gentamycin
release from a bioactive tricalcium silicate bone cement.
Material Science and Engineering C 29, 2486–92.
Martinez-Ramirez S, Frıas M, Domingo C (2006) Micro-Raman
spectroscopy in white Portland cement hydration: long-term
study at room temperature. Journal of Raman Spectroscopy
37, 555–61.
Mente J, Hage N, Pfefferle T et al. (2009) Mineral trioxide
aggregate apical plugs in teeth with open apical foramina: a
retrospective analysis of treatment outcome. Journal of
Endodontics 35, 1354–8.
Meredith P, Donald AM, Luke K (1995) Pre-induction and
induction hydration of tricalcium silicate: an environmental
scanning electron microscopy study. Journal of Materials
Science 30, 1921–30.
Oliveira AL, Malafaya PB, Reis RL (2003) Sodium silicate gel
as a precursor for the in vitro nucleation and growth of a
bone-like apatite coating in compact and porous polymeric
structures. Biomaterials 24, 2575–84.
Orefice R, Hench L, Brennan A (2009) Evaluation of the
interactions between collagen and the surface of a bioactive
glass during in vitro test. Journal of Biomedical Material
Research 90A, 114–20.
Pace R, Giuliani V, Pagavino G (2008) Mineral trioxide
aggregate as repair material for furcal perforation: case
series. Journal of Endodontics 34, 1130–3.
Rehman I, Karsh M, Hench L, Bonfield W (2000) Analysis of
apatite layers on glass-ceramic particulate using FTIR and
FT-Raman spectroscopy. Journal of Biomedical Material
Research 50, 97–100.
Reyes-Carmona JF, Felippe MS, Wilson TF (2009) Biominer-
alization ability and interaction of mineral trioxide aggre-
gate and white Portland cement with dentin in a phosphate-
containing fluid. Journal of Endodontics 35, 731–6.
Santos AD, Moraes JCS, Araujo EB, Yukimitu K, Valerio Filho
WV (2005) Physico-chemical properties of MTA and a novel
experimental cement. International Endodontic Journal 38,
443–7.
Saravapavan P, Jones JR, Pryce RS, Hench LL (2003)
Bioactivity of gel-glass powders in the CaO-SiO2 system: a
comparison with ternary (CaO-P2O5-SiO2) and quaternary
glasses (SiO2-CaO-P2O5-Na2O). Journal of Biomedical Material
Research 66A, 110–9.
Sarkar NK, Caicedo R, Ritwik P, Moiseyeva R, Kawashima I
(2005) Physicochemical basis of the biologic properties of
mineral trioxide aggregate. Journal of Endodontics 31, 97–
100.
Saunders WP (2008) A prospective clinical study of perira-
dicular surgery using mineral trioxide aggregate as a root-
end filling. Journal of Endodontics 34, 660–5.
Schiephake H, Scharnweber D (2008) Chemical and biological
functionalization of titanium for dental implants. Journal of
Materials Chemistry 18, 2404–14.
Skibsted J, Hall C (2008) Characterization of cements minerals,
cements and their reaction products at the atomic and nano
scale. Cement and Concrete Research 38, 205–25.
Taddei P, Tinti A, Gandolfi MG, Rossi PL, Prati C (2009a)
Vibrational study on the bioactivity of portland cement-
based materials for endodontic use. Journal of Molecular
Structure 924 924–926, 548–54.
Taddei P, Tinti A, Gandolfi MG, Rossi PL, Prati C (2009b)
Ageing of calcium silicate cements for endodontic use in
Bioactivity of ProRoot MTA Gandolfi et al.
International Endodontic Journal, 43, 917–929, 2010 ª 2010 International Endodontic Journal928
simulated body fluids: a micro-Raman study. Journal of
Raman Spectroscopy 40, 1858–66.
Tay FR, Pashley DH (2008) Guided tissue remineralization of
partially demineralised human dentine. Biomaterials 29,
1127–37.
Tay FR, Pashley DH, Rueggeberg FA, Loushine RJ, Weller RN
(2007) Calcium- phosphate phase transformation produced
by the interaction of the Portland cement component of
white mineral trioxide aggregate with a phosphate-contain-
ing fluid. Journal of Endodontics 33, 1347–51.
Torabinejad M, White DJ (1995) US Patent Number,
5,769,638; May 1995.
Torabinejad M, Smith PW, Kettering JD, Pitt Ford TR (1995a)
Comparative investigation of marginal adaptation of min-
eral trioxide aggregate and other commonly used root-end
filling materials. Journal of Endodontics 21, 295–9.
Torabinejad M, Hong UJ, McDonald F, Pitt Ford TR (1995b)
Physical and chemical properties of a new root-end filling
material. Journal of Endodontics 21, 349–53.
Torrisi A, Torrisi V, Tuccitto N, Gandolfi MG, Prati C,
Licciardello A (2010) Tof SIMS images and spectra of
biomimetic calcium-silicate based cements after storage in
solutions simulated the human biological fluid effects.
International Journal of Mass Spectrometry 289, 150–61.
Weller RN, Tay KCY, Garrett LV et al. (2008) Microscopic
appearance and apical seal of root canals filled with gutta-
percha and ProRoot Endo Sealer after immersion in a
phosphate-containing fluid. International Endodontic Journal
41, 977–86.
Zhao W, Wang J, Zhai W, Wang Z, Chang J (2005) The self-
setting properties and in vitro bioactivity of tricalcium
silicate. Biomaterials 26, 6113–21.
Gandolfi et al. Bioactivity of ProRoot MTA
ª 2010 International Endodontic Journal International Endodontic Journal, 43, 917–929, 2010 929