Unwanted effects due to interactions between dental materials and magnetic resonance imaging: a review of the literature

Abstract

Magnetic resonance imaging (MRI) is an advanced diagnostic tool used in both medicine and dentistry. Since it functions based on a strong uniform static magnetic field and radiofrequency pulses, it is advantageous over imaging techniques that rely on ionizing radiation. Unfortunately, the magnetic field and radiofrequency pulses generated within the magnetic resonance imager interact unfavorably with dental materials that have magnetic properties. This leads to unwanted effects such as artifact formation, heat generation, and mechanical displacement. These are a potential source of damage to the oral tissue surrounding the affected dental materials. This review aims to compile, based on the current available evidence, recommendations for dentists and radiologists regarding the safety and appropriate management of dental materials during MRI in patients with orthodontic appliances, maxillofacial prostheses, dental implants, direct and indirect restorative materials, and endodontic materials.

INTRODUCTION

Imaging is an integral step in diagnosis in medicine and dentistry. Conventional radiographic methods (intraoral radiographs, orthopantomograms) have inherent limitations, since they capture 3-dimensional anatomy on a 2-dimensional image and because they involve ionizing radiation. Advanced imaging techniques include computed tomography (CT), cone-beam CT, magnetic resonance imaging (MRI), ultrasonography, and positron emission tomography [1,2]. MRI, when indicated, is advantageous over other imaging techniques because it provides high spatial resolution images of hard and soft tissues, the images are obtained in various planes, and it involves no ionizing radiation, unlike intraoral radiographs and CT scans [3].

MRI creates images using a strong uniform static magnetic field and radiofrequency pulses [4]. When placed in a magnetic field, all substances are magnetized to a degree that depends on their magnetic susceptibility [4,5]. Unfortunately, variations in the magnetic field strength that occur at the interface between dental materials and the adjacent tissue can lead to spatial distortions and signal loss, thereby generating an artifact in the image [6]. Apart from artifact formation, other unwanted effects of MRI are radiofrequency heating (a physical effect) and magnetically-induced displacement (a mechanical effect) of the dental material [7].

In addition to the medical applications of MRI, newer approaches have been proposed in various branches of dentistry with regard to MRI applications, including in the fields of endodontics, caries diagnosis, prosthodontics, and orthodontics [8,9,10,11,12,13,14,15]. However, information on the capacity of dental materials to induce unwanted effects is not readily available.

REVIEW

A search in PubMed and Google Scholar was conducted using the keywords ‘safety’, ‘artefacts’, ‘artifacts’, and ‘magnetic resonance imaging’. Only articles from dental journals were selected. No restrictions were used regarding the language of the articles. The literature search yielded 81 articles from 1988 to 2018, of which 45 were found to be relevant. In addition to the articles in the English language, 3 were in Chinese, 2 in French, and 1 in German. There were 3 case reports, 14 clinical studies, and 22 in vitro studies. There were also 3 review articles (Sinkiewicz et al. [7], Hubálková et al. [16], Hu et al. [17]), and 1 letter to the editor (Hunt et al. [18]).

Mechanism of MRI

MRI creates detailed images of organs and tissues within the body using a strong uniform static magnetic field and radio waves [4]. The images are constructed from the rate of decay or relaxation of proton resonance in a plane longitudinal (T₁ images) or transverse (T₂ images) to the magnetic field plane. Modern MRI machines use magnets with a field strength of 0.5–2 tesla (T). The strength of the magnet is directly proportional to its sensitivity in detecting small lesions [19]. Most MRI machines are large tube-shaped magnets that align the water molecules in the body, which in turn produce signals through the induction of radio waves. The result is the creation of cross-sectional magnetic resonance (MR) images [20].

Types of unwanted effects

The potential unwanted effects caused by the interaction of MRI and dental materials fall into 3 broad categories (Table 1) [20,21,22,23].

Table 1. Unwanted effects of magnetic resonance imaging (MRI)-dental material interaction.

Type of unwanted effect	Description
Artifactual	The accuracy of the image is affected by the dental material.
Mechanical (magnetically-induced displacement)	The external strong magnetic field may dislodge or move a ferromagnetic material into a position parallel to the lines of that field.
Physical (radiofrequency heating)	The ferromagnetic material is heated by the high-frequency electromagnetic field.

1. Artifact formation in MRI

An MRI-induced artifact is defined by pixels that do not faithfully represent the tissue components under study [23]. The shape of the artifact (elicited by a cubic sample) depends on the scanning plane. Artifacts have a circular pattern when scanned in the axial plane, and a ‘clover-like’ pattern in the sagittal plane [24]. Artifact severity depends on the following factors: the magnetic properties of the metal object that causes the artifact; the shape, position, orientation, and number of objects; the homogeneity of the alloy; the MRI sequence; and the sequence parameters used [6,8].

Owing to differences in the magnetic susceptibility of human tissues and dental alloys, metallic dental restorations produce serious artifacts, especially in maxillofacial imaging [23]. Alloys may behave very differently from ‘pure’ metals, and manufacturers are often reluctant to disclose the composition of their ‘trademark’ alloys [7,21]. The literature contains contradictory results regarding the severity of image artifacts caused by different dental materials such as high gold-content alloys, titanium, and dental amalgam [8,25,26,27,28,29,30,31,32,33,34]. If a material is capable of causing an artifact on a scan, it can do so on a ‘slice’ of the scan several sections distant from the slice that contains the material [29]. Whether materials cause strong artifacts, moderate artifacts, or no effect strongly depends on the specific application. For example, a material that is compatible with brain MRI can severely affect the quality of orofacial MRI [8].

The mechanisms of artifact formation and other interactions can be understood by reviewing the principles of MRI (Figure 1). MR is based on the dependence of the resonant frequency of a hydrogen (H) nucleus on the strength of the magnetic field to which the nucleus is exposed. Any distortion of the magnetic field, either by intrinsic or extrinsic effects, will therefore result in spatial distortion of the image; that is, the distortion of the magnetic field at a certain point shifts the resonant frequency of the H nuclei at that point [6]. Figure 1 summarizes the mechanism of MRI and artifact formation. In the case of dental materials, there are 2 potential sources of artifacts in MRI.

Figure 1. Mechanism of artifact formation.

MR, magnetic resonance.

1) Distortion of the static magnetic field (B₀) due to differences in the magnetic susceptibility of materials and body tissues

A susceptibility artifact (SA) is defined as signal incoherence generated by the intermingling of substances with discrepant capacities to be magnetized (measured by x, susceptibility). Because most body tissues are diamagnetic (not very magnetizable), proximity to substances with highly magnetic properties (i.e., ferromagnetic materials) induces SAs.

