an in vitro investigation into the accuracy of cad/cam digitizing
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An in vitro investigation into the accuracy of CAD/CAM digitizing devices formeasurement of tooth wear
Austin, Rupert Sloan; Elliott, Thomas
Awarding institution:King's College London
Download date: 12. Apr. 2018
KING’S COLLEGE LONDON DENTAL INSTITUTE
An in vitro investigation into the accuracy of CAD/CAM digitizing
devices for measurement of tooth
wear Submitted in Partial Fulfilment of
MClinDent Prosthodontics
Thomas Elliott 7/1/2014
1
Contents
Acknowledgements .................................................................................................................. 4
Abstract .......................................................................................................................................... 5
Literature Review ...................................................................................................................... 7
1.1 Introduction ................................................................................................................. 7
1.2 Profilometry ................................................................................................................ 8
1.2.1 Surface Profile Measurement ...................................................................... 9
1.2.2 Contacting Profilometry ................................................................................ 9
1.2.3 Non-‐contacting Profilometry .................................................................... 10
1.2.4 Limitations of Optical Instruments ........................................................ 11
1.3 Applications of Profilometry in Dental Research ..................................... 12
1.4 Accuracy of Profilometers in Dental Research .......................................... 15
1.4.1 Fundamentals of Metrology ...................................................................... 17
1.4.2 Accuracy of Profilometry ............................................................................ 17
Measuring Tooth Wear ................................................................................................... 22
1.4.3 Qualitative Measurement of Tooth Wear ............................................ 23
1.4.4 Traditional Quantitative Measurement of Tooth Wear ................ 24
1.4.5 Profilometry and Tribology Studies ...................................................... 26
Aims and Objectives .............................................................................................................. 32
2.1 Aims ............................................................................................................................. 32
2.2 Objectives .................................................................................................................. 32
2
Null Hypotheses ...................................................................................................................... 34
Materials and Methods ......................................................................................................... 35
3.1 Test Digitizing Devices ......................................................................................... 36
3.2 Test Conditions for Measurement .................................................................. 36
3.3 Measurement Software ........................................................................................ 36
3.4 Specimen Preparation .......................................................................................... 37
3.5 Engineering Slip Gauge Specimen ................................................................... 37
3.6 Inlay shaped Specimen and Bridge Shaped Specimen ........................... 41
3.7 ‘Proof of Concept’ of Using the 3Shape® Extra-‐oral Scanner and the
3M™ True Definition Intra-‐oral Scanner to Follow a Profilometric Tooth
Wear Measurement Technique ................................................................................... 50
3.8 Statistics ..................................................................................................................... 53
Results ......................................................................................................................................... 55
4.1 Measurement of Engineering Slip Gauges ................................................... 55
4.2 Repeatability, Reproducibility and Trueness of Measurement of the
Inlay Shaped Specimen and the Bridge Shaped Specimen .............................. 57
4.2.1 Repeatability Measurement Results ...................................................... 57
4.2.2 Reproducibility of the Measurement .................................................... 59
4.2.3 Trueness of the Measurement ................................................................. 61
4.3 ‘Proof of Concept’ of Using the 3Shape® Extra-‐oral Scanner and the
3M™ True Definition Intra-‐oral Scanner to Follow a Profilometric Tooth
Wear Measurement Technique ................................................................................... 63
3
Discussion .................................................................................................................................. 65
Conclusion ................................................................................................................................. 70
References ................................................................................................................................. 71
4
Acknowledgements
Professor David Bartlett
Dr. Rupert Austin
Mr Alberto Alverez and Mr Steven Nelson from 3M ESPE for the loan of the
3M™ True Definition Scanner.
The laboratory technicians in Orthodontics for their training in the use of
the 3Shape scanner
5
Abstract
Aim: To investigate the accuracy and precision of measurement of extra-‐oral
and intra-‐oral digitizing devices, and to carry out a ‘proof of concept’
evaluation following a previously published profilometric tooth wear
measurement technique.
Methodology: Engineering slip gauges of known dimensions were scanned
and measurements were compared to the gold standard measurement
device (a triangulation laser profilometer). Inlay-‐ and bridge-‐shaped
artifacts were used to assess precision (repeatability and reproducibility)
and accuracy (trueness) of the test devices. Each device recorded sixty scans
and the variances of the height and angle measurements of the artifacts
were calculated to assess repeatability and reproducibility. Accuracy was
then calculated by measuring the difference between the mean repeatability
measurement of the reference device and the mean repeatability
measurement of the test device. Finally, tooth wear calibration models that
had previously used to evaluate a method of profilometric tooth wear
measurement were scanned by the test digitizing devices and compared to
the reference profilometer. In all instances the scans were analysed using
Geomagic® Qualify 11 computer software and parametric statistical analyses
were performed.
Results. All digitizing devices demonstrated good correlation in measuring
slip gauge widths of 400 μm and above. However, below this value the test
devices were unable to provide accurate readings, while the reference
scanner was able to measure to 100 μm. Repeatability and reproducibility
6
for both the extra-‐oral and the intra-‐oral scanners was found to be
statistically significantly increased than that of the reference profilometer
when measuring either the height or the angle of both the inlay specimen
and the bridge specimen (p<0.05). Both the 3Shape® extra-‐oral scanner and
the 3M™ True Definition intra-‐oral scanner were able to follow the
previously published profilometric tooth wear measurement process,
however they showed a mean volume error of ± 0.2 mm3.
Conclusions. The optical resolution and precision of the test scanners was
inferior to the reference profilometer however the trueness of measurement
between the test devices was not statistically significant (p>0.05).
7
Literature Review
1.1 Introduction
Following rapid progress in the use of computer assisted processing
technology in other industries, research and development in dental
profilometry has been prevalent since the 1980’s and is still growing today.
In 2012 Millennium Research Group (MRG), the global authority on medical
technology market intelligence, predicted that the worldwide CAD/CAM
system market is set to reach a value upwards of $560 million by 2016.
Moreover, they state that from around 50 percent of the CAD/CAM market
in 2010, chairside systems and intra-‐oral scanners will hold nearly 60
percent of a much larger market by 2016. This indicates that the use of these
technologies will be far more widespread in dentistry over the coming
years.
The use of profilometry in clinical dentistry is becoming increasingly
relevant, especially with the advent of optical scanning systems that can
record the oral environment directly. This negates the need for impressions
that can introduce errors, albeit small ones, due to the inherent properties
of the material used (Eames et al. 1979, Williams et al. 1984), operator error
(Carrotte et al. 1993, Winstanley et al. 1997), or due to the casting process.
Extra-‐oral non-‐contact profilometers are also used frequently in dentistry,
including the 3Shape® scanner under investigation in this study. However,
these machines still rely on transfer of information via traditional
impressions.
8
Surface point measurements captured by profilometers are stored in the
form of binary digits or ‘bits’. These bits are then combined into larger units
to provide more meaningful data. In practical terms the advantages of
having data in this form is that it can be stored and then used to guide the
milling process or for future reference. Another advantage is that scans can
be recorded in one location and the information sent via the Internet to an
alternate location where it can be used for various purposes but usually
prosthesis construction. This has transformed the scale of production
previously seen with traditional techniques.
The use of dental CAD/CAM for construction of prostheses and for
laboratory based studies have been well documented (Persson et al. 1995,
Luthardt et al. 2001, Syrek et al. 2010 etc.) but there is need to establish
whether this technology is able to offer further clinical benefits, such as the
quantitative measurement of tooth wear over time. As noted by DeLong et
al. (2003), “interactive three-‐dimensional images of the soft and hard tissues
of the dental patient will provide dentists with quantitative evidence to aid
dentists in diagnosis, treatment planning, and outcome assessment.”
Naturally, in order for this to be applicable we must show that any images
recorded are accurate representations of the patient’s intra-‐oral tissues.
1.2 Profilometry
Essentially a profilometer is a device used to record the surface profile of an
object. Vlaar et al. (2006) defined a dental profilometer as “a device used to
record the topographical characteristics of teeth, dental impressions or
9
stone models by analog or digital methods for use in computer assisted
design and manufacturing of dental prosthetic restorative devices.”
1.2.1 Surface Profile Measurement
Surface profile measurement is described in ‘Fundamental Principles of
Engineering Nanometrology (2nd Edition)’ as the measurement of a line
across a surface that can be represented mathematically as a height function
with lateral displacement, z (x). By lining up parallel profiles a topographic
image can be produced representing z (x,y). Profilometers, also referred to
as digitizing devices or scanners, can be broadly divided into two categories:
contact and non-‐contact. Either a stylus (contact) or an optical instrument
(non-‐contact) is used to measure the surface profile. In non-‐contacting
profilometry an optical instrument is used to carry out a measurement, and
the surface profile of the point cloud recorded is then usually extracted in
software.
1.2.2 Contacting Profilometry
This is by far the most common method for measuring surface topography
within engineering measurement applications. In contacting profilometry
the stylus is traversed across a line on the surface being measured at a given
distance and contact pressure (typically 0.75 mN). The profile measurement
can then be recorded by mapping vertical displacement of the stylus as a
function of its position z (x,y). The accuracy of the data recorded depends
largely on the radius of the stylus and the scan speed. The stylus can be as
small as 2 μm, and as such can usually offer better accuracy than non-‐
contact profilometers.
