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24 May 2021 Accuracy of commercial intraoral scanners
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Purpose: In dental offices, there is a trend replacing conventional silicone impressions and plaster cast models by imaging data of intraoral scanners to map the denture and surrounding tissues. The aim of the study is the analysis of the accuracy of selected commercially available scanners. The accuracy is considered as the main drawback in comparison to the conventional approach.

Approach: We evaluated the reproduction performance of five optical scanners by a direct comparison with high-resolution hard x-ray computed tomography data, all obtained from a polyetheretherketone model with similarity to a full-arch upper jaw.

Results: Using the software GOM Inspect (GOM GmbH, Braunschweig, Germany), we could classify the intraoral scanners into two groups. The more accurate instruments gave rise to the following precision values: 35  μm (TRIOS® 3, 3shape, Copenhagen, Denmark), 43  μm (CS 3600, Carestream, Atlanta, Georgia), and 46  μm (3M™ True Definition Scanner, 3M ESPE, St. Paul, Minnesota). The less precise systems yielded 93  μm (Medit i500, Medit corp., Seongbuk-gu, South Korea) and 97  μm (Emerald™, Planmeca Oy, Helsinki, Finland).

Conclusions: The selected scanners are suitable for single crowns, small bridges, and separate quadrants prostheses. Scanners based on triangulation are hardly appropriate for full-arch prostheses. Besides precision, however, the choice of the scanner depends on scanning time, intraoral-camera size, and the user’s learning curve. The developed protocol, which includes three-dimensional (3D) imaging and advanced computational tools for the registration with the design data, will be increasingly used in geometrical metrology by nondestructive procedures to perform dimensional measurements with micrometer precision and is capable for detailed 3D geometrical models reconstruction.



An increasing number of dental treatments require the highly precise impression of the oral situation, and the quality of the treatment and the related success of the therapy depend on the correctly performed impression. For any fixed and removable prosthetics, the impression is fundamental, while for less critical cases, irreversible hydrocolloid materials, such as alginate, are used in conventional workflow. With an accuracy below 150  μm, these hydrocolloidal impressions are usually less precise than digital impressions;1 however, conventional impressions, taken with rigid trays and elastomeric materials, are so accurate that they are considered as the gold standard.2 Conventional impressions require the production of a plaster cast model.

In the digital workflow, no cast is needed, but depending on the procedure, a physical model with the necessary accuracy requirements has to be produced. These models are mostly three-dimensionally printed using stereolithography apparatuses (SLA), and they feature clinically acceptable accuracy.3 Intraoral scanners (IOS) are gaining importance in dental offices, and so they are therefore responsible for a paradigm shift in prosthetic dentistry.2,4 The latest generation of video-based systems (IOS) seems to be more accurate, faster, and more efficient in clinical application than previously employed devices, and they are even suitable for less experienced practitioners, because of their simplified handling.1,5,6 IOSs offer advantages compared to conventional impressions, and digital impressions are time-efficient and much more comfortable for patients. In particular, patients suffering from the gag reflex benefit.7

IOSs use suitable cameras for the optical detection of the denture that collect point clouds on a path proposed by the suppliers and determined by the dentist. The physical principles of IOSs can be divided into confocal techniques with structured light with wavelengths ranging from ultraviolet to red color and the triangulation of projected pattern using preselected colors.810 The description of the obtained surface in the three-dimensional (3D) space happens in the standard triangulation language (STL)-format.

Crowns and bridges can be directly manufactured using computer-assisted design (CAD)/CAM, or, alternatively, models can be produced by means of stereolithography.11,12 The main disadvantages of IOS are acquisition costs and intricate access to light-tight areas, including subgingival preparations.