2) Eddy currents

These are induced by alternating gradients and radiofrequency magnetic fields. The induced eddy currents distort the applied magnetic field, leading to image distortion [8]. Eddy current artifacts due to metallic objects within the MRI field are referred to as non-SAs [35].

2. Unwanted mechanical (magnetically-induced displacement) effects

The term ‘MR environment’ encompasses the static, gradient, and radiofrequency electromagnetic fields that may affect implants and other devices in the body. The most immediate risk associated with the MR environment is the attraction between the MRI device (a magnet) and ferromagnetic metal objects [17,36,37]. The magnetic field is strong enough to pull heavy objects towards the scanner at a very high velocity (known as the projectile effect) [38]. The translational attraction (dependent on magnetic field strength and the object's mass, shape, and magnetic susceptibility) and resultant torque may cause the movement or dislodgment of ferromagnetic implants, resulting in uncomfortable sensation or injury to the patient [22,39,40].

According to testing standards (ASTM F2052-06) of magnetically-induced deflection, if the device under testing is deflected by < 45°, the risk induced by this deflection force is no greater than that imposed by normal daily activity in the earth's gravitational field [41]. Hasegawa et al. [22] found that the deflection angles were > 90° with deflection forces of 0.03–0.3 N for magnetic dental attachments with castable alloys (components of removable partial denture prostheses) during 3 T MRI. The authors concluded that magnetic dental attachments may cause patient discomfort, but the retention force of dental luting cement (48–150 N) is strong enough to prevent prosthesis dislodgment. Nevertheless, the fixation of the ferromagnetic prosthesis to the tooth must be checked before and after MRI, due to the possibility of cement degradation [40].

Patients in which MRI poses a high risk include those with biomedical devices and implants such as pacemakers, cochlear implants, neurostimulators, infusion pumps, fixed metal prostheses, and aneurysm clips. MRI is contraindicated in such patients because the magnetic field of MRI can cause these devices to become non-functional, thus generating life-threatening situations, dislocation (due to torsion), and soft tissue burns (due to the absorption of radiofrequency energy) [3,27,38,42,43].

3. Unwanted physical effects (radiofrequency heating)

Due to interactions with MRI, metallic objects in the human body can undergo radiofrequency-induced heating [17]. The heat-pain threshold for the oral mucosa is a temperature rise of 8°C–10°C. A temperature increase above 10°C for more than 1 minute constitutes the safety threshold for the periodontal ligament, which is a highly vascular tissue compared to bone [22,40]. The aforementioned study by Hasegawa et al. [22] assessed the increase in the temperature of magnetic dental attachments with castable alloys (components of removable partial denture prostheses). Using 3 T MRI, the maximum elevation in temperature was 1.42°C. This temperature increase was not high enough to cause pain or damage to periodontal tissues.

Factors influencing unwanted effects

1. Magnetic susceptibility and magnetic permeability

During MRI, when no matter is present (i.e., in a vacuum), the induced field (B) and applied field (H) are essentially equivalent. Whenever matter is present within a given region of space, the induced field (B) is generally not equal to the applied field (H) because various electromagnetic interactions (internal magnetization [Mi] or polarization [J]) occur that concentrate or disperse the magnetic lines of force. This magnetization is proportional to the applied field by a dimensionless constant known as magnetic susceptibility (χ), which is synonymous with magnetizability. It is a measure of the extent to which a substance becomes magnetized when it is placed in an external magnetic field. Another dimensionless factor is magnetic permeability, a physical constant. It is related to magnetic susceptibility by the expression: µ = 1 + χ.

With regard to magnetic effects, 3 classes of materials exist (Table 2; Figure 2). Nearly all biological tissues are weakly diamagnetic. Other than trace amounts of magnetite, there are no endogenous ferromagnetic substances in the human body. However, many extrinsic metallic foreign bodies and surgical implants commonly encountered in MR imaging are ferromagnetic [8,27,34,44,45,46].

Table 2. Classification of materials according to their interactions with magnetic fields.

Type of magnetic effect	Effect on applied magnetic field	Magnetic permeability/susceptibility	Significance	Example
Diamagnetism	Internal magnetization (polarization) opposes the externally applied field;	µ < 1 (or χ < 0);	Least likely to cause an artifact	All biological tissues; silver (dental amalgam alloy)
	Magnetic field lines are ‘thinned’ or ‘dispersed’	Slightly lower permeability than free space;
		Negative susceptibility
Paramagnetism	Internal magnetization (polarization) is in the same direction as the externally applied field;	µ > 1 (or χ > 0);	Far less likely to cause an artifact	Vascular stents [46]; dental amalgam
	Magnetic field lines are ‘concentrated’ in the object	Slightly higher permeability than free space;
		Positive susceptibility
Ferromagnetism	Magnetic field lines are ‘concentrated’ in the object;	µ >> 1 (or χ >> 0);	High potential to cause MRI artifacts	Stainless steel
	Strongly attracted by a magnetic field	High permeability;
		Positive susceptibility

MRI, magnetic resonance imaging; χ, magnetic susceptibility (synonym = magnetizability); µ, magnetic permeability, µ = 1 + χ.

Figure 2. Classification of materials according to their interactions with magnetic fields.

χ, magnetic susceptibility (synonym = magnetizability); J, Polarization or Internal magnetization.

The greater the magnetic permeability of a material, the more magnetic field distortion (size of the resultant artifact) it will produce [6,27]. Thus, alloy composition is important in creating artifacts on MRI. Other important factors include the size and shape of the metallic material, as well as its position in the body [34]. MRI without artifacts is possible, even in close proximity to dental materials (such as amalgam, precious metal alloys, and titanium), provided that they have a low magnetic susceptibility. Unfortunately, not all current dental materials meet this criterion of low magnetic susceptibility [ 34]. Schenck [45] described the role of magnetic susceptibility of a material in MRI. Tymofiyeva et al. [8] analyzed and classified dental materials into 3 categories according to differences in susceptibility, as shown in Table 3.

Table 3. Classification of materials based on magnetic susceptibility.

Classification	Description	Significance	Example
Compatible	Compatible: Δx < 3 ppm;	Fully compatible materials;	Resin-based sealer AH Plus, glass ionomer cement, gutta-percha, zirconium dioxide, and some composites.
	Material produces no detectable distortions on either SE or GRE imaging.	Can be present even in the tooth of interest.
Compatible I	Compatible I: 3 < Δx < 200 ppm;	Limited distortions;	Some composites, amalgam, gold alloy, gold-ceramic crowns, titanium alloy, NiTi orthodontic wires
	Material produces noticeable distortions, acceptability depends on application.	Image usability depends on area of interest.
Non-compatible	Non-compatible: Δx > 200 ppm;	Strongest distortions;	Stainless steel orthodontic appliances (wires, brackets), Co-Cr sample.
	Material produces strong image distortions even located far from the imaging region.	Classified as non-compatible.