10
A drawback of a stylus instrument when scanning an area is the time
required to record a measurement as this can often be up to several hours.
This is an area where optical instruments offer an advantage over the stylus
instruments. Within dentistry this type of profilometer only has laboratory
applications.
1.2.3 Non-‐contacting Profilometry
Non-‐contact profilometers operate using a variety of techniques, e.g. laser
triangulation and confocal microscopy. These techniques can be regarded in
two categories: those that measure actual surface topography by scanning a
beam or using field of view, and those that measure a statistical parameter
of the surface, usually by analyzing the distribution of scattered light.
The measurement can be affected by the need to stitch optical images
together. Stitching can be a significant source of error in optical
measurements (Bray 2004, Zhang 2006), and it is important that the
process is well defined and understood for any given application.
1.2.3.1 Triangulation Lasers
Laser triangulation instruments measure the relative distance to a surface.
Light is projected onto the surface where it then scatters. A detector then
focuses the scattered light onto a sensor. Because the fixed angle between
the projector and sensor is known, the distance to the object can be
calculated through Pythagoras’ theorem, as one side and one angle of the
triangle are now known, hence the name ‘‘triangulation’’. As the surface
changes the focused light moves across the sensor enabling the surface
characteristics to be recorded. The reference profilometer used in this study
11
and the 3Shape® extra-‐oral scanner both utilise this technology. However,
the two machines operate differently in that the former has a fixed scan
head whereas the latter has more cameras and a motion system supporting
several axes for positioning the scanned object towards the light source and
camera, allowing surface mapping from multiple angles, including
undercuts.
1.2.3.2 Active Wavefront Sampling
This is the 3-‐D imaging technique employed by the 3M™ True Definition
intra-‐oral scanner. Essentially light reflected from the object being scanned
is reflected through a lens system onto a sensor. If the object is in focus then
it coincides with the given focal length of the lens but if the object is blurred
then the distance from the object to the lens is calculated by a set
mathematical formula. This information is then combined to provide three
dimensional cloud points required for surface mapping. Twenty 3-‐D
datasets per second can be captured with over 10,000 data points in each,
resulting in over or 24 million data points for an accurate scan.
1.2.4 Limitations of Optical Instruments
Non-‐contact profilometers offer a number of advantages over contacting
profilometers: they do not physically contact the surface so won’t damage it
and they are usually faster at recording measurements. However there are
also some limitations to the use of these optical instruments. In order to
magnify the surface features of the object being recorded a microscope is
required. Any instrument that uses a microscope objective has defined
limitations:
12
1. Numerical Aperture – The numerical aperture is a measure of how
much light can be collected by an optical system such as a microscope
lens. This determines the largest slope angle of the surface that can
be measured because it is related to the acceptance angle, which
indicates the size of a cone of light that can be physically reflected
back into the objective lens and therefore be measured.
2. Optical resolution of the objective – This determines the minimum
distance between two lateral features on a surface that can be
measured.
Another limitation for non-‐contacting profilometry is optical spot size. In
scanning instruments like the ones used for dentistry this will determine the
area of surface measured as the instrument scans, much like the stylus in
contacting profilometry.
As result of the aforementioned limitations most optical instruments
experience difficulties when measuring very high slope angles or
discontinuities.
1.3 Applications of Profilometry in Dental Research
Over the years the description of techniques and methods for assessing the
accuracy of profilometers have been varied. Most of the initial reports
focused on measuring wear in dental materials, particularly composites, in
order to assess their suitability as restoratives. Initial techniques largely
relied on before and after impressions and casts in order to assess the wear,
which, as previously discussed, carry their own inaccuracies.
13
In one of the first attempts at volumetric measurement using profilometry
Atkinson et al. (1982) used laser optical interferometry in order to assess
wear in dental restorations. Measurements were made by comparing
suitable impressions of the restorative being investigated both before and
after the test. Detailed information about the pre and post wear restorative
was then obtained from contour maps of the impressions in order to find the
volume of restorative material lost during the test. The authors recognised
that the whole experiment relies on the accuracy of the polyvinylsiloxane
impression material so they investigated this and found it to be “adequate.”
The authors also related how the pre and post wear contour maps had to be
repositioned in order to have the same reference plane during comparison
and provide reproducibility. The contour maps were compared using three
different methods: a fringe displacement method, a moiré method and, most
appropriate to the experiment being presented, by computer-‐aided analysis.
When looking at the volume of material lost, an accuracy of 4% was
described for the computer-‐aided analysis method, which the authors
considered to be the “most accurate” of the three methods described. The
discussion does state that the main drawback was the length of time
required to digitize the contour maps (30 minutes per pair) and the
experiment described translates to the reader as a particularly arduous
undertaking.
DeLong et al. (1985) describe a method to measure and capture change in
surface contour of restorations using a combination of servohydraulics and
computer graphics. Measuring two depressions of a known value in a flat
aluminium surface assessed the accuracy of this method. Using a
14
servohydraulic machine, a stylus was run across the surface of the
depressions and the coordinates fed into a microcomputer. Each pass over
the surface constituted one profile and numerous profiles could then be
assembled using computer graphics in order to provide an image of the
surface. The device measured a 6 μm3 depression as 5.3 ± 0.6 μm3 (12%
error) and a 28.1 μm3 depression as 28.8 μm3 ± 1.1 μm3 (2.5% error), which
were considered “acceptable” and “very good” respectively. Even at this
early stage of computer mapping the authors recognised that “an important
feature of this method is the ability to visualise the change in surface
contour and relate it to anatomy of the tooth.”
Hewlett et al. (1992) first identified the need for a gold standard against
which profilometers could be periodically calibrated. They note,
“Descriptions of instrument capability have rarely distinguished between
precision (the level of instrument variability) and accuracy (the degree to
which a measurement actually represents what it is intended to represent).”
In their investigations a contact profilometer was used to measure points at
200 μm intervals on a precision steel sphere, half embedded in acrylic.
These points were stored in a computer memory. ‘True’ value for any point
on a hemispherical surface can be measured using Pythagorean Theory, so
by using the known value of the scanner contact tip (1 mm) and the
precision sphere (6.35 mm) it was therefore possible to determine
trigonometrically the error of each point measurement due to the slope on
the surface of the sphere. Because the point error would equal zero if no
mechanical error existed, the accuracy of the device as a function of the
slope of the measurement point could be quantitatively measured. The
15
results indicated a linear relationship between increased surface slope angle
and increased error for the device being tested. The authors note that in
practical terms that when measuring an occlusal surface a coordinate
measuring machine will undoubtedly encounter steep angles due to the
cusps. Not only that, but the size of the contact probe is problematic when
considering fine detail. Despite this the authors assert, “The accuracy test
described here has validity and is applicable as a standard for three-‐
dimensional contour measuring instruments.” The findings of this study
were similar to Rudolph et al. (2007) who investigated the influence of
digitizing and surface morphology on the accuracy in CAD/CAM technology.
Three different non-‐contact profilometers were used to scan metal teeth and
the authors found that areas of strong curvature showed the largest
deviation. However they found that these deviations do not significantly
influence error in the duplicate and are to be expected when measuring a
free form surface such as a tooth.
1.4 Accuracy of Profilometers in Dental Research
Producing an exact three-‐dimensional replica of any given object is near
impossible no matter what method or material is being used. The areas in
which error might occur in a replication process are often the subjects of
much investigation in an effort to be as accurate and precise as possible.
Dahlmo (2001) notes that in CAD/CAM there are three potential sources for
error:
1. Measurement accuracy of the device used and in the transfer of
data files to the computer.
16
2. The ability for computer software to accurately transfer data, so
that what is designed on the computer translates accurately in the
manufacture.
3. The manufacturing processes and the precision of machinery used
to manufacture a restoration.
It is not the remit of this investigation to cover the accuracy of the
manufacturing process. However, the inherent accuracy of profilometers
and their ability to provide quantitative data will be considered.
In his book ‘Degradation of Dental Polymers’ (1987) Jean-‐François Roulet
provided a detailed description for accuracy determination of profilometers
using impressions and casts highlighting three key determinants:
1. The inherent accuracy of the profilometer.
2. Producing an accurate replica.
3. Repositioning the replica accurately.
Modern profilometers are able to capture information directly from the
intra-‐oral environment and surface-‐mapping software exists to allow best fit
matching of scans. This means that producing and repositioning a replica is
no longer necessary and the inherent accuracy of the device is now the
major determinant. However, before considering modern devices it is
relevant to look at some of the original techniques employed using
profilometers in order to appreciate the progress made in this field of
dentistry.
17
1.4.1 Fundamentals of Metrology
In metrology accuracy is the degree to which a measurement of a quantity
conforms to a ‘true’ value of the quantity. For this reason it is sometimes
termed as ‘trueness’. Precision of measurement, defined by repeatability and
reproducibility, is the degree to which a quantity can be measured under
unchanged conditions and show the same results. A measurement system
can be accurate but not precise, precise but not accurate, but ideally is both.