The technology involved in intraoral scanning has significantly improved since 1980, when the first CEREC was introduced to the market.13 In the meantime, intraoral scanning has been established in a wide range of indications.14 Intraoral scans are used in prosthodontics for inlays/onlays, crowns, frameworks, fixed and removable partial prostheses, posts and cores, crowns and bridges and for digital smile design. In orthodontics, digital impressions serve as the basis for treatment planning, for custom-made devices and (transparent) aligners.15 In implant surgery, intraoral scans are integrated into the digital workflow to plan clinical cases and produce surgical guides,16 and they are increasingly considered more often as highly accurate, exhibiting no difference in comparison to conventional impressions for crowns and fixed dental prostheses of limited length.17,18 In the current literature, however, long-spanning fixed restorations or totally removable prostheses, which include six or more elements, are deemed somewhat problematic.1,15 The available studies about the precision of IOS hardly cover the latest generation of devices. The progress in technology by comprising high-resolution cameras for data acquisition and high-performance software for the polygonal mesh generation of the model has led to sudden improvement of the IOS performance.19 The advancement of software particularly has enabled solutions not otherwise possible with conventional impression technology. Here, it is possible not only to analyze imaging data in detail but also to modify crown preparations during treatment. Potential deficiency in the obtained impressions can be minimized or even fully removed, and related shade measurements assist in the determination of crown color. To educate the patient, the captured images can be presented immediately after scanning, while a series of scans from the same patient can be the basis of monitoring changes over time.

There is an increasing number of comparative studies addressing accuracy, which refers to both trueness and precision.810,20 Advanced micro computed tomography systems provide an accuracy of <10  μm for objects as large as a human jaw.2 Therefore, this approach is also applied for this study.21 The study should quantitatively answer the question how far the five selected IOS systems reach the clinically required accuracy of 120  μm.18 Employing this example, we will discover the assets and drawbacks of registering the nondestructively acquired 3D data of microtomography and optical scanning with the design for metrology of 3-in. solids down to a very few micrometers.




Model Fabrication

The anatomic model of a maxillary full denture, based on standard working models (frasaco GmbH, Tettnang, Germany), was created with CAD and commercially available software (Meshmixer, Autodesk Inc., San Rafael, California). The parallel cylinders, with a predefined inner diameter and a depth of 4 mm, were placed at tooth positions 17 (C1), 21 (C2), and 27 (C3) as reference elements (see photograph in Fig. 1). A characteristic crown preparation at tooth 23, and an inlay preparation at tooth 16, simulated a normal prosthetic situation. The master model was milled out of an industrially manufactured polyetheretherketone (PEEK) block (Denseo PEEK blank, Denseo GmbH, Aschaffenburg, Germany) on a five-axis computerized-numerical-control milling machine (SilaMill 5, vhf camfacture AG, Ammerbuch, Germany). PEEK is a high-performance polymer, and it is known to be dimensionally stable 22 and is also used in medical applications, see, e.g., Ref. 23. An extension on the back of the model served for mounting purposes.

Fig. 1

The PEEK model’s size corresponds to that found in the human body, as displayed by the photographs on the left. Three well-defined hollow cylinders were incorporated to determine the precision of the IOSs. The other photograph shows the placement of the model on the rotation stage in the CT-system nanotom® m (phoenix|x-ray, GE Sensing & Inspection Technologies GmbH, Wunstorf, Germany).


In addition, two other models were fabricated using the same design. A photopolymer resin, namely dental model resin (Formlabs, Somerville, Massachusetts), was used within the SLA printers form 2 (Formlabs, Somerville, Massachusetts) and with a layer thickness of 25  μm. Models fabricated by the stereolithography technology were washed with isopropyl alcohol for a period of 15 min. Subsequently, they were postcured with UV light under an inert gas atmosphere. The density of the models was experimentally determined to 1.59  g/cm3, which is significantly higher than the value of the raw material at 1.12  g/cm3. This result is an indicator of cross-linking at the 405-nm wavelength.


Reference Generation

The high-resolution CT (μCT) scans of the master model, described already, served as the reference data. Tomographic data were recorded using the advanced conventional system nanotom® m (phoenix|x-ray, GE Sensing & Inspection Technologies GmbH, Wunstorf, Germany), as shown in Fig. 1. This system is equipped with a nanofocus tube with a maximal acceleration voltage of 180 kV, which produces power of up to 15 W. For data acquisition, we employed the maximal acceleration voltage and a beam current of 30  μA. To shift the mean photon energy to higher values, a 0.5-mm-thin copper film was placed behind the transmission target. We recorded 1600 radiographs throughout 360 deg. The exposure time for the first two datasets was set to 3 s per radiograph, whereas it was increased to 9 s for the third and to 24 s for the fourth dataset. To investigate the repeatability of the μCT-system and the impact of the cone beam, the following source–sample distances (SSDs) and source–detector distances (SDDs) were positioned. For the first and the second scans, SSD and SDD were 78.75 and 225.00 mm, respectively. For the third scan, we used SSD 157.50 mm and SDD 450.00 mm, and for the fourth scan SSD 210.00 mm and SDD 600.00 mm were used. Exposure times were adapted to maintain comparable intensities, and the effective pixel length corresponded to 35  μm. These approaches keep the magnification constant. A large SSD limits the angle of the cone beam and might improve the accuracy but leads to significantly longer exposure times.