χ, magnetic susceptibility (synonym = magnetizability); SE, spin-echo; GRE, gradient-echo; compatible I, 3 < Δx < 200 ppm; material produces noticeable distortions, acceptability depends on application.

2. Electrical conductivity of the dental material

The magnetic field in MRI can also be distorted by electric currents flowing in materials within or close to the machine. Currents are induced in materials (especially in good conductors) by fluctuating magnetic fields [8]. The main magnetic field (B_o) is time-invariant, but gradient magnetic fields induce an electric current in any conductor in the field regardless of its magnetic properties. These induced currents, called ‘eddy currents’, themselves generate a magnetic field and cause spatial distortion of the image. The magnitude of the eddy current is determined by the rate of change of the magnetic field and the electrical resistance and configuration of the material [8].

3. Mechanical history (tensile strength) of the dental material

Although materials with sufficiently high nickel content (> 10%) show low magnetic permeability, those with lower nickel content show no correlation between composition and magnetic permeability. This lack of correlation is explained by the association between magnetic permeability and tensile strength [6,46]. As tensile strength increases, so does magnetic permeability. Tensile strength depends on the crystalline structure of the metal, and may be changed by ‘working’, or the extent to which the metal has been formed, bent, twisted, or cut by cold, which has a major effect on its crystalline structure. Hence, the past mechanical history of stainless steel alloys determines their effect on the images (Figure 3) [6].

Figure 3. Relationship between ‘working’ and magnetic permeability.

4. Imaging sequence used for MRI

In a study done by Bartels et al. [47], paramagnetic substances in vascular stents caused artifacts on MRI. The authors explained that the artifacts that were generated depended on the MRI sequence used and material size and thickness. Some sequences are more sensitive to SAs (Table 4) [34]. However, in the sequence protocol adopted by Costa et al. [27], a short echo time was not sufficient to reduce SAs.

Table 4. Relationship between artifacts and imaging sequence.

MRI sequence	Magnitude of artifact	Reason
Long echo time; GRE sequences	Most severe artifacts (loss of signal around the material) [8]	Intravoxel dephasing is the predominant cause of signal loss, resulting in a dark or black area around the metal on processed images [48,49].
Shortened echo time and decreased voxel size; SE sequence [49,50]	Best sequence for reducing the severity of susceptibility artifacts (complex spear-shaped artifacts) [8]	Diminished phase shifts in voxel caused by local static magnetic field gradients [80].

MRI, magnetic resonance imaging; GRE, gradient echo; SE, spin-echo.

Recommended guidelines

According to a literature review and the available evidence (Table 5), the following conclusions can be drawn regarding the use, safety, and diagnostic value of MRI in the presence of various dental materials and devices.

Table 5. Summary of unwanted effects due to interactions of dental materials with MRI, according to a literature search (1988–2018).