1.4.2 Accuracy of Profilometry
As stated above, accuracy is equivalent to ‘trueness’, or how well what is
being measured matches a ‘true’ object. Most investigations into the
accuracy of profilometers used in dentistry pertain to the marginal fit of
prosthetic restorations (Brandestini et al. 1985, May et al. 1998, Denissen et
al. 1999, 2000, Groten et al. 1997, Tinschert et al. 2000). Most studies report
inaccuracy of fit to be between 50 to 75 μm, which is well within the range
of the 100 μm error advocated for clinical production (McLean 1971,
Karlsson 1993) and generally considered to be an acceptable result.
However, any conclusions drawn for these studies take into account errors
that may exist in the manufacturing process and as such are not directly
applicable to the present study.
Vlaar et al. (2006) note that an international standard exists for assessing
‘Digitizing quality’ of profilometers but that the test methods are laborious
and do not take into account the geometries and undercut measurements
encountered in scanning dental surfaces. The authors set up a study in order
to find a suitable artifact to serve as a dental standard. The method is the
18
same as that described in section 1.4.2.2 of this present study and the
authors found the accuracy of two digitizing systems to be “adequate” but
there is no comment made as to this method’s further use as a ‘dental
standard.’
Vlaar et al. (2006) and Persson et al. (2006) have both shown that accuracy
in dental profilometers depends on the density of the point cloud recorded.
This partly helps to explain why profilometers encounter differences when
recording areas with strong changes in curvature (Hewlett et al. 1992,
Rudolph et al. 2006). The other reason that a strong change of curvature
causes problems in measurement is given by the numerical aperture, as
described in section 1.2.4.
One of the only studies to consider precision (i.e. repeatability and
reproducibility) as well as accuracy of dental profilometers was conducted
by Persson et al. (2008). The authors investigated the precision of Procera,
which is a contact profilometer for the CAD/CAM of crowns and one of the
first commercial systems available. The aim was to determine the
reproducibility of digitized dental stone replicas compared to the master
model, and the reliability of computer-‐aided analysis. The reliability of
computer-‐aided analysis was expressed in terms of accuracy and precision.
Accuracy of measurement, which was the mean values of the discrepancies,
was shown to be between 0.2 and 0.8 μm. The repeatability coefficient for
the measurement method was shown to be between 7 and 16 μm, whereas
analysis of the stone replicas showed a repeatability coefficient of 19 to 26
μm. However it must be noted that only 6 measurements were taken, which
19
is well below the 30 measurements recommended by BS EN ISO 12836. The
authors felt that “the reliability of the computer evaluation method has
shown to be both accurate and precise.”
1.4.2.1 Reference Profilometer
The reference measurement system was a previously calibrated non-‐
contacting laser profilometer (Xyris 2000TL NCLP, Taicaan® Technologies-‐
Southampton, UK). This profilometer consists of a 785 nm wavelength laser
triangulation sensor which has a spot diameter of 30 μm a z resolution of 0.1
μm and an angular tolerance of 90°. The sensor was mounted onto a z stage
that allows vertical movement with a focal depth of 15 mm. The object to be
measured was placed underneath the sensor and an x and y stage was used
to scan backwards and forwards in a raster pattern whilst the data points
are being captured. The measurement control software was used to capture
a data point every 50 μm in the x and y direction and each scan of a tooth
took 45 minutes. The scanner therefore records 3-‐D data points that form a
character encoded (ASCII) point cloud data file which can be converted into
a polygon mesh.
The system has been previously calibrated (Rodriguez et al. 2012) and the
accuracy and repeatability were 1.3 μm and 1.6 μm respectively, at a step
over distance of 50 μm.
1.4.2.2 Test Device 1: 3Shape® Extra-‐oral Scanner
The 3Shape® extra-‐oral scanner has a red laser sensor and scans a dental
model as it rotates on a 360° spinning stage. Two charge-‐coupled device
20
cameras with 1.3 Mega Pixels capture the scan data over the course of 25 to
80 seconds and the point cloud data is then converted into a 3-‐D data format
for export as an .stl file. The stated accuracy of the system is 10 μm for
crowns and bridges (3Shape® Dental Systems Brochure, 2014). The
3Shape® extra-‐oral scanner is designed to scan gypsum models poured up
from impressions or the impression directly and does not require any
surface modification of the models or the impressions.
As mentioned above, Vlaar et al (2006) set up a study in order to find a value
for the measurement error of scanned dental surfaces and to try and find an
artifact to serve as a dental standard for profilometers. A sphere of known
radius was chosen because it “has, like a dental preparation, a continuously
changing surface and is therefore the perfect object to quantify the undercut
as a gauge of how far a scanner can measure steep walls and undercuts.” The
sphere was sprayed with fine titanium dioxide powder and scanned from 8
different angles by two different profilometers, one of which was a early
model of the 3Shape® extra-‐oral scanner. The recorded data was then
entered into software in order to calculate a ‘best fit’ sphere and compared
to the actual artifact of known dimension. Both machines showed
“adequate” accuracy (7.7 ± 0.8 μm and 13.9 ± 1.0 μm).
Sousa et al. (2012) set up a study to investigate accuracy and reproducibility
of three-‐dimensional digital model measurements. Again, an earlier model
of the 3Shape® extra-‐oral scanner was used to scan 20 dental casts. Fifteen
anatomical dental points were identified and 11 linear measurements made.
The digital models were analysed using software, while the casts were
21
analysed with calipers and then the two measurement modalities compared.
No statistical differences were found between the two measurement
systems but the authors consider linear measurements of digital models to
be more accurate and reproducible.
1.4.2.3 Intra-‐oral Scanners
The 3M™ True Definition intra-‐oral scanner is based on “active wavefront
sampling” technology and can capture 3-‐D images directly of teeth and
periodontal tissues in vivo (van der Meer et al. 2012). Light is emitted from a
source within the system and is transferred down a cable to a wand that has
similar dimensions to a dental handpiece. The wand is inserted into the
patient’s mouth with a stand-‐off distance between 5 and 20 mm. Before
scanning the surface needs to be lightly dusted with Lava Powder (3M™
ESPE, St. Paul, USA), which is a titanium oxide powder required in order to
provide an optically active surface for the registration of the 3-‐D patches
obtained during scanning. The 3-‐D positioning of the surface is recorded in a
live video feed format as the teeth are scanned in a ‘zigzag’ pattern across
the dental arch. The scanner captures twenty 3-‐D frames per second. During
the scanning procedure, patented software stitches the 3-‐D scans together
in real time to allow for continuous data capture up to a total scanning time
of seven minutes per arch. A post-‐scanning processing cycle recalculates the
registration and compensates for potential errors and the 3-‐D data is then
uploaded to 3M™ for processing into an .stl file that can then be accessed.
3M™ have not published any accuracy data for the digitizing of crown and
bridge shaped artifacts, however the smallest mean distance error of the
22
precursor to the True Definition scanner, the Lava COS was measured using
an implant bar model to be 2.2 μm (van der Meer et al. 2012).
Giménez et al. (2013) also investigated the 3M™ Lava COS scanner in order
to assess its accuracy in scanning dental implants. A master model
containing 6 implants was scanned with a contacting profilometer and this
data served as ‘true’ value. The authors found that measurements for
angulation and depth of implant did not differ significantly from ‘true’ value.
However, the experience of the operator was found to be a significant factor
and training for digital impression capture was advocated.
Measuring Tooth Wear
In a review of tooth wear indices Bardsley (2007) notes there is “both a
clinical and a scientific need to be able to measure tooth wear, and the
literature abounds with many methods which can be broadly divided into
quantitative and qualitative methods.” This review notes that qualitative
measurements can be valuable measurement tools but they are also
subjective and require appropriate training. In the general practice setting
this may present a problem where patients do not necessarily get continuity
in the dentist at the practice that they attend. Quantitative assessment relies
on objective physical measurement and in the case of tooth wear this may
be something like the size of a wear facet or the height of a crown. The
advantages of the quantitative measurement are that it is less subjective and
that wear can be measured over time, meaning an overall rate of wear may
be determined. The disadvantages in the past have largely been due to the
fact that impressions are required from which casts are produced and the
23
measurement taken; these study casts then also require storage. Typically
quantitative measurement has been recorded by looking at change in crown
height, but using profilometry and computer software it is now possible to
record a volumetric measurement.
1.4.3 Qualitative Measurement of Tooth Wear
There exist several indices that provide qualitative measurement of tooth
wear, mostly developed or modified from the Smith and Knight index
(1984). These are mostly qualitative and descriptive, and generally relate to
the involvement of dentine in the lesion. In most instances calibration and
training in the use of these indices is required. One of the most prevalent of
these is the Basic Erosive Wear Examination (Bartlett et al. 2008) This is a
partial scoring system recording the most severely affected surface in a
sextant and the cumulative score guides the management of the condition
for the practitioner. The four level score grades the appearance or severity
of wear on the teeth from no surface loss (0), initial loss of enamel surface
texture (1), distinct defect, hard tissue loss (dentine) less than 50% of the
surface area (2) or hard tissue loss more than 50% of the surface area (3).