In a previous study,2 we have captured a dental model using the nanotom® m and the tactile coordinate measuring machine Leitz PMM 864 (Hexagon Metrology GmbH, Wetzlar, Germany). Both approaches provided true micrometer resolution. Consequently, the micrometer precision of the nanotom® m system for centimeter distances was validated.

For visualization purposes, the acquired volume data were processed by means of VGStudio MAX (Volume Graphics, Heidelberg, Germany). In addition, the data size was reduced and converted into the STL format. This conversion enabled us to compare the tomography data with data for the intraoral scans.


Data Acquisition, Using Intraoral Scanners

This study comprises five IOS systems, namely the 3M™ True Definition Scanner (3M ESPE, St. Paul, Minnesota), the TRIOS® 3 (3shape, Copenhagen, Denmark), the CS 3600 (Carestream, Atlanta, Georgia), the Medit i500 (Medit corp., Seongbuk-gu, South Korea), and the Emerald™ (Planmeca Oy, Helsinki, Finland). With each system, the master model was scanned 10 times to obtain the necessary statistics. For this purpose, the model was mounted in the anatomically correct upright position. One trained examiner (M.S.) performed all of the scans in identical conditions (light, temperature, etc.), and scanner handling, the use of powder, and the scan path were carried out according to the manufacturer’s guidelines. 3M recommended the use of powder to improve the scanning results. To prepare the model as recommended, a thin layer of powder (3M Powder Sprayer; 3M, St. Paul) was applied to the model. The scans with the other four systems were taken without the application of powder, i.e., in a powder-free fashion.


Data Procession and Evaluation

The measurements and analyses were performed using the well-established software GOM Inspect (GOM GmbH, Braunschweig, Germany). The positions of the three hollow cylinders were determined using their center points, identified via the Gaussian best-fit method, see Fig. 2. The three distances were derived from tomography and IOS data individually, see Fig. 3.

Fig. 2

Scheme for determining the center points of the hollow cylinders via the Gaussian best-fit method.


Fig. 3

Scheme for specifying the three distances. Distance d1 characterizes the length between 17 and 21, distance d2 is the length between 21 and 27, and distance d3 corresponds to the length between 17 and 27.


To compare accuracy and precision, these data were matched to the reference. The global best-fit deviation was calculated for each scan, in order to visualize the displacement field, see what follows.


Results and Discussion


Measurements with nanotom® m

To confirm the well-known stability of the μCT-system and the reproducibility of the tomographic data acquisition, the first two scans were performed in identical conditions. As expected, differences were within the micrometer range, and even for distances between 4 and 5 cm, as given by the spacing between the hollow cylinders, the differences were well below the voxel length of 35  μm. For scan 1, we found d1=45.444  mm, d2=41.622  mm, and d3=48.098  mm. For scan 2, the selected distances were determined to d1=45.450  mm, d2=41.627  mm, and d3=48.101  mm. This result, i.e., differences of 4 to 6  μm or relative deviations by about 104, indicates that imaging modality and the method for determining longitude are appropriate choices for precision measurements. As a consequence, we assumed an error bar of 6  μm for establishing the spacing between the hollow cylinders.

To evaluate the impact of the cone-beam geometry in the nanotom® m on the accuracy, two scans with modified sample positions with respect to source and detector were performed. The experimentally determined distances between the hollow cylinders of scan 3 were d1=45.468  mm, d2=41.640  mm, and d3=48.127  mm. The values for scan 4 amounted to d1=45.480  mm, d2=41.647  mm, and d3=48.134  mm. Compared to the set value, given by the STL file with d1=45.503  mm, d2=41.676  mm, and d3=48.192  mm, we identified values only 23, 29, and 58  μm smaller. Although the discrepancies amount only to 1/10th of a percent and less than two pixel lengths, the phenomenon was still detectable. Therefore, tomographic data acquisition for the three-dimensionally printed models was performed with the parameters in scan 4. It should be noted, however, that the potential gain in accuracy meant that data acquisition took seven times longer to complete than the standard approach.