No.	Author (year)	Dental material used	MRI specifications/area of interest	Results	Conclusion/recommendation
1	Beau et al. (2017) [51]	Orthodontic brackets (S.S., Ti, ceramic with metal slots); retainers	1.5 T; 2 scans per patient with empty wax jig & with wax jig including the attachment.	S.S brackets always caused non-interpretability of all anatomic areas (100%). Ti (20%), ceramic brackets with metal slots (17%) and S.S. retainers (87%) caused artifacts in the oral cavity.	Ceramic brackets with metal slots & Ti brackets do not have to removed, based on the scan area; metal fixed retainers are to be removed only in oral cavity scans; S.S. brackets must always be removed before head & neck MRI.
	[Article in French]
2	Blankenstein et al. (2017) [52]	11 test specimens of known permeability (1.003–1.431)	1.5 T MRI; TSE & gradient-echo sequences of head & neck region.	Steel caused a wide range of artifact sizes (10–74 mm), depending on their permeability. Ti, Co-Cr & ceramic materials produced artifact radii up to 20 mm.	Permeability can be reliably assessed by conventional measurement devices & artifact size can be predicted. Radiologists can decide whether the orthodontic attachments should be removed.
3	Zhylich et al. (2017) [53]	Orthodontic brackets (S.S., ceramic, ceramic with metal slots); retainers	Head MR scans of 9 regions: sagittal T1-weighted, axial T2-weighted, axial gradient-recalled, axial diffusion-weighted, non-contrast axial MR angiography, & axial fluid-attenuated inversion recovery sequences.	MR images were affected by type of appliance, MR sequence, and location (head region). The maximum image distortion was found with S.S. brackets and molar tubes; minimal distortion occurred with ceramic brackets.	Type of appliance, region imaged, and MR sequence must be considered before imaging is done in patients with fixed orthodontic appliances.
4	Smeets et al. (2017) [54]	Dental implants of Zr, Ti, and Ti-Zr alloy embedded in gelatin	3 T MRI; T2-weighted space sequence & T1-weighted volumetric interpolated brain examination technique.	Ti & Ti-Zr alloy induced an extensive signal void in MRI (strong susceptibility — MR signal attenuated up to 14.1 mm from implant); Zr implants were clearly definable with only minor distortion artifacts.	MRI allows excellent image contrast and limited artifacts for Zr implants. CT & CBCT examinations are less affected by artifacts from Ti & Ti-Zr alloy implants than MRI.
5	Hilgenfeld et al. (2016) [55]	1 Zr & 4 Ti dental implants were provided with different single crown materials: PFM precious alloy, PFM non-precious alloy, porcelain-fused-to-Zr and monolithic Zr	3 T MRI; applying SPACE and TSE (2 standard sequence types).	The fewest artifacts were found with the Zr implant combined with a monolithic Zr crown. The Ti implant combined with a single crown framework of non-precious alloys had an unfavorable artifact volume. Smaller artifact volumes were noted for Ti implants with remaining 3 crown materials (PFM precious alloy, porcelain-fused-to-Zr, and monolithic Zr).	Material composition of dental implants provided with single crowns had a profound impact on artifact volume. In comparison with crowns containing cobalt, chromium and tungsten, MRI artifacts are reduced in precious alloy- and Zr-based crowns.
6	Lan et al. (2016) [56]	Crowns of Co-Cr, Ni-Cr, Ti alloy & pure Ti	3 T MRI with 6 sequences: T1weighted SE, T2 weighted-inversion recovery, T2 star GRE, T2 weighted-FSE, T1 weighted-fluid attenuate inversion recovery, and T2 weighted-imaging.	Artifacts in the T2 star GRE sequence were significantly wider than those in the other sequences.	The T2 star GRE exhibited the strongest influence on artifacts, whereas the other 5 sequences contributed equally to artifact generation.
	[Chinese]
7	Murakami et al. (2016) [24]	7 metallic dental materials: Al, silver alloy (Ag), type IV gold alloy (Au), gold-palladium-silver alloy (Au-Pd-Ag), Ti, Ni-Cr & Co-Cr alloy	Sequences included GRE, FSE, GRASS, SPGR, FSPGR, FIESTA & EPI (axial/sagittal planes).	Artifact volumes: FSE-T1/FSE-T2 < FSPGR/SPGR < GRASS/GRE < FIESTA < EPI. For all scan sequences, artifact volumes for Au, Al, Ag & Au-Pd-Ag were significantly smaller than other materials (artifact volume size: Ti < Ni-Cr < Co-Cr. Artifact-specific shape (cubic sample) depended on scan plane (i.e., circular pattern for the axial plane & ‘clover-like’ for the sagittal plane).	Availability of standardized information on artifact size & configuration during MRI will enhance the diagnosis in patients with metallic compounds.
8	Xu et al. (2015) [57]	3 metals and 2 ceramics, fabricated to same size and thickness of incisor crown	Different sequences of 3 MRI field strengths: 0.35, 1.5 & 3 T–T1WI & T2WI images.	No artifacts were found for Zr crowns; for casting ceramic, they were minimal. All dental precious metal alloys, Ni-Cr alloy dental porcelain, & Co-Cr ceramic alloy had varying degrees of artifacts.	Zr & casting ceramics presented almost no or faint artifacts. By contrast, precious metal alloys, Ni-Cr alloy dental porcelain and Co-Cr ceramic alloy displayed MRI artifacts. The artifact area increased with the strength of the magnetic field.
	[Article in Chinese]
9	Cortes et al. (2015) [58]	Ni-Cr metal-ceramic restorations (i.e., dental crowns & fixed bridges) and cylindrical reference specimens	1.5 & 3 T MRI scanners; GRE, SE & UTE pulse sequences.	A significant correlation was found between TE and artifact area in GRE images. Higher receiver bandwidth significantly reduced artifact area in SE images. UTE images yielded smallest artifact area at 1.5 T. Significant differences were found in the mean artifact area between 1.5 & 3 T images and between images from GRE & SE pulse sequences.	A significant correlation found between TE and artifact area in GRE images. It is possible to compensate for the effect of higher field strength on MRI artifacts by setting optimized pulse sequences for scanning patients with metal-ceramic restorations.
10	Shalish et al. (2015) [59]	2 commonly used fixed retainers: Twistflex & Ortho Flex Tech retainers.	1.5 to 3 T; SE sequence; T1- & T2-weighted sequence.	Ortho Flex Tech retainers caused no distortion. Twistflex retainers caused distortion (46%) in areas close to the retainer (tongue, jaws). Maxillary fixed retainers & maxillary-mandibular fixed retainer combination further increased distortion. Greater distortion was seen with 3 T magnetic fields & T1-weighted SE sequences.	Removal of Ortho Flex Tech retainer is unnecessary before MRI. Removal of Twistflex should be considered if MRI scans are performed to diagnose areas close to fixed retainers, when 3 T magnetic fields and T1-weighted sequences are used, and when both maxillary & mandibular fixed retainers are present.
11	Zachriat et al. (2015) [60]	Ceramic brackets & S.S. brackets	1.5 T MRI of head & neck region; different types of MR sequences (EPI, TSE and TSE-WARP, GRE).	In vitro: Artifact radii of 1.12 (ceramic brackets) and 7.4 cm (ferromagnetic steel brackets). WARP reduced artifacts by 32.7%.	In vitro measurements allow estimation of in vivo artifact size. Orthodontic appliances may often remain intraorally when performing MRI. WARP showed more significant effect in vitro than in vivo.
				In vivo: EPI sequence for brain imaging was not analyzable. The TSE sequence of the brain had no artifacts except for the nasal cavity. The TSE sequence of the cervical spine had severe artifacts in the midface region. The GRE sequence was more susceptible to artifacts than TSE.
12	Wylezinska et al. (2015) [61]	S.S. arch wire, brackets & molar bands; appliances/reinforcement with Ni/Ti alloys.	0.5 T scanner using standard spin & GRE sequences. Craniofacial region, with special interest in soft palate and velopharyngeal wall (real-time speech imaging) & TMJ & pituitaries (anatomical imaging).	The most extensive effects were associated with S.S. arch wire, particularly if combined with S.S. brackets & S.S. molar bands (diagnostic quality severely degraded). All non-metallic, non-metallic with Ni/Cr reinforcement, or Ni/Ti alloys appliances were of little concern.	Appliances manufactured from S.S. cause extensive artifacts, which may render the image non-diagnostic. The presence and type of orthodontic appliances should be always included in patient's screening, so risks of artifacts can be assessed prior to imaging. Although risks to patients with fixed orthodontic appliances at 1.5 T are low, their secure attachment should be confirmed.
13	Blankenstein et al. (2015) [62]	16 orthodontic small-device and wire specimens made of different steel and Ti or Co-Cr alloys	SE and GRE sequences at 1.5 & 3 T.	Artifact formation depends on material properties (specimen size, crystalline structure, processing) & MRI specifications (main field strength, sequence type). Artifact radii ranged from 14 mm (SE, 1.5 T) to 51 mm (GRE, 3 T). No artifacts at 1.5 T around Ti & Co-Cr specimens; the same observation was made with 1 of the steel grades.	Artifact size cannot be predicted merely from the designation ‘steel’ or from crystalline structure. Relevant is the magnetic permeability (or susceptibility) of the final products, which is not disclosed by manufacturers, and it cannot be measured in fixed intraoral appliances. Some steel devices can remain in situ without triggering adverse consequences.