While it is a useful screening tool it should be noted that a study by Ganss
and Lussi (2005) examined teeth both clinically and histologically for the
presence of exposed dentine and found that the correlation between the two
examinations was poor. It is this subjective nature of qualitative
measurement that necessitates the need for a simple, clinical method of
measuring tooth tissue loss.
24
1.4.4 Traditional Quantitative Measurement of Tooth Wear
Traditional metrological measurement of tooth wear has always required a
reference point. This is obviously challenging in the oral environment
because it is living tissue and is subject to change. Some of the methods
employed to overcome this problem include indentations cut into enamel
(Lambrechts 1984) and cementation of metal discs to less than 10% of a
tooth’s surface (Bartlett at al. 1997). Neither method can be considered
satisfactory for reasons of ethics, retention of the metal discs and
reproducibility. As previously described, Atkinson et al. (1982) made an
early attempt at quantitative measurement of wear in dental restorations
using laser dual source contouring using polyvinylsiloxane impressions to
provide information about the topology of the restorative surfaces pre-‐ and
post-‐test by contour mapping. This was a time consuming but innovative
attempt at employing the new technology.
Molnar et al. (1983) measured wear rate by using casts taken at intervals of
64 Aboriginal children (from the ages of seven and up) during a growth
study and then measuring the cusp heights of the first and second
permanent molars. Photos of casts were traced using electronic planimetric
methods that automatically recorded the size and location of wear facets. By
18 years of age an average of 0.5 mm of molar cusp height had been lost, a
wear rate of 0.41 μm per year. In general they found wear rates to be greater
than Europeans and put this difference in wear rate down to quantity of
dietary abrasives.
25
Glentworth et al. (1984) used a 147Pm β particle backscatter instrument to
measure changes in surface profiles of dental restorations due to wear. They
found this instrument to be capable of measuring changes of the order of 15
μm in the profile of irregularly shaped surfaces.
Lambrechts et al. (1989) carried out a quantitative in vivo study of wear in
human enamel. Twenty-‐one subjects were selected with the inclusion
criteria being possession of a complete dentition and ‘normal’ occlusion. The
mean age of the subjects was 20 years and there was no gender segregation.
Polyvinylsiloxane impressions were taken of molars and premolars at
baseline, 6, 12, 18, 24, 36 and 48 months and then these were converted into
accurate positive replicas using a copper plating technique. Intraoral
photographs, articulation paper and stereomicroscopic evaluation of the
replicas were used to identify attrition sites and the maximum loss of
substance at these sites was then measured using a computerised three-‐
dimensional measuring microscope. Forty-‐eight occlusal contact areas on
premolars and 49 occlusal contact areas on molars were measured and the
means and standard deviations of vertical loss due to wear determined.
After four years the total enamel wear was 153 μm on molars and 88 μm on
premolars. This translated to a steady wear rate of about 29 μm per year for
molars and about 15 μm per year for premolars. The advantage of the
copper plating technique was that it removed the significant variation in
thickness caused by applying a surface coating (e.g. gold leaf) to an already
formed replica. The disadvantages of electroplating are the need for
specialised equipment and the time taken for the electroplating process.
26
1.4.5 Profilometry and Tribology Studies
In a study into using mapping apparatus for measuring tooth wear over time
Chadwick et al. (1995) noted, “The subjective ranking scales hitherto
employed in [such] epidemiological studies are insufficiently sensitive to
detect small amounts of tooth wear that, in themselves, may be of little
significance but cumulatively may result in significant loss of tooth surface.
The ability to detect such increments would be of value when clinically
following up patients with tooth wear.” The present study aims to eliminate
this subjectivity by investigating the ability of dental profilometers to
provide an accurate volumetric measurement of tooth substance loss.
Indeed the use of profilometry is not a particularly new concept. As far back
as the early 1990’s Noordmans et al. (1991) were able to use computer-‐
aided profilometry to assess the abrasive wear of human enamel and
dentine. Freshly extracted incisors were prepared and scanned using a
contact profilometer (Perthometer C5D, Perthen GmbH) to give a baseline
reading of surface roughness. These samples were then brushed over a
period of time, both in vivo and in vitro. Measurements were taken every 7
days for 7 weeks. In vivo wear rates in the experiment were 0.2 to 3.0 μm
per week for enamel, depending on the toothpaste used and the subject. For
dentine these values were 4.0 to 35.0 μm per week. Attin et al. (2001)
performed a similar in situ study in order to assess the susceptibility of
previously demineralised enamel to tooth brushing action. Enamel samples
were analysed using a laser profilometer and mean (standard deviation)
wear of the samples was found to be between 0.66 ± 1.11 μm and 6.78 ±
27
2.71 μm depending on the time between the demineralization and the tooth
brushing. The authors were able to conclude from this that at least 60
minutes should pass before tooth brushing after presenting teeth with an
erosive challenge.
In another study, Bartlett et al. (1997) cemented metal discs to the palatal
tooth surface of 20 patients (13 with unexplained palatal erosion and 7
controls without evidence of tooth wear) in order to act as reference areas.
Wear was then estimated by taking impressions at 6 month intervals and
scanning them with a contacting profilometer. A statistically significant
difference between the two groups of patients was found, with patients in
the tooth wear category showing a median 36.5 μm of wear over 6 months
in comparison to a median of 3.7 μm in the control group. Two follow up
studies have been carried out (Azzopardi et al. 2001, Sundaram et al. 2007)
in which teeth were coated with resin-‐based dentine bonding agent to see if
it provided any protection from erosive and/or abrasive tooth wear.
Impressions were taken and scanned using a laser profilometer, and were
able to show a statistical difference between the rate of wear in the control
group and those protected by dentine bonding agent. This use of
profilometry demonstrated potential for dentine bonding agents to provide
up to 3 months of protection from tooth wear. In their study into the
prevention of erosion and abrasion Azzopardi et al. (2001) note in the
discussion, “Digital terrain modelling, which relies on the premise that acid
does not affect the whole area under investigation equally, also shows
particular promise.”
28
The reference profilometer used in the present study was a non-‐contacting
laser profilometer (NCLP-‐Taicaan® Technologies-‐Southampton) that has
been used in previous studies by Rodriguez et al. (2009, 2010). In the
former study the same profilometer was used to measure surface accuracy
of impression materials and dental stones. The system works by using a
triangulation laser sensor that detects the deflection of a laser spot on a
charge coupled device camera. This NCLP has a 785nm wavelength laser
triangulation sensor with a spot diameter of 30 μm and an axis and sensor
resolution of 0.1 μm. Its accuracy in measuring surface roughness was
tested by scanning an impression made of a 6 μm roughness standard
(Taylor Hobson-‐Reference Specimen Type 112/1534). The mean and
standard deviation of the roughness value from this impression of the 6 μm
roughness standard was found to be 5.99 μm ± 0.29, a mean difference of
0.01 μm, indicating excellent accuracy in recording surface roughness. The
authors do note, “the NCLP was capable of detecting vertical features less
than the laser spot diameter because the vertical resolution of the sensor
was 0.01 μm.” In a later study the accuracy of measurements of tooth wear
by the same NCLP, in combination with surface matching software was
assessed. Accuracy and repeatability were assessed by repeatedly scanning
a calibrated 25 mm engineering steel gauge block. Scanning titanium
frustums of varying volumes made volumetric assessments possible.
Accuracy and repeatability of the systems in measuring step height and
volume after surface matching were measured using a custom model with
cemented engineering slip gauges and cemented onlays of super-‐plastically
formed titanium. The accuracy and repeatability were 1.3 μm and 1.6 μm in
29
measuring length and the system was accurate for volumetric measurement
with coefficients of variation <5%. It is this accuracy of volumetric
measurement that can potentially be applied to measurement of tooth
substance loss in cases of tooth wear.
The same authors (Rodriguez et al. 2012) carried out an in vivo
measurement of tooth wear of 63 patients. Maximum follow up time was 12
months for only 30 of the patients but all 63 had a maximum follow up time
of 6 months. A questionnaire was also used in order to assess tooth wear
risk factors in the participants and silicone impressions were taken of the
patients at baseline and subsequently every 6 months. The impressions
were poured in type IV gypsum and scanned using the same reference
profilometer being used in the present study. Images were then
superimposed using computer software in order to assess the amount of
tooth wear in each subject. Measurement error was stated as 15 μm. Of the
1078 teeth measured only 72.2% of showed wear <15 μm over a 6 month
period, while of the 63 patients participating 77.7% showed a median tooth
wear <15 μm. There was a statistical trend associated with gastric risk
factors.
Three-‐dimensional measurement of tooth wear was previously described by
Mehl et al. 1997 where the authors investigated the accuracy, with and
without referenced positioning, of a 3-‐D optical scanner and reference free
automated superimposition software. Crucially they were able to show that
accuracy depends on surface inclination of the object being scanned, as per
the limitation of numerical aperture. Up to an angle of 60 degrees the
30
precision was better than 3 μm and the accuracy better than 6 μm.
However, the method described does assume that the three-‐dimensional
calculations made by the software are perfectly accurate which may not
have been the case, and in addition no actual volumetric measurement was
described.