Geometry of the PEEK Model

The PEEK model was generated from the STL-data by a milling machine, it is therefore unknown how far the model corresponds to the desired geometry. Comparing the STL data with the tomography data, one obtains a superposition of deficiencies from milling and imaging. Previous studies with the nanotom® m, however, demonstrate true micrometer accuracy, which is further supported by the measurements described above. Therefore, we can reasonably estimate the accuracy of the PEEK machining through a direct comparison of STL-data with high-resolution tomography data.

Figure 4 elucidates the differences between the design and the measured data using the color code on the color bar. The red color indicates positions, where material more than 100  μm thick should be further removed. The blue color represents positions, where the milling tool removed more than originally desired, and the green color shows positions in perfect agreement. Since the hollow cylinders are almost identical, their axes and related center points are not affected. Measurement of the distances described already is therefore meaningful.

Fig. 4

3D representation of the differences between the desired geometry, given by the STL-file and the data from scan 4 and according to the color bar and the related values on the right. Perfect agreement is represented by the green color. Obviously, the milling tool provided a reasonable result, although in some areas more material than desired was removed (blue color), while other areas show excess material (red color). One can further observe that the hollow cylinders are larger in size than planned, but because we only consider the center points, the determination of distances is hardly affected.



Geometry of the SLA Models

In specific situations, the digital workflow has to be modified, which might require a physical model to be generated from the IOS data. Here, the method of choice is stereolithography,24 but current clinical experience shows that these SLA-models are less accurate than conventional impressions. To quantify this level of accuracy, we produced two SLA-models and used tomographic imaging and registration.

Based on the high-resolution tomography measurements performed as described already, the distances d1, d2, and d3 were extracted. For the first SLA-model, the three distances corresponded to 45.611, 41.830, and 48.210 mm, whereas for the second SLA model, we found 45.753, 41.831, and 48.247 mm, meaning that the two models were not exactly the same in terms of geometry. The differences were in the submillimeter range, see Fig. 5. Comparison with STL-data, however, is the benchmark. The average deviation along the full arch amounted to (49±9)  μm. For the distances considered within this study, the deviations accounted for Δd1=108  μm, Δd2=154  μm, and Δd3=18  μm (first SLA model), and Δd1=250  μm, Δd2=155  μm, and Δd3=55  μm (second SLA model). These differences between the desired design and the actual physical models clearly indicate the limitations of the stereolithography printers currently used in dental offices.

Fig. 5

3D representation of the differences between the desired geometry, given by the STL-file, we used for the model preparation (photograph on the left) and the high-resolution tomography data of the two 3D-printed models. The green color shows parts without differences, whereas the red and blue colors indicate excess and deficiency of material, respectively.



Accuracy of the Intraoral Scanners

The results obtained from the 10 independent experiments with each of the IOS systems are listed in Table 1. These numbers show the reproducibility of the individual devices, when an experienced dentist has performed data acquisition according to the guidelines provided by suppliers. The data scattered within a few tens of micrometers.

Table 1

Measured distances d1, d2, and d3 (in mm) obtained from the IOS systems used. The data determined from the μCT scans (d1=45.480  mm, d2=41.647  mm, and d3=48.134  mm) can be regarded as ground truth.

3M TDSTRIOS® 3CS 3600Medit i500EMERALD™

To determine the accuracy of the IOS systems in measuring the three selected distances, we compared these values with tomography data for the PEEK model. For the 3M™ True Definition Scanner (3M ESPE, St. Paul, Minnesota), which is based on pulsed blue light and active wavefront sampling,8 the deviations for d1 were (80±14)  μm, for d2 (62±8)  μm, and for d3 we found (20±7)  μm. For the TRIOS® 3 (3shape, Copenhagen, Denmark), a structured light scanner using confocal microscopy principle,9 the length deviations amounted to (57±18)  μm, (82±16)  μm, and (124±97)  μm, respectively. The CS 3600 (Carestream, Atlanta, Georgia), a system applying four-color structural light,10 provided (81±22)  μm, (41±20)  μm, and (40±64)  μm, respectively. Using the Medit i500 (Medit Corp., Seongbuk-gu, South Korea), based on triangulation, we found (93±54)  μm, (76±33)  μm, and (41±247)  μm. Finally, the Emerald™ (Planmeca Oy, Helsinki, Finland), a system applying tree-color projected pattern for triangulation,10 yielded d1=(14±48)  μm, d2=(80±54)  μm, and d3=(110±291)  μm. The error bars corresponded to the standard deviations derived from the 10 measurements. Whereas the data were generally within a tenth of a millimeter, one recognizes some trends. The results of the Medit i500 scanner, for example, gave rise to values below the selected ground truth.