14	Beau et al. (2015) [23]	60 patients requiring head MRI scan for medical reasons were given one of 4 types of fixed attachments: S.S., Ti, ceramic brackets with metal slots, & S.S. retainers	Each patient had 2 scans at 1.5 T; the 4 areas under investigation were maxillary sinus, oral cavity, TMJ, & posterior cerebral fossa.	S.S. brackets always caused non-interpretability of all anatomic areas (100%). Ti brackets, ceramic brackets with metal slots, and S.S. retainers caused artifacts in the oral cavity only (for 20%, 16.65%, and 86.65% of subjects).	Ceramic brackets with metal slots & Ti brackets do not always have to be removed before head & neck MRI, depending on the investigation area. Metal fixed retainers are to be removed if the oral cavity itself is under investigation. S.S. brackets are to always be removed before head & neck MRI.
15	Duttenhoefer et al. (2015) [63]	Ti & Zr implants embedded in 10% (w/v) gelatin phantoms (MRI), or post-implantation (micro-CT)	3 T MRI; T1-weighted TSE & T2-weighted TSE sequences.	Post-implantation, while Ti implants induced a strong B0-field distortion resulting in extensive signal voids, Zr implants were clearly depicted with only minor distortions.	Excellent contrast, limited artifacts, radiation-free and accurate implant assessment indicate that MRI is a valuable imaging alternative for Zr implants.
16	Fang et al. (2014) [64]	6 casting alloy post & cores (Zr post & core – control). All 7 types of post & cores were of same the size & shape	T1-weighted SE imaging (SE-T1WI), T2-weighted turbo spin-echo imaging (TSE-T2WI), and DWI.	Co-Cr alloy post & core generated severe artifacts, whereas Au-Pd alloy post & core generated no obvious artifacts, & no difference was seen between the Zr & Au-Pd alloy post & cores. Pure Ti alloy post & core produced mild artifacts. Post & cores of Ti, Ni-Cd, & Au-Pt alloys generated moderate artifacts.	Different metal post & cores had different influences on MRI. With exception of that generated by Co-Cr alloy, the artifacts generated by single-alloy post & core did not influence normal head & neck imaging.
	[Article in Chinese]
17	Sinkiewicz et al. (2013) [7]	Orthodontic appliances	-	-	This review article gave recommendations for the removal or retention of orthodontic appliances during MR imaging.
18	Tymofiyeva et al. (2013) [12]	A series of standard dental materials was studied & their magnetic susceptibility was estimated	1.5 T MRI system using SE and GRE pulse sequences.	Materials were classified as fully compatible (material can be present even in tooth of interest), compatible I, & non-compatible (material should not be present in patient's mouth for any dental MRI applications).	A material classification that complies with the standard grouping of materials according to their magnetic susceptibility can serve as a guideline in future dental MRI research.
19	Taniyama et al. (2010) [65]	Non-magnetic metal (type-4 gold alloy ring) that was intact or cut	2 T MRI; excitation RF field was along the x-axis, with RF-receiver coil in the y-z plane. T1 (spin-lattice relaxation time)-weighted images.	For the intact gold ring, a portion around the ring disappeared. It was nearly restored with a cut ring. Artifacts appeared when the circumferential surface of the ring was placed perpendicular to the RF field of MRI. However, in other directions or with a cut ring, the artifact disappeared.	This demonstrated the characteristics and cause of artifacts by non-magnetic dental metals. An alternating magnetic field was shown to induce a surface current that interfered with the field on the continuous gold ring.
20	Costa et al. (2009) [27]	Retrospective study of 1,200 medical records of epileptics who underwent MRI. 70 MR images with artifacts were retrieved & reviewed	MRI acquisition parameters were: 1) sagittal T1 SE; 2) coronal images, T1-weighted inversion recovery; 3) axial images, T1-weighted GRE.	The artifact image plane was given a score of 0 or 1 (0 = distinguishable for diagnosis; 1 = not distinguishable). 78% of artifacts were caused by orthodontic appliances (the highest scores in all planes), followed by dental Ti implants (18%) & metallic crowns (4%).	It is difficult to avoid the effects of metallic artifacts in maxillofacial regions on brain scans. Removing the metallic parts of orthodontic appliance should ensure diagnostically useful scans.
		Metallic objects were dental (Au) crowns, dental Ti implants, & metallic orthodontic appliances (bands, brackets, arch wires)	a) T1-weighted GRE; b) FLAIR.
21	Hunt et al. (2009) [18]	-	-	-	In this letter to the editor, the authors contemplated the use of Essix trays to fit over bonded canine-to-canine retainers or other fixed attachments prior to MRI to prevent appliance dislodgement. They also suggested the use of TMA wire for fixed retainers.
22	Elison et al. (2008) [66]	10 subjects received 5 consecutive cranial MR scans. A control scan was conducted with Essix trays fitted over the maxillary & mandibular teeth. 4 experimental head MR scans were done with plastic, ceramic, Ti, & S.S. brackets incorporated into Essix tray material	Each MR scan consisted of 4 sequences: sagittal T1-weighted SE (T1 sagittal), axial T2-weighted SE (T2 axial), GRE & DWI.	Statistically significant difference between the distortion scores of S.S. brackets & those of other experimental MR scans.	Plastic, ceramic & Ti brackets caused minimal distortion of cranial MR images. However, S.S. brackets caused significant distortion (cranial regions were non-diagnostic). The areas with the most distortion were the mandible body, hard palate, base of tongue, globes, nasopharynx & frontal lobes. The closer the S.S. appliance was to a specific anatomic region, the greater MR image distortion was found.
23	Hu et al. (2008) [17]	-	-	-	This review article concluded that FPDs produced artifacts in MRI, thus reducing image quality when patients with a metallic prosthesis in mouth undergo head & neck MRI. However, these FPDs cannot be removed arbitrarily.
	[Article in Chinese]
24	Destine et al. (2008) [28]	1 pre-fabricated magnetic keeper and 4 clinical dental alloys (Au-Ag-Pa, casting Au alloy type 3, Co-Cr, Au porcelain alloy); in total, 2 metal crowns & 5 magnetic keepers were analyzed	1.5 T MRI apparatus; in axial, coronal, & sagittal planes; T1-weighted SE sequence (TR/TE) & T2-weighted TSE sequence were used.	Co-Cr showed greater signal intensity, up to 40 mm in coronal T2WI images & 70 mm in axial T1WI images for the magnetic keeper. The signal intensities of Au-Ag-Pa & casting Au alloy type 3 were similar to the control. The signal intensity of Au-porcelain alloy was different from the control at 0 mm & 5 mm in coronal T1, T2WI & in sagittal T1WI at 0 mm.	The artifacts generated by the magnetic keeper and Co-Cr crown when they were used in a second molar could disturb MR images of the TMJ.
25	Starčuková et al. (2008) [34]	Magnetic susceptibility, electrical conductivity and artifacts were evaluated for 45 cylindrical standardized samples of dental alloys and amalgam.	Artifact sizes were measured in SE and GRE images at 1.5 T according to the standards of the American Society for Testing and Materials.	Short-echo-time GRE imaging is possible even at very close distances from dental devices made of amalgam, precious alloys & Ti alloys. Ni-Cr & Co-Cr artifacts were still acceptable, but large restorations of Al-bronzes preclude orofacial imaging. Influence of electrical conductivity on artifact size was negligible.	Dental materials differ considerably in their magnetic susceptibility, electrical conductivity and artifacts. For dental devices, magnetic susceptibility differences are of little clinical importance for diagnostic SE/GRE imaging of the neck and brain, but are significant for orofacial imaging. MRI is possible even close to dental devices if they are made of dental materials with low magnetic susceptibility. Not all materials in current use meet this requirement.
		Magnetic susceptibility and electrical conductivity were determined.
26	Blankenstein et al. (2006) [67]	5 standard dental magnet attachments with volumes of 6.5–31.4 mm3: NdFeB magnet with open magnetic field, NdFeB magnet with closed magnetic field, SmCo magnet with open magnetic field, S.S. keeper (AUM-20) & PdCo piece	1.5 T & 3 T MRI; gradient-echo and T1- & T2-weighted SE sequence.	In gradient-echo images, artifacts were substantially larger and symmetrically adjusted around the object. Areas with total signal loss were mushroom-like. In SE images, the signal loss areas were smaller, but not centered. Different ferromagnetic attachments had no clinically relevant influence on the signal loss in either 1.5 T or 3 T MRI.	Ferromagnetic materials used in dentistry are not intraorally standardized. To ensure that the area of interest is not affected by artifacts, the maximum extent of the signal loss area should be assumed: a radius of up to 7 cm in 1.5 & 3 T MRI by T1 & T2 sequences, and a radius of up to 10 cm in T2 sequences. To decide whether magnet attachments have to be removed before MRI, physicians should consider both the intact retention of keepers and safety distance between ferromagnetic objects and the area of interest.
	[Article in German]
27	Hubálková et al. (2006) [16]	-	-	-	This review article concluded that MRI causes movement or heating of metal objects (with positive magnetic properties) present in the body, which can lead to health risks. The safety & MRI compatibility of dental alloys must always be considered prior to MRI.