Pintado et al. (1997) demonstrated annual tooth wear rates in a group of 18
dental students to be 0.04 mm3. This was assessed over two years by taking
polyvinyl silicone impressions, making epoxy resin models and then
scanning them with a contacting profilometer. They also found that for all
angles less than 60° the accuracy was 7 μm and the precision was 5 μm, in
close agreement to Mehl. A more recent study by Tantbirojn et al. (2012)
looked at 12 patients with gastro-‐esophageal reflux disease (GERD) and 6
control subjects. Impressions were taken at baseline and at 6 months, cast in
dental stone and scanned with an optical scanner. The mean (standard
deviation) volume loss per tooth in the participants was found to be
significantly higher than that in control participants: 0.18 ± 0.12 mm3 versus
0.06 ± 0.03 mm3. This measurement was calculated by overlapping scans
using computer software, a technique that the authors provide a mean
(standard deviation) accuracy of 0.006 ± 0.001 mm3.
Currently in dental literature there exist no studies that investigate
volumetric measurement of tooth wear using an intra-‐oral scanner. With the
an increasing plethora of digital scanners now available to the dental
community, there is a need for greater understanding of the capabilities of
31
these systems for both diagnostic and treatment purposes, all of which rely
of the fundamental concept of accuracy of measurement.
32
Aims and Objectives
2.1 Aims
The overall aim was to investigate the accuracy of intra-‐oral and laboratory
profilometers for the measurement of tooth wear.
The investigation was comprised of three individual experiments with the
following specific aims:
1. To determine the resolution of the digitizing devices at measuring
objects of known dimensions.
2. To assess the reproducibility, repeatability and trueness of
measurement of the digitizing devices, with comparison to a
reference measurement system.
3. To compare the performance of the digitizing devices using a
previously validated profilometric tooth wear measurement
technique, using an in vitro calibration model.
2.2 Objectives
1. To measure engineering slip gauges of known dimensions in order to
determine the minimum resolution of the digitizing devices, in
comparison to a calibrated triangulation laser profilometer.
2. To determine the reproducibility, repeatability and trueness of the
digitizing devices in the measurement of an inlay-‐shaped artifact and
a crown-‐and-‐bridge-‐shaped artifact, in comparison to a calibrated
triangulation laser profilometer.
33
3. To determine ‘proof of concept’ for the accuracy of the digitizing
devices in the measurement of calibration models previously used to
evaluate a method of profilometric tooth wear measurement, in
comparison to a calibrated triangulation laser profilometer.
34
Null Hypotheses
The digitizing devices will not be able to measure the engineering slip
gauges.
There is no difference in the accuracy of measurement between the
digitizing devices and the triangulation laser profilometer.
There is no difference in the capabilities of the digitizing devices and the
triangulation laser profilometer for the measurement of calibration models
used to evaluate a profilometric tooth wear measurement method.
35
Materials and Methods
Preliminary discussions with the Freeform Measurement Centre at the
National Physical Laboratory were entered into regarding the procedures
required for fully following the measurement protocol specified by BS EN
ISO 12836 (2012). However, during these discussions it became apparent
that the cost of fabricating and calibrating the artifacts required would be
extremely costly and moreover the dimensions of the specified artifacts
were much greater than that would be likely to be seen in a natural human
dentition.
There are many different protocols currently existing for the assessment of
accuracy of intra-‐oral scanners, many of which are based on the
measurement of a full arch implant model with 6 implants evenly
distributed across the arch (van der Meer et al. 2012). This model has its
merits but for the measurement of tooth wear more local accuracy is
required and therefore the ISO bridge and inlay specimen (BS EN ISO
12836:2012, 2012) and the tooth wear calibration model (Rodriguez et al.
2012) have more relevance and so were employed here.
36
3.1 Test Digitizing Devices
The test digitizing devices investigated in this study were the 3Shape® extra-‐
oral scanner (D700, 3Shape® Copenhagen, Denmark) and the 3M™ True
Definition intra-‐oral scanner (3M™ True Definition intra-‐oral scanner, 3M™
ESPE® St. Paul, MN, USA).
3.2 Test Conditions for Measurement
The specific test conditions for measurement were carefully controlled,
including monitoring of the change in temperature during the test to ensure
that it remained within ±1oC, and this was measured using an EL-‐USB-‐2 data
logger (Lascar Electronics® -‐ Salisbury, UK). The ambient room temperature
was maintained at 23 ± 2 °C and the quality of the data set in terms of
missing or corrupted data were continuously evaluated and in the case of
missing or corrupted data the test was repeated.
3.3 Measurement Software
All measurements were carried out using Geomagic® Qualify surface
matching software (Geomagic® Qualify 11 – Geomagic® Incorporated, North
Carolina, USA), following measurement workflows as defined below for each
measurement specimen.
37
3.4 Specimen Preparation
Three types of artifacts were prepared for measurement using the digitizing
devices.
3.5 Engineering Slip Gauge Specimen
Ten engineering slip gauges (Laser Tools®, Southampton, UK) of varying
thicknesses from 50 μm to 800 μm were selected in order to determine the
smallest possible item that could be measured.
In order for the dental digitizing devices to be able to scan the data it was
necessary to mount the gauges in a base that was shaped like a dental arch,
as the scanning devices were designed to recognised dental jaw shapes and
initial scanning failures had identified this as an issue when scanning a free
standing object that was not tooth shaped.
In order to make the model as clinically relevant as possible, thirteen human
teeth were collected according to research ethics (REC reference:
12/LO/1836) and the teeth were then set up in Moonstone™ (Bracon Ltd.,
Etchingham, England) in a die tray (Sterdo Split model tray, Zirc Company,
Buffalo, MN). Condensation cured laboratory putty (Zetalabor®, Zhermack,
Rovigo, Italy) was used to replicate the periodontal tissues with the putty
trimmed to the cemento-‐enamel junction around all the extracted teeth. This
therefore simulated a partially dentate mandibular human arch with only
the lower right first molar missing, as shown in Figure 1 below.
38
Figure 1 -‐ Extracted teeth set up to simulate a partially dentate mandibular arch
The slip gauges were then mounted individually between the teeth and were
fixed in place with laboratory putty. As the surface of the slip gauges was a
shiny metal, in order for all scanners to be able to scan the gauges it was
first necessary to apply a thin coating of 50 nm Telescan carbon coating
(DFS® Diamon GbmH – Riedenburg, Germany). In order to control film
thickness the gauges were sprayed from a distance of 30 cm for no longer
than 2 seconds.
Each thickness of slip gauge was then scanned with the three scanners
following measurement protocols defined. The scan data was then imported
into Geomagic® Qualify 11 for measurement of the thickness of the edge of
the slip gauges.
39
For the measurement of the slip gauges the measurement work flow was as
follows. The point cloud data was converted into a polygon mesh of the area
of the slip gauge and the surrounding teeth as seen in Figure 2 below.
Figure 2 -‐ Digital model with slip gauge in situ
The scan was cleaned up such that only the scan data from the top edge of
the slip gauge alone was considered. This resulted in an image as shown in
Figure 3 below.
Figure 3 -‐ Digital model of a slip gauge thickness
40
In order to ensure that the thickness of the slip gauges was measured in the
same plane of orientation for the three measurement devices, a three-‐step
process was carried out within Geomagic® Qualify. Firstly a best-‐fit
alignment was carried out in order to ensure that the scans of the slip
gauges were all orientated in the same 3-‐D space. Secondly a cross section of
the scans was made using a plane that was identical for all the slip gauges as
shown in Figure 4 below.
Figure 4 -‐ Geomagic® software being used to create a 2-‐D outline of a slip gauge thickness
This created a 2-‐D outline of the identical part of the slip gauge for all three
measurement devices. The final part of the measurement was to carry out a
measurement of the 2D dimensions of the parallel-‐sided walls of the slip
gauge as shown in Figure 5 below.
41
Figure 5 -‐ Measurement of the 2-‐D outline of a slip gauge thickness
The mean and standard deviation of the 30 measurements was then
calculated for the three digitizing devices.
3.6 Inlay shaped Specimen and Bridge Shaped Specimen
The measurement protocol specified in ISO standard 12836 publication
‘Dentistry — Digitizing devices for CAD/CAM systems for indirect dental
restorations — Test methods for assessing accuracy’ was used to measure an
inlay shaped specimen and a bridge shaped specimen prepared from human
teeth that had been mounted in a simulation of an mandibular jaw as
described above. The natural teeth were restored thus providing more
clinically relevant artifacts than those specified in the ISO standard, which
were not of similar dimensions to natural teeth. The teeth were prepared to
provide clinically relevant inlay shaped specimens and a bridge shaped
specimen consisting both of natural tooth tissue and artificial restorative
materials thus providing a clinically relevant range of materials with their
varying optical surface properties.
42
To prepare the teeth, a truncated cone shaped diamond bur with a medium
grit and a head diameter of 2.0 mm (Hi-‐Di No.625, Dentsply® Ash
Instruments, UK) was inserted into the shank of a milling machine (PFG 100,
Cendres & Metaux S.A, Bienne, Switzerland). The lower left second molar
was prepared for an inlay-‐shaped cavity, roughly following the shape
specified in the ISO standard. This is shown below in Figure 6.
