###### Abstract  
The medical imaging of a patient with a cardiac implantable electronic device (CIED) inside a magnetic resonance imaging (MRI) scanner carries the risk of tissue heating at the tip of the implant lead. In this work, we numerically assessed the impact of various factors, namely the resonant frequency, the imaging position, the implant position inside the human body and the coil configuration, on the induced tangential electric field along 10,080 cardiac lead paths at 1140 different scanning scenarios. During this comparative process, a function was considered based on the induced electrical potential at the tip of the lead. The input power of each coil was adjusted to generate constant B1+RMS at the iso-center or to limit the global SAR to the values provided in the safety guidelines IEC 60601-33. The values of the function were higher for higher static field and longer coil lengths when assessing the cases of a constrained B1+RMS, and the trend was reversed considering the limiting SAR values. Moreover, the electric field was higher as the imaging landmark approached the thorax and the neck. It was also shown that both the choice regarding the insertion vein of the lead and the positioning of the implantable pulse generator (IPG) affected the induced tangential electric field along the paths. In particular, when the CIED lead was inserted into the left axillary vein instead of entering into the right subclavian vein, the electrical potential at the tip could be on average lower by 1.6 dB and 2.1 dB at 1.5 T and 3 T, respectively. cardiac lead; tangential electric field; coil configuration; imaging position; human body 4.0.0000-0002-0002-0000-0000-0000-0000-0000-0000-00000-00000-00000-00000-00000-00000-00000-00000-00000-00000-00000-00000-00000-000000-000000-000000-  
medical devices (AIMDs), where electrodes are located [4]. However, it is estimated that more than 50% of patients with implanted medical devices will require an MRI exam during their lifetime [5]. Therefore, many previous studies reported in vitro measurements of the induced heating at the tip of a pacemaker implant [6; 7] and in vivo measurements [8] for specific electrodes, MRI systems and conditions. In addition, previous works have studied several factors that influence the amount of heating at the lead tip, such as the lead geometry [9; 10], the conductivity of the medium at the lead tip [11; 12], the location of the implant inside the body [13], the coil [14; 15] and the MR systems [16; 17]. In these studies, temperature measurements were evaluated in homogenous phantoms in 1.5 T coils, and, in the majority of the cases, the lead configurations did not reflect realistic clinical scenarios since the positioning of the device inside a phantom cannot reproduce specific clinical pathways. Therefore, because of the high degree of complexity during the interaction between the MRI coil and the implant, the results of previous works measured in homogenous phantoms might not provide enough confidence regarding patients' safety as the patient's body composition alters the RF power deposition in the tissue surrounding implanted leads [18; 19; 20; 21; 22; 23]. In [24], the RF-induced electric field inside a homogenous phantom was assessed, demonstrating a different spatial distribution compared to the respective distribution inside a human model [25]. In addition, in [26], the induced E-fields along paths of typical implants inside patient models were compared to those induced in the ASTM phantom and it was concluded that the phantom was not always conservative relative to clinical exposures. Furthermore, ref. [27] presented a database of MRI-induced heating measurements quantifying the contributions of the above factors showing in addition that the temperature increase inside a human-shaped phantom was lower than in a rectangular model, emphasizing the effect of the morphological properties of a model in addition to the properties of its material.