28	Harris et al. (2006) [68]	A patient undergoing orthodontic treatment who required repeated MRI scans on a regular basis	-	S.S. & other metallic orthodontic appliances created substantial artifacts & obliterated details in the facial area. Ceramic brackets & directly-bonded metal tubes did not affect MRI scan diagnostic quality.	The authors concluded that metallic orthodontic appliances in the head & neck region can distort MR images, thus reducing their value. Aesthetic brackets (no metal components and arch wires removed) do not distort MRI scans.
29	Shafiei et al. (2003) [32]	11 dental casting or implant materials were imaged	1.5 T MRI apparatus with 3 different sequences.	A variety of artifacts with different magnitudes was observed. Only 1 sample, composed mainly of Pa, In, & antimony (Sb), showed no artifacts in any imaging sequences.	Selecting specific dental casting alloys according to their elemental compositions can minimize metal artifacts in MRI; however, Ti alloys currently pose a problem with respect to causing MRI artifacts.
30	Okano et al. (2003) [69]	MR imaging was performed in 20 TMJs before and after insertion of 6 kinds of orthodontic appliances (ceramic/metal brackets; directly-bonded tube/band tube; +/− S.S. arch wires)	-	For disk position, diagnostic accuracy was 70%–80% (ceramic/metal brackets with no S.S. arch wires), & 60%–70% with S.S. arch wires. For condylar configurations, accuracy was 80% (ceramic brackets & directly-bonded tube), 55% (metal brackets & directly-bonded tube), 40% (metal brackets & band tube), reduced to 10%–40% in the presence of S.S. arch wires. No significant changes were found in the condylar head marrow signals.	MRI should preferably be performed in orthodontic patients by using ceramic brackets in the front teeth & direct bonding tubes in molars, while removing arch wires.
31	Hubálková et al. (2002) [70]	15 dental alloys, 4 dental implants, 1 surgical splint & 2 wires for fixation of maxillofacial fractures	-	Artifacts were significant: for surgical splints, a spherical artifact of 55 mm in diameter; for wires, up to 22 mm; & for the dental blade implant, a 28 × 20 mm artifact.	Although the selected dental appliances are safe when present in patients undergoing MRI, artifacts can substantially influence MRI results.
32	Savane et al. (2001) [71]	Ti implants	1.5 T MR unit, with 2 commonly used sequences (SE,GRE)	Minor artifacts, without distortions	In order to minimize ‘ghost images’, Ti and its alloys should be an alternative.
	[Article in French]
33	Abbaszadeh et al. (2000) [25]	Dental Au, amalgam, S.S., Ti, Ag-Pa, & vitallium	T1-weighted MR imaging.	All metallic objects produced artifacts. Artifacts were most pronounced in the central plane of the object. Au produced the greatest artifacts; amalgam produced the least.	Because metals commonly used in the maxillofacial region produce artifacts on MR images, avoidance measures should be used to minimize these artifacts.
34	Tetsumura et al. (1999) [72]	Minute metallic particles deposited during surgery may cause artifacts — 4 types of cutting instruments were used to cut an extracted tooth: a diamond bur attached to a rotor handpiece, a steel bur & bone bur attached to a micromotor handpiece & a bone file	1.5 T; 6 MR sequences: SE, 2 TSE sequences, fast low angle short, turbo gradient SE, turbo inversion recovery sequences.	MR artifacts seen in tooth samples using the bone bur & bone file, but not the diamond & steel burs.	Artifacts seen on postoperative MRI were derived from minute metal particles from the bone bur or file used for condylar arthroplasty. Metal artifacts should be considered when interpreting postoperative MR images.
35	Borris et al. (1999) [73]	Large ferromagnetic MRI artifacts were seen in the area of a previous mandibular osteotomy	-	MRI revealed multiple non-uniform halo-appearing teardrop-shaped areas associated with the mandibular ramus in the osteotomy area, visible in axial & coronal views. Surgical exploration revealed several minute hard & soft tissue specimens (foreign bodies).	Even tiny particles distort MR images leading to halo artifacts. Surgeons must be aware of foreign bodies implanted during surgery, and recognize their appearance. Dental restorations usually do not cause artifacts.
36	Devge et al. (1997) [44]	Implants from the Brånemark System were tested	The ferromagnetic properties of implant materials are seldom described by the manufacturer. Important factors are alloy composition, size & shape of the metallic material, and its position in body.	Artifacts caused by implants were minor and did not jeopardize scan evaluation. However, magnet keepers attached to implants caused major artifacts.	Magnet keepers attached to implants must be removed before an implant patient is referred for MRI examination
37	Behr et al. (1996) [74]	Cylindrical samples of 13 alloys & 14 pure substances (in plaster & water-filled acrylic resin phantom-representing disc & TMJ condyle were investigated)	SE & GRE sequence.	Metallic artifacts appeared on SE technique as distortions, and on gradient-echo technique signal loss could be observed. Precious alloys were diamagnetic. Non-precious alloys investigated were paramagnetic.	Paramagnetic alloys produce clinically relevant artifacts.
38	Beuf et al. (1994) [26]	Cylindrical dental alloy samples incorporating gold, silver, and palladium (placed in a Pyrex beaker filled with distilled water)	0.13 T using 2-dimensional Fourier transformation and projection reconstruction at 360° imaging methods.	Only palladium-based alloys were detected to be paramagnetic. One of the silver-based alloys did not induce detectable distortion because its susceptibility was very close to that of distilled water.	Use of this material may be recommended for applications involving MRI evaluation.
39	Iimuro (1994) [75]	Specimens of each material were prepared as spheres & cylinders. Sphere samples with diameters of 1, 2, and 3 mm and 4 mm cylinders of 0.2, 0.3, 0.4, 0.6, 0.8 diameter and 1 mm height were prepared	0.2 T; 3 sequences: short SE (TR-300, TE-38), long SE (TR-500, TE-110) and GRE (TR-200, TE-23, flip angle 60) were used. Images were taken in the coronal, sagittal & transverse planes.	During MRI, artifacts were not caused by the magnet itself, but by the S.S. keeper (ferromagnetic). Short & long SE sequences resulted in the same artifact range (distortion; further from the specimen, distortion was attenuated); the gradient-echo sequence caused a larger image artifact (signal loss/blackout). The image around the most severely deformed area was quite distorted, but the structures could be distinguished.	The higher the magnetic permeability, the greater the artifact produced. The size and volume of the material directly influence the artifact produced. Artifact size can be attenuated by the sequence used to obtain images. In vitro and in vivo results suggest that even in patients with a magnetic attachment system, MRI is the diagnostic method of choice. Possible solutions to reduce the artifact range are to find alternative keeper materials with a lower magnetic permeability; or to design the keeper in such a manner that it can be removed easily.
40	Oikarinen et al. (1993) [76]	4 samples of different sizes of fractured tooth crown, pieces of amalgam, glass, asphalt, composite, dry wood, and stone (embedded in soft tissue)	1 T; T1 and T2 weighted and proton-density images.	MRI was the least suitable imaging method, as particles with a metallic content gave rise to artifacts. Foreign body particles in soft tissue were better defined in form & size with CT & ultrasonography than with MRI or plain radiography.	When plain radiographs, history, and clinical examination fail to reveal the presence of superficial foreign bodies, ultrasonography or CT can serve as an alternative method that is preferable to MRI.
41	Laurell et al. (1989) [77]	8 types of prosthetic magnet keepers of the disc and bar type	1.5 T, with partial saturation pulse sequence.	Image artifacts present in all 8 samples (160–280 mm diameter). Artifacts obliterated vital cranio-cervical areas. For bar keepers & Jackson disc keepers, artifacts partially/totally obliterated eye & brain images. Other disc keepers degraded eye images, but not brain or cervical spine images.	The ferromagnetic potential of magnetic keepers caused sufficient localized alterations of the magnetic field, leading to signal loss. Patients with magnetic keepers requiring comprehensive head & neck MRI must have them removed.
42	Sadowsky et al. (1988) [78]	5 patients with fixed appliances in maxillary & mandibular arches undergoing MRI scans of brain & TMJ	T1-weighted scan; transverse multi-echo sequence of the brain.	Orthodontic appliances produced MR artifacts in the facial region (mouth & maxillary sinus). The frontal & temporal lobes of the brain were most affected, but the degree of the artifact varied from patient to patient. Artifacts were not severe enough to alter the diagnostic scan quality. On TMJ scans, no degradation was detected.	Phantom studies indicated that orthodontic arch wires increased distortion & artifacts. All banded & bonded attachments should be checked for firm attachment to the teeth or passively ligated with elastic chains for added safety. Eliminating all removable components of appliances (arch wires) ensures a diagnostic scan. Complete removal of metallic appliances is not needed unless the region of interest is close to the mouth.