Figure 6 – Photograph of the inlay shaped preparation
Figure 7 below shows a 3D comparison of the inlay shape before and after
preparation showing the amount of tooth tissue that was removed. Red
equals the most tissue removed and green equals no tissue removed.
43
Figure 7 – 3D comparison of the shape of the inlay shape preparation before and after
preparation showing the amount of tooth tissue that was removed for the preparation (red
equals the most tissue removed and green equals no tissue removed)
The three-‐unit fixed-‐fixed bridge preparation was carried out following
standard preparation guidelines using the lower right second premolar and
the lower right second molar (with the lower right first molar missing) as
shown in Figure 8 below.
44
Figure 8 -‐ Bridge specimen
Again, a thin coating of Telescan (DFS® Diamon GbmH – Riedenburg,
Germany) was applied prior to scanning and then the models were scanned
with a similar scanning technique as previously described to produce 3-‐D
images as shown in the Figure 9 and Figure 10 below.
45
Figure 9 -‐ 3-‐D digital model of inlay specimen
Figure 10 -‐ 3-‐D model of bridge specimen
Following the ISO standard protocol, the repeatability, reproducibility and
trueness of measurement of the height b, in mm, of the preparations, and the
angle α, in °, of the taper of opposing walls of the preparation were
quantified as described below. The ISO standard specifies the measurement
protocol to quantify the height and taper of the inlay specimen and the
bridge specimen and recommends the use of surface analysis software such
46
as Geomagic® Qualify to carry out the analyses.
3.6.1.1 Height and Taper of Inlay Specimen
As shown in Figure 11 the angle α and a height b of the inlay shaped cavity
were measured using Geomagic® Qualify. The same workflow as described
above for measuring the thickness of the slip gauges was used but this time
the height and taper of the preparation was quantified.
Figure 11 Three primary views of the inlay-‐shaped artifact as specified in the ISO standard (BS
EN ISO 12836:2012, 2012)
3.6.1.2 Height and Taper of Bridge Specimen
As shown in Figure 12, the angle α and a height b of the bridge shaped cavity
was measured using Geomagic® Qualify.
47
Figure 12 Views of the bridge-‐shaped artifact as specified in the ISO standard (BS EN ISO
12836:2012, 2012)
Following scanning of the bridge preparations, height and taper was again
measured using the workflow described for measuring the slip gauges. A
screen grab of this process can be seen in Figure 13 below.
48
Figure 13 -‐ Height b and angle α being measured for digital model of bridge specimen
In order to quantify the accuracy of the digitizing devices at measuring the
inlay specimen and the bridge specimen the repeatability, reproducibility
and trueness of measurement were calculated as described below.
3.6.1.3 Repeatability
Repeatability is defined as the closeness of the agreement between the
results of successive measurements of the same measurement and carried
out under the same conditions of measurement (Leach, 2014). This is a
qualitative concept that can, however, be quantified by calculating the mean
and standard deviation of the measurements, and the standard deviation is
then expressed as the repeatability of measurement.
For the purposes of this investigation the repeatability conditions were
thirty individual measurements obtained with the same measurement
procedure in the same laboratory by the same operator (T.E.) using the
same equipment. For the laser profilometer, the measurement control
software was used to carry out consecutive measurements, without
49
removing the specimens from the digitizing device. For the 3Shape® extra-‐
oral scanner the measurements were carried out within a short space of
time, again without removing the specimen from the device. For the 3M™
True Definition intra-‐oral scanner the measurements were carried out
within a short space of time with the specimen held in the same position on
the bench top.
3.6.1.4 Reproducibility
Reproducibility is defined as the closeness of the agreement between the
results of measurements of the same measure and carried out under
changed conditions of measurement. The changed conditions may include
the observer, measuring instrument, location and time. (Leach, 2014). As
with repeatability, this is a qualitative concept that can be quantified by
calculating the mean and standard deviation of the measurements and the
standard deviation is then expressed as the reproducibility of measurement.
For the purposes of this investigation the reproducibility conditions were 30
measurements obtained with the same measurement procedure in the same
laboratory by the same operator (T.E.) using the same equipment as above,
however this for the reproducibility measurement the specimens were
removed from the measurement device and repositioned in the digitizing
device before each new measurement.
3.6.1.5 Trueness
Trueness is defined as the closeness of agreement between the mean
obtained from repeated measurements and a true value or a conventional
true value (Leach, 2014). As with the concepts above, trueness is a
50
qualitative concept however it can be expressed by calculating the
systematic error of a measurement system.
For the purposes of this investigation, trueness was measured by calculating
the difference between the mean of the thirty repeatability measurements of
the test digitizing devices and the mean of the thirty repeatability
measurements of the reference device.
3.7 ‘Proof of Concept’ of Using the 3Shape® Extra-‐oral Scanner and the
3M™ True Definition Intra-‐oral Scanner to Follow a Profilometric
Tooth Wear Measurement Technique
As a ‘proof of concept’ investigation, a previously constructed calibration
model used to simulate tooth wear was scanned using the test digitizing
devices to create data sets of the calibration models. Rodriguez et al. (2012)
fabricated the model using type IV dental stone (MoonstoneTM Bracon Ltd.,
Etchingham, England), which had involved the use of superplastically
formed Titanium-‐64 alloy onlays of known step height being cemented onto
the occlusal/palatal surfaces of the UR5, UR6, UL5 and the palatal surface of
UL2. When in place these additions represented a ‘before’ wear state and
another MoonstoneTM cast of the original model without these additions
represented an ‘after’ wear state.
For the scanning with the two digitizing sytems being tested the casts were
again coated with Telescan carbon powder (DFS® Diamon GbmH –
Riedenburg, Germany) and scanned as described above. The description of
the measurement of the occlusal/palatal onlays for profilometric tooth wear
51
measurement technique (step height) has been fully described by Rodriguez
et al. however Figure 14 and Figure 15 below illustrate how this
measurement was carried out.
Figure 14 -‐ Geomagic® software being used to create a 2-‐D outline of the calibration model and
its onlays
Figure 15 -‐ Geomagic® software being used to analyze calibration model volume
In order to quantify the accuracy of the 3Shape® extra-‐oral scanner and the
3M™ True Definition intra oral scanner for measurement of this calibration
52
model the step height data from the onlays, as quantified by the test devices,
was compared to the true known step height of the onlay as described by
Rodriguez et al. (2012).
53
3.8 Statistics
Data were exported to an Excel spread sheet (Microsoft® Office Excel® 2010,
Microsoft® Corporation, USA) and statistical analyses were performed using
GraphPad Prism statistical software (GraphPad Prism version 6.00 for
Windows, GraphPad Software, La Jolla California USA, www.graphpad.com)
using the GraphPad Statistics Guide to guide the choice of analysis
(GraphPad Software, 2013).
For the comparison of the resolution of measurement a Bland-‐Altman plot
was used to graphing the comparison of measurement techniques by
calculating the difference between the test measurements and the true
values. These differences were then described descriptively.
In order to compare the reproducibility and repeatability of the 3M™ True
Definition intra-‐oral scanner and the 3 Shape® extra-‐oral scanner with the
reference profilometer, the F-‐test of the equality of two variances was
carried out using Excel. Firstly, the normality of the data were tested with
the D'Agostino & Pearson omnibus normality test using GraphPad Prism
statistical software. The data were found to be normally distributed and
were therefore expressed as means and standard deviations. Secondly, in
order to compare the variance data of the test scanners in comparison to the
reference scanner, the F-‐test of the equality of two variances was carried out
with p<0.05 used to infer any statistically significant differences.
Finally, unpaired t-‐tests were carried out in order to compare the trueness
(height b and angle α) of the 3M™ True Definition intra-‐oral scanner in
comparison to the 3 Shape® extra-‐oral scanner. Statistical significance was
54
determined with p<0.05 and height and angle measurement data were
analysed individually, without assuming a consistent standard deviation of
the sampled population data.
As ‘proof of concept’ of wear measurement was carried out using a single
measurement no statistical comparisons were required for this part of the
study. .
55
Results
4.1 Measurement of Engineering Slip Gauges
Table 1 Mean (SD) results of the measurement of slip gauges using the test and reference
measurement devices (n=30)
Thickness of slip gauge (µm)
50 100 150 200 300 400 500 600 700 800
Mean (SD) Reference
Profilometer measurement
(n=30)
NM 198 (34)
172 (21)
252 (14)
346 (18)
420 (5)
513(4)
608 (4)
712 (5)
818 (6)
Mean (SD) 3Shape® extra-‐oral scanner measurement
(n=30)
NM NM NM 660 (110)
433 (120)
445 (13)
596 (26)
635 (18)
701 (13)
815 (14)
Mean (SD) 3M™ True Definition
intra-‐oral scanner
measurement (n=30)
NM NM NM 440 (142)
460 (127)
491 (43)
540 (12)
660 (19)
734 (21)
822 (16)
Table 1 Mean (SD) results of the measurement of slip gauges using the test
and reference measurement devices (n=30). It was clear that none of the
measurement devices were accurate when measuring the width of a slip
gauges below 400 µm. The reference profilometer was able to obtain the
most readings and would appear to be the most accurate as well. The 3M™
True Definition intra-‐oral scanner was not able to obtain any readings below
200 µm and was not particularly accurate below 500 µm. The 3Shape®
extra-‐oral scanner was not able to provide quantifiable readings for either
50 or 100 µm, while the scan data it provided below 400 µm was not close to
the ‘true’ value.