Considering the combination of the three selected distances, one can directly compare the performance in length measurements of the five IOS systems by means of the median values and the related variances. From the lowest to the highest median amplitudes, the Emerald™ gained (2±34)  μm, the CS 3600 achieved (58±2)  μm, the 3M™ True Definition Scanner scored (59±4)  μm, the TRIOS® 3 reached (79±4)  μm, and the Medit i500 led to (98±45)  μm.

The average values, however, do not represent the full story. Therefore, the color-coded deviation fields are shown in Fig. 6. Although the Emerald™ IOS reproduced the three selected distances perfectly well, the strong color gradients indicate the challenging handling and a relatively weak reproducibility. Consequently, the CS 3600, the 3M™ True Definition Scanner, and the TRIOS® 3 might be the better choice concerning reproducible and accurate measurements within the oral cavity of the patient. The results displayed in Fig. 6 also show that the Medit i500 is less precise than other IOS systems.

Fig. 6

Color-coded deviation field of the IOS derived from the difference to the selected ground truth, i.e., the high-resolution tomography experiments using nanotom® m. The green color shows agreement, whereas the red and blue colors point the locations of positive and negative deviations.


Using the software GOM Inspect (GOM GmbH, Braunschweig, Germany), one finds a similar result. This software provided the following precision values: TRIOS® 3—35μm, CS 3600—43  μm, and 3M™ True Definition Scanner—46  μm. The other two systems yielded less precise data: Medit i500—93  μm and Emerald™—97  μm. If only a single quadrant is considered, one finds another picture; therefore, the selection of the best available IOS system depends on the clinical case, the training of the dentist, and the convenience.


Accuracy of Single-Crown Preparation

To analyze the single tooth preparation and the IOS-accuracy on a smaller length scale, Tooth 16 was considered. The mean deviation was determined in the same manner as for the full arch, i.e., n=10. The IOS-data of the single-tooth preparations demonstrated the expected performance of the systems included into the study. The accuracy is almost perfect, because the number of images to be stitched is limited. For the tooth stump (tooth 16), we found the following precision values: TRIOS® 3—(9±5)  μm, CS 3600—(10±5)  μm, Medit i500—(11±1)  μm, and 3M™ True Definition Scanner—(12±1)  μm. Only one system yielded a significantly less precise dataset: Emerald™—(47±9)  μm.


Limitations Related to Clinical Conditions

It should be noted that the results of IOS cannot be fully judged from an in vitro study. The dentists have to treat also edentulous patients, to consider the difficulties in controlling the salivary flow, and to account for the presence of restorative and prosthetic works in the dental arch. The usability of the selected IOS device depends the learning curve of the dentist and the size of intraoral-camera size with respect to the space and accessibility of the oral cavity as well as the available and necessary scanning time to record the 3D surface data.



The accuracy of the nanotom® m data was validated in a previous study.2 Replacing the previously used metal cast with the mechanically machined PEEK model, we were able to reduce significantly streak artifacts. Neither full dentition model included edentulous areas, which can be more difficult to scan and could have affected the results.25 This experimental study avoided the presence of soft tissues, saliva, blood, filling materials, or space limitations, which often can compromise the accuracy of the scan data in a clinical setting.

Compared to the study presented herein, it is more challenging to determine the precision of IOS systems in an in vivo setting. In such studies, the reference model is digitized after a conventional impression and may contain related errors. There are only a few full-arch in vivo studies, see, for example, Ref. 1 and an older study;26 the results nevertheless correlate with our findings. Physiological tooth mobility can range from 30 to 100  μm,27 and the clinically acceptable limit of the marginal gap of a crown is generally 120  μm.18

For the full arch, the IOS systems considered herein show reasonable results, although the precision of at least some systems should be improved. In a separate quadrant, however, the devices reach the desired performance.