T, tesla; S.S., stainless steel; Ti, titanium; Co-Cr, cobalt-chromium; Zr, zirconium; CT = computed tomography; CBCT, cone-beam computed tomography; SPACE, sampling perfection with application optimized contrasts using different flip angle evolution; TSE, turbo spin-echo; T1W1, T1-weighted; T2W1, T2-weighted; TMJ, temporomandibular joint; Au, gold; Ag, silver; Pd, palladium; Pt, platinum; Cd, cadmium; NdFeB magnet, neodymium iron boron magnet; SmCo magnet, samarium cobalt magnet; PdCo, palladium cobalt magnet; GRE, gradient echo; PFM, porcelain-fused-to-metal; GRASS, gradient-recalled acquisition in steady state; SPGR, spoiled GRASS; Al, aluminum; Ni-Cr, nickel-chromium alloy; FSPGR, fast SPGR; SE, spin-echo; UTE, ultrashort-echo time; TE, echo time; EPI, echoplanar imaging; DWI, diffusion-weighted imaging; RF, radiofrequency; FLAIR, fluid attenuated inversion recovery; FPD, fixed partial denture; TR, repetition time; FIESTA, fast imaging employing steady state; EPI, echo planar imaging.

1. Orthodontic materials: the issue of artifacts

In fixed orthodontic treatment, NiTi and stainless steel arch wires are used with stainless steel brackets (austenitic stainless steel: 18% Cr; 8% Ni) [20]. Since nickel and chromium are ferromagnetic metals, they distort local magnetic fields, causing large artifacts that make image interpretation impossible [27]. Debonding procedures, apart from potentially damaging enamel, are time-consuming, uncomfortable for the patient, and costly [48]. Orthodontists may be asked for recommendations regarding the removal of fixed orthodontic appliances for MRI scans of the head and neck region, and the following guidelines may be useful in that context:

• When firmly bonded and carefully ligated, fixed orthodontic appliances are safe for use in MRI scanners. Steel retainer bonds should be checked prior to the scan to ensure their attachment.

• Leaving a non-ferromagnetic wire in place keeps the brackets together even if the enamel bond fails.

• If the dento-alveolar region is to be studied, the plane of the scan should be altered to avoid the site of metal devices. If not feasible, the orthodontic brackets and wires should be removed [7,21].

• Artifacts may not always interfere with the diagnosis, especially when they are present in areas that are not of interest (Table 6) [22].

Table 6. Recommendations for the removal of orthodontic appliances based on the type of material.

Appliance type	Magnitude of artifact	Recommendations for appliance removal
Ceramic brackets with metal slot and titanium brackets	Very limited or no artifacts	Removal is only necessary if the area under investigation is close to fixed appliances (i.e., in the oral cavity).
Fixed retainers containing steel	Poor image quality in the area of the oral cavity only	Removal is only necessary ahead of an MRI scan if the area under investigation is within the oral cavity.
Stainless steel brackets	Extensive artifacts in the oral cavity and other areas (TMJ, posterior cerebral fossa, maxillary sinus), images uninterpretable	Removal is always necessary before MRI images of the head and neck area are taken.