56
Figure 16 Bland-‐Altman plot of the agreement between the three measurement systems at the
measurement of engineering slip gauges of increasing dimensions
The Bland-‐Altman plot shows that there is a clear trend for a smaller
difference between the methods as the dimensions of the slip gauges
increases. As the thickness of the slip gauges increased the agreement also
increased, such that at the largest thickness the limits of agreement were
very narrow and from 700 µm onwards the measurement methods were
essentially equivalent. However, the limits of agreement were seen to be
very wide at the lower limits of the dimensions of the slip gauges with a
threshold level seemingly around a dimension of 400 µm.
0 2 0 0 4 0 0 6 0 0 8 0 0 1 0 0 00
2 0 0
4 0 0
6 0 0
8 0 0
1 0 0 0
T ru e d im e n s io n o f s lip g u a g e (mm )
Measu
red valu
e (mm
)
R e fe re n ce p ro filom e te r
3 S h a p e® e x tra -‐o ra l s c a n n e r
T ru e D e fin it io n ™ in tr a -‐o ra l s c a n n e r
57
4.2 Repeatability, Reproducibility and Trueness of Measurement of
the Inlay Shaped Specimen and the Bridge Shaped Specimen
4.2.1 Repeatability Measurement Results
4.2.1.1 Inlay Specimen (Height and Taper)
Table 2 Repeatability results of the measurements of the height b (mm) and angle α (°) of the
inlay specimen
Repeatability of reference data (Reference
profilometer)
Repeatability of test data (3Shape® extra-‐
oral scanner)
Repeatability of test data (3M™ True
Definition intra-‐oral scanner)
Mean (SD) Height b (mm)
1.767 (0.009) 1.753 (0.019)* 1.775 (0.014)*
Mean (SD) Angle α (°)
17.484 (0.199) 17.822 (0.288)* 18.572 (0.294)*
* Indicates statistically significant differences between the SD of the test digitizing devices vs. the reference device (p <0.05)
Table 2 Repeatability results of the measurements of the height b (mm) and
angle α (°) of the inlay specimen (n=30). As specified in the ISO standard (BS
EN ISO 12836:2012, 2012) the repeatability of measurement is expressed as
the standard deviation therefore the repeatability of height b measurement
of the reference profilometer was 9 µm, of the 3Shape® extra-‐oral scanner
was 19 µm and of the 3M™ True Definition intra-‐oral scanner was 14 µm.
Repeatability of the devices with regards to angle α measurement was
0.199°, 0.288° and 0.294° respectively.
Statistical testing using the F-‐test showed the variance of the test data was
statistically significantly increased in comparison to the reference data
(P<0.05), which therefore suggested that the extra-‐ and intra-‐oral scanners
showed poorer repeatability at measuring the height and angle of the inlay
specimen than the reference profilometer.
58
4.2.1.2 Bridge Specimen (Height and Taper)
Table 3 Mean (SD) Repeatability results of the measurements of the height b (mm) and angle α
(°) of the bridge specimen
Repeatability of reference data (Reference
profilometer)
Repeatability of test data (3Shape® extra-‐
oral scanner)
Repeatability of test data (3M™ True Definition intra-‐
oral scanner)
Mean (SD) Height b (mm)
2.659 (0.005) 2.599 (0.012) * 2.754 (0.027) *
Mean (SD) Angle α (°)
9.292 (0.170) 9.980 (0.413) * 10.192 (0.305) *
* Indicates statistically significant differences between the SD of the test digitizing devices vs. the reference device (p <0.05)
Table 3 Mean (SD) Repeatability results of the measurements of the height b
(mm) and angle α (°) of the bridge specimen (n=30). Again, the repeatability
of measurement is expressed as the standard deviation so the repeatability
of height b of the reference profilometer was 5 μm, of the 3Shape® extra-‐
oral scanner was 12 μm and of the 3M™ True Definition intra-‐oral scanner
was 27 μm. Repeatability of the devices with regards to angle α
measurement was 0.170°, 0.413° and 0.305° respectively.
Statistical testing using the F-‐test showed the variance of the test data was
statistically significantly increased in comparison to the reference data
(P<0.05), which therefore suggested that the extra-‐ and intra-‐oral scanners
showed poorer repeatability at measuring the height and angle of the bridge
specimen than the reference profilometer.
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4.2.2 Reproducibility of the Measurement
4.2.2.1 Inlay Specimen (Height and Taper)
Table 4 Mean (SD) Reproducibility results of the measurements of the height b (mm) and angle
α (°) of the inlay specimen
Reproducibility of reference data (Reference
profilometer)
Reproducibility of test data (3Shape® extra-‐
oral scanner)
Reproducibility of test data (3M™ True Definition intra-‐
oral scanner)
Mean (SD) Height b (mm)
1.755 (0.027) 1.757 (0.047) * 1.780 (0.061) *
Mean (SD) Angle α (°) 17.441 (0.409) 17.947 (0.654) * 18.006 (0.580) *
* Indicates statistically significant differences between the SD of the test digitizing devices vs. the reference device (p <0.05)
Table 4 Mean (SD) Reproducibility results of the measurements of the
height b (mm) and angle α (°) of the inlay specimen. The reproducibility of
the reference profilometer with regards to mean height b of was 27 μm,
whereas the 3Shape® extra-‐oral scanner and the 3M™ True Definition intra-‐
oral scanner had a reproducibility of 47 μm and 61 μm respectively. The
reproducibility of angle α measurement for the reference scanner was
0.409°, for the 3Shape® extra-‐oral scanner was 0.654° and for the 3M™ True
Definition intra-‐oral scanner was 0.580°.
Statistical testing using the F-‐test showed the variance of the test data was
statistically significantly increased in comparison to the reference data
(P<0.05), which therefore suggested that the extra-‐ and intra-‐oral scanners
showed poorer reproducibility at measuring the height and angle of the
inlay specimen than the reference profilometer.
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4.2.2.2 Bridge Specimen (Height and Taper)
Table 5 Mean (SD) Reproducibility results of the measurements of the height b (mm) and angle
α (°) of the bridge specimen
Reproducibility of reference data (Reference
profilometer)
Reproducibility of test data (3Shape® extra-‐
oral scanner)
Reproducibility of test data (3M™ True Definition intra-‐
oral scanner)
Mean (SD) Height b (mm)
2.669 (0.021) 2.657 (0.020) * 2.768 (0.051) *
Mean (SD) Angle α (°)
9.271 (0.311) 9.426 (0.582) * 9.909 (0.403) *
* indicate statistically significant differences between the SD of the test digitizing devices vs. the reference device (p <0.05)
Table 5 Mean (SD) Reproducibility results of the measurements of the
height b (mm) and angle α (°) of the bridge specimen. When looking at
reproducibility of height b measurement of the reference profilometer the
value was 21 μm, which was similar to the 3Shape® extra-‐oral scanner’s
reproducibility of 20 μm but statistically different. The reproducibility of
height b measurement the 3M™ True Definition intra-‐oral scanner was
recorded as 51 μm. The reference profilometer was again most reproducible
for measurement of the angle α with a standard deviation of 0.311°. The
3Shape® extra-‐oral scanner and 3M™ True Definition intra-‐oral scanner
showed a reproducibility of 0.582° and 0.403° respectively.
Statistical testing using the F-‐test showed the variance of the test data was
statistically significantly increased in comparison to the reference data
(P<0.05), which therefore suggested that the extra-‐ and intra-‐oral scanners
showed poorer reproducibility at measuring the height and angle of the
bridge specimen than the reference profilometer..
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4.2.3 Trueness of the Measurement
Table 6 Mean (SD) trueness of the test data from the measurement of the height b (µm) of the
inlay specimen and the bridge specimen using the 3Shape® extra-‐oral scanner and the 3M™
True Definition intra-‐oral scanner
Trueness of test data from the 3Shape® extra-‐oral scanner
Trueness of test data from the 3M™ True Definition intra-‐oral scanner in comparison to the
reference profilometer Height b (µm) of the
inlay specimen -‐14.2 7.6
Height b (µm) of the bridge specimen
-‐68.8 94.8
Mean (SD) -‐41.5 (38.61) ns
51.2 (61.66) ns
Table 7 Mean (SD) trueness of the test data from the measurement of the angle α (°) of the
inlay specimen and the bridge specimen using the 3Shape® extra-‐oral scanner and the 3M™
True Definition intra-‐oral scanner in comparison to the reference profilometer
Trueness of test data (3Shape® extra-‐oral scanner)
Trueness of test data (3M™ True Definition intra-‐oral scanner)
Angle α (°) inlay specimen 0.338 1.087
Angle α (°) bridge specimen 0.688 0.900
Mean (SD) 0.51 (0.25) ns
0.99 (0.13) ns
Table 6 Mean (SD) trueness of the test data from the measurement of the
height b (µm) of the inlay specimen and the bridge specimen using the
3Shape® extra-‐oral scanner and the 3M™ True Definition intra-‐oral scanner
Although these results suggest that there was a trend for the 3Shape® extra-‐
oral scanner to underestimate the true value of the height and angle of the
specimens in comparison to the 3M™ True Definition intra-‐oral scanner,
which showed a trend of overestimating these dimensions, this was not
62
statistically significant. Further to this, these results also demonstrate that
the variability of the trueness of the angle test data was less for the 3M™
True Definition intra-‐oral scanner than the 3Shape® extra-‐oral scanner,
which may suggest that the angular tolerance of the 3M™ True Definition
intra-‐oral scanner may be more consistent.