If the situation requires a physical model, which is then produced using stereolithography technology, full-arch accuracy is often not achieved—contrary to the conventional silicone impressions. As a consequence, they are generally considered as unsuitable for larger prosthetic reconstructions.2,3 In this study, we incorporated only two printers from one model, and thus, the obtained data have limited informative value.

Besides precision, there are further factors including scanning time, the learning curve, or intraoral-camera size, each of which strongly affects the usability of an IOS device. Nevertheless, we can state that current digital impressions exhibit micrometer accuracy and generally produce clinically acceptable data. All analyzed IOS devices are suitable for generating 3D data for working models, single crowns, and small bridges.

Since the accuracy of the digital impressions is fundamental for most clinical applications and the systems differ significantly, it is preferable to use one of the more accurate instruments, which circumvent triangulation, namely the TRIOS® 3, the CS 3600, and the 3M™ True Definition Scanner for the full-arch scanning.


The authors declare no conflict of interest.


The authors thank ArteDent, Palma de Mallorca, Spain, for the reference model and the SLA model production. The authors also thank the companies Kaladent AG, St. Gallen, Switzerland, Curaden Dentaldepot, Kriens, Switzerland, and Alfons Stöcklin, Praxis-Team St. Margarethen, Binningen, Switzerland, for providing the intraoral scanners. The financial support of the Swiss National Science Foundation in the frame of the R’equip initiative 316030_133802 is gratefully acknowledged. An earlier version of this paper with modified title and abstract as well as complemented text and references was published as Proc. SPIE 11113, 111131Q (2019).



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Mattia Sacher is a dental practitioner with a focus in oral surgery. He graduated in dentistry at the University of Basel in 2015. Since 2018, he has been working at the Biomaterials Science Center toward the doctoral thesis on comparing the accuracy of intraoral scanners, using advanced micro computed tomography. In 2020, he received his certificate “Dr. med. dent.” from the University of Basel. He is especially interested in research related to digital dentistry.

Georg Schulz graduated in theoretical physics at the University Freiburg, Germany, in 2008. Subsequently, he started his PhD project on the multimodal visualization of human brain at the University of Basel. He earned his doctoral degree in physics in 2012. Since 2012, he has been a research associate in the field of high-resolution hard x-ray imaging. He is also the responsible scientist for the Core Facility “Micro- and Nanotomography” at the medical faculty of the University Basel.

Hans Deyhle is a beamline scientist at the k11 DIAD beamline at Diamond Light Source, United Kingdom. He studied experimental physics at the ETH Zurich until 2007. From 2009 to 2012, he worked for his doctoral degree in physics at the University of Basel on the micro- and nanostructure of human teeth using synchrotron radiation, a topic he is still interested in. After postdocs at the School of Physics and the MuVis Imaging Centre in Southampton, United Kingdom, he is now responsible for the x-ray commissioning at DIAD beamline.

Kurt Jäger is an experienced Swiss dentist, head of the dental center “Argodentis Zahnmedizin” in Aarburg, and adjunct professor at the Medical Faculty of the University of Basel. He earned his doctoral degree from the University of Basel in 1985 and his habilitation for dentistry and prosthetics in 1991. Subsequently, he became a lecturer at the dental school and at Biomaterial Science Center in Basel. Furthermore, he has been the chief dentist of the Swiss army. He has published more than 200 papers and book chapters.

Bert Müller holds the Thomas Straumann Chair for Materials Science in Medicine at the University of Basel, Switzerland. He is the founding director of the Biomaterials Science Center. In 1989, he received his MS degree in physics from the Dresden University of Technology, Germany. He received his PhD in experimental physics from the University of Hannover, Germany, in 1994. He is the author of more than 300 journal papers and many book chapters. His current research interests include high-resolution hard x-ray imaging, nanocontainers for targeted drug delivery, dielectric elastomer transducers for medical applications, and physics-based approaches in dentistry. He is a fellow of SPIE.

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Mattia Sacher, Georg Schulz, Hans Deyhle, Kurt Jäger, and Bert Müller "Accuracy of commercial intraoral scanners," Journal of Medical Imaging 8(3), 035501 (24 May 2021).
Received: 13 November 2019; Accepted: 7 May 2021; Published: 24 May 2021

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