MRI, magnetic resonance imaging; TMJ, temporomandibular joint.

2. Orthodontic materials: issues regarding physical and mechanical effects

Due to interactions with MRI, metallic objects in the human body can undergo radiofrequency-induced heating. A study by Gorgulu et al. [20] found that the radiofrequency-induced heating of NiTi arch wires and continuous stainless steel ligature wires was statistically significant (3.04°C), but this was not the case for stainless steel arch wires combined with elastic or continuous stainless steel ligatures (≤ 2.12°C). Although this temperature increase was regarded as insufficient to cause pain or damage to periodontal tissues (heat-pain threshold = 8°C–10°C), the authors stated that it would be safer to replace NiTi and stainless steel wires before MRI; however, brackets were considered to be ‘MR safe’ [20].

3. Maxillofacial prostheses

Hasegawa et al. [22] evaluated the behavior of removable partial denture magnetic dental attachments (keeper and copings) in terms of radiofrequency-induced heating and displacement (torque), and arrived at the following conclusions:

• Radiofrequency-induced heating of magnetic dental attachments during 3 T MRI should not pose a risk to patients.

• Since the magnetically-induced torque was within the acceptable limits, but the deflection forces exceeded those limits, ferromagnetic devices should ideally be removed from the oral area before MRI. Since this may not always be possible, for safety purposes, the fixation (cement degradation) of such devices should be inspected before and after MRI [22].

4. Dental implants

Dental implants are made of non-ferromagnetic materials (titanium) and contain traces of ferromagnetic iron, which causes a drop-out of signal near the metallic surface [27,46]. Costa et al. [27] found that titanium implants caused artifacts in all planes, resulting in severe blooming that led to issues in diagnosis, but less so than orthodontic appliances [49]. Other authors reported that titanium caused only minor artifacts and allowed good visualization [6,50]. Devge et al. [44] also found that artifacts caused by implants were minor and did not jeopardize scan evaluation. However, magnet keepers attached to implants caused major artifacts, so they are recommended to be removed before an implant patient is referred for an MRI examination.

5. Direct restorative materials

1) Glass-ionomer cements (GIC)

GIC restorations produce no detectable distortions on MR imaging. They are classified as compatible with MRI (the material produces no detectable distortions; Δx < 3 ppm, Table 3) [8].

2) Composite resin

Tymofiyeva et al. [8] found that the composite resins of some manufacturers were compatible on MRI, whereas other brands were compatible I (the material produces noticeable distortions, with the acceptability depending on the application; 3 < Δx < 200 ppm) (Table 3). Ingredients such as ytterbium trifluoride, ferric oxide, and lanthanum oxide (coloring agents) cause image disturbances in MRI because they are ferromagnetic.

3) Amalgam

Amalgam is composed of several metals (silver, tin, copper, zinc, platinum, palladium, and mercury), with silver being the major component [79]. Dental amalgam alloy has little influence in dental MRI because silver is a diamagnetic (non-ferromagnetic) metal [49]. However, MRI is not completely devoid of any effects on amalgam restorations. Shahidi et al. [80] found a statistically significant increase in microleakage when teeth restored with amalgam were exposed to MRI.

Interestingly, during the setting reaction with mercury, diamagnetic silver becomes paramagnetic [81,82]. Yilmaz et al. [3] studied the effects of a 3 T magnetic field on amalgam restoration materials with different ratios of silver content (40%, 50%, and 70%), and found no significant differences in microleakage between the amalgam types (non-gamma-2 spherical amalgam versus non-gamma-2 admixed amalgam).

6. Indirect restorative materials

1) Gold crowns

The metals commonly used to manufacture crowns are gold, palladium, nickel, and chromium [79]. Although gold is a diamagnetic substance, gold alloys contain traces of other ferromagnetic metals [27]. According to Eggers et al. [29], even small amounts of a ferromagnetic substance can cause an extensive blank in the image. This compositional difference accounts for discrepancies in study results regarding artifact formation with gold crowns. Abbaszadeh et al. [25] found significant image distortion in MRI; whereas Costa et al. [27] found that gold crowns generated little image distortion, visible only in the sagittal plane.

It has been speculated that the only reason why dental gold might produce distortion may be because it supports large eddy currents caused by its high electrical conductivity [6]. Camacho et al. [35] investigated MRI artifacts caused by radiofrequency eddy currents and found substantial artifacts. However, Fache et al. [6] found that the impact of eddy currents was negligible, as a piece of dental gold studied in vitro, and extensive gold restorations in the mouth of a volunteer revealed no distortions on the MRI scanner.

Tymofiyeva et al. [8] classified gold alloy and gold-ceramic crowns as compatible I, with the acceptability depending on the application (Table 3).

2) Ceramic and metal-ceramic crowns

Tymofiyeva et al. [8] classified gold-ceramic crowns as compatible I (Table 3). Precious metal alloys, nickel-chromium alloy, and cobalt-chromium ceramic alloy used as metal copings for dental porcelain display MRI artifacts. The artifact area increases with the strength of the magnetic field.

Cortes et al. [58] analyzed the impact of nickel-chromium metal-ceramic restorations (i.e., dental crowns and fixed bridges) and found a significant correlation between echo time and artifact area in gradient echo pulse sequence images. They suggested that it is possible to compensate for the effect of higher field strength on MRI artifacts by setting optimized pulse sequences for scanning patients with metal-ceramic restorations [59].

Xu et al. [57] found that zirconia and casting ceramics presented almost no or faint artifacts. In contrast, the study by Klinke et al. [46] found that ceramic (zirconium dioxide) led to the same effect as metal-based materials on MRI of the lower mid-face. Wedge-shaped specimens (1 – 3.5 × 9 × 16 mm) of the ceramic materials IPS Empress and Ducera gold showed artifacts less than 15 mm, while Cergo and Vita Omega 900 showed artifacts between 15 and 30 mm, and zirconium dioxide showed artifacts larger than 30 mm (the same as metal alloys).

7. Endodontic materials

Endodontic materials such as resin-based sealer (AH Plus) and gutta-percha produce no detectable distortions on MRI. They are classified as compatible with MRI (Table 3). No data are available on silver cones, or separated NiTi and stainless steel instruments used in root canal therapy [8].

CONCLUSIONS

As MRI is becoming widely used in dentistry, it is critical that dental practitioners are aware of the potential of dental materials to cause adverse interactions during MRI. Dental practitioners must be acquainted with the composition of orthodontic devices, maxillofacial prostheses, implants, direct and indirect restorative materials, and endodontic materials, in order to anticipate complications and take precautions prior to MRI in patients with the aforementioned dental materials.