63
4.3 ‘Proof of Concept’ of Using the 3Shape® Extra-‐oral Scanner and the
3M™ True Definition Intra-‐oral Scanner to Follow a Profilometric
Tooth Wear Measurement Technique
Figure 17 – Volume of ‘tooth tissue loss’ demonstrated using Geomagic® best fit analysis
As shown in Figure 17 above, a heat map of ‘tooth tissue loss’ was generated
using Geomagic® Qualify. The blue areas designate where there has been
loss height when comparing the model without onlays to the model with
onlays. The darker the blue, the more ‘tissue loss’ has occurred.
Table 8 Results of the volumetric measurement of the calibration model
Reference profilometer
3Shape® extra-‐oral scanner
True Definition™ intra-‐oral scanner
Volume data (mm3)
Volume data (mm3)
Volume error (mm3)
Volume data (mm3)
Volume error (mm3)
UR5 8.6 8.5 -‐0.1 8.7 0.1
UR6 18 18.1 0.1 18.2 0.2
UL2 12.7 12.3 -‐0.4 12.9 0.2
UL5 11 10.5 -‐0.5 10.9 0.3 Mean (SD) volume error (mm3) -‐0.2 (0.3) 0.2 (0.1)
64
Table 8 Results of the volumetric measurement of the calibration model.
Both the 3Shape® extra-‐oral scanner and the 3M™ True Definition intra-‐oral
scanner show a mean volume variation from the reference volume of ± 0.2
mm3. However the 3Shape® extra-‐oral scanner tended to underestimate the
volume, while the 3M™ True Definition intraoral scanner tended to
overestimate the volume.
65
Discussion
As can be seen in the Bland and Altman plot (Figure 16 above), all three
devices show good correlation in their ability to measure slip gauge
thicknesses of 400 μm and above. The Bland and Altman plot was chosen to
display the data because it is the most appropriate statistical analysis to use
when needing to compare two or more measurements that each contains
some errors in their measurement. Essentially the Bland and Altman plot
allows these measurements to be evaluated for their ‘agreement’. The
reference scanner’s sensor has a 30 μm diameter and can capture data
points every 50 μm. This explains why it was unable to provide readable
data when measuring the 50 μm slip gauge. Accuracy of both the 3Shape®
extra-‐oral scanner and 3M™ True Definition intra-‐oral scanner in measuring
the width of the slip gauges below 400 µm was poor in comparison to the
reference scanner. It can be deduced from this that the optical resolution of
the test scanners is inferior to that of the reference scanner.
As has previously been described, optical resolution of the objective is a
limiting factor for non-‐contacting profilometers. This describes the
minimum distance between two lateral features that can be measured, and
in the case of this study the lateral features were the right angle edges of the
engineering slip gauges. The intra-‐ and extra-‐oral dental scanners are
designed to measure tooth-‐shaped freeform objects which may have limited
the capabilities of the stitching software to allow images to be reliably
reconstructed when the thickness of the gauges was below 400 µm. Below
this 400 µm threshold value, the two right angles presented to the sensor
66
were too closely approximated and so the profilometers had difficulty in
recording the width. This was a situation that may not be clinically relevant
and the test was perhaps more applicable for investigating the capabilities
of the hardware, rather than the hardware and software combined. Another
limitation of this study that could have affected the measurements is that
accurate scanning depends on an uninterrupted line of sight between laser,
surface and detector. Therefore, if a step is to be measured, as is essentially
the case when measuring a slip gauge from side on, the sensor must be in
the correct orientation so that the laser spot is not hidden by the edge of the
step (Zeng et al, 1997).
Repeatability and reproducibility for both the extra-‐oral and the intra-‐oral
scanners was found to be poorer than that of the reference profilometer
when measuring either the height or the angle of both the inlay specimen
and the bridge specimen. Therefore the reference scanner had the best
repeatability and reproducibility with a standard deviation of 5 – 9 μm. The
3Shape® extra-‐oral scanner had the next best repeatability with a range of
12 – 19 μm and the 3M™ True Definition intra-‐oral scanner had a range of
14 – 27 μm. All of these were similar to the coefficient of repeatability range
of 7–16 μm found by Persson et al (2008) and the poorer precision of
measurement in comparison to the reference profilometer was perhaps not
unexpected considering that the reference profilometer was a high
specification measurement device.
Previous studies have looked at implant angulation but as far as the authors
are aware there are no other studies that have investigated the repeatability
67
or reproducibility of convergence angle α. Despite the poorer repeatability
and reproducibility, the results suggest that the precision of angular
measurement is reasonably good for all three scanners. The ability of intra-‐
oral scanners to accurately measure angulation will of course be of
particular benefit in implant dentistry, where the clinician is often faced
with large span frameworks that through errors do not fit passively. If
implant fixtures at varying angles can be measured with precision and
accuracy then costly and time-‐consuming chair side adjustment may be
avoided.
Without a metrological standard, the reference profilometer scans of the
inlay and bridge specimens served as the reference model. The accuracy of
this scanner in measuring length was shown to be 1.3 μm by Rodriguez et al.
(2012) and it was felt that this was an acceptable standard against which to
compare the two scanners being investigated. It should be noted however
that BS EN ISO 12836 required inlay and bridge specimens to be of exact
dimensions and made from a dimensionally stable material but this was not
possible for this study for reasons already stated.
With regard to the accuracy results of the two test scanners, as shown in the
trend towards a overestimation of the trueness for the 3M™ True Definition
intra-‐oral scanner in comparison to the 3Shape® extra-‐oral scanner may
have been as a result of the need for a light dusting of titanium dioxide
powder, which is of unknown thickness. Titanium dioxide application is
described by various authors (Syrek et al. 2010, Van der Meer et al. 2012)
but at present there is no report into how this might scanning accuracy.
68
As considered by Bartlett (2010), understanding of the aetiology and
pathogenesis of tooth wear is still lacking. Techniques to quantitatively
measure tooth wear have proved to be time consuming and costly, usually
requiring specialised hardware and software (Lee et al. 2012). Traditionally
in vivo quantitative tooth wear studies have measured tooth surface loss in
terms of height lost, which can be subjective to measure and offers little
information about the wear lesion. Conversely, in vitro studies offer little to
no information with regard to aetiology and no matter how well designed do
not precisely replicate the conditions found in an intra-‐oral environment,
although Sagakuchi et al. (1986) have previously reported good correlation.
Both the 3Shape® extra-‐oral scanner and the 3M™ True Definition intra-‐oral
scanner show a mean volume variation from the reference volume of ± 0.2
mm3.
There are few studies that look at volumetric tooth wear but the volumetric
error measurement found in this ‘proof of concept’ investigation carried out
in this present study would potentially render the intra-‐oral scanner
unsuitable for use in a clinical study investigating short term rate of tooth
wear given that Tantbirojn et al. (2012) described mean (standard
deviation) volume loss per tooth of 0.18 (0.12) mm3 over a 6 month period
(in patients with gastro-‐esophageal reflux disease). However Tantbirojn et
al. do note that they scanned dental stone models cast from
polyvinylsiloxane and they go on to state, “the accuracy [of measurements]
can be improved further with advances in intra-‐oral scanning techniques
that will eliminate potential distortions and dimensional changes in the
impression material and dental stones.”
69
As CAD/CAM technology continues to develop and become more prevalent
in dental surgeries it will not be surprising to see its application to the
quantitative measurement of tooth wear. However, further research is
certainly required in this area in order to determine more clearly the
effectiveness of intra-‐oral scanning in the quantitative measurement of
wear, in comparison to more established profilometric techniques. In vivo
studies to investigate volume of tooth substance loss over time would be of
particular benefit, especially in ‘at risk’ individuals, however the time and
cost implications of the large numbers of participants who would need to be
recruited for such a study do have to be factored in to the planning of future
clinical research in this area.
70
Conclusion
The digitizing devices under investigation were found to be able to measure
the engineering slip gauges accurately to 400 μm width and above. Below
this no readable data could be recorded. When compared to the reference
profilometer this would suggest that the optical resolution of the test
devices is inferior.
Repeatability and reproducibility for both of the test scanners was found to
be statistically significantly increased than that of the reference
profilometer when measuring either the height or the angle of both the inlay
specimen and the bridge specimen (p<0.05). Both the 3Shape® extra-‐oral
scanner and the 3M™ True Definition intra-‐oral scanner were able to follow
the previously published profilometric tooth wear measurement process
however they displayed a mean volume error of ± 0.2 mm3. This suggests
that as dental digitizing devices improve in their accuracy they will certainly
have future application in the quantitative measurement of tooth wear.
71
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