## 1 Introduction and Related Works
Additionally, these steels may corrode in high-chloride or acidic environments, compromising implant integrity over time. Fatigue and mechanical stress can further weaken the material, forming cracks and eventual structural failure [13; 14]. The causes of endoprosthesis failure have evolved. Historical data suggest that some failure mechanisms have been mitigated through implant design and material selection improvements [15; 16]. Data from the Norwegian Hip Registry indicate that aseptic loosening decreased between 1987 and 2007, attributed to the widespread use of well-documented implants. However, during the same period, infection rates and dislocation cases increased. Preventing implant failure remains a crucial priority, as inadequate material quality can lead to fatigue and cracking [17; 18]. Early diagnosis is essential to avoid complete failure, and a thorough understanding of materials science and electromagnetism can aid in detecting potential damage at an early stage [19]. Ref. [20] studied the effect of crack tip constraint in terms of the thickness and initial crack size on the failure behavior of AISI 316L. Fracture tests were performed, and the crack extension for the resistance curve method due to deviating from the standard was evaluated. The failure of the samples was also assessed using the Failure Assessment Diagram (FAD). The results showed that unloading compliance underestimates the crack extension in the presence of significant plastic deformation of the samples and that the plastic collapse occurs in all samples before the crack grows in the blunting regime. Another research group investigated the effects of tempering and cryogenic heat treatment on grain orientation and a few key mechanical parameters of austenitic stainless steel 304. The experiment outcomes demonstrated that various heat treatment techniques can be used to modify and enhance the mechanical properties of AISI 304 to suit a particular need. Their findings demonstrated that in comparison to tempered samples, which provided the best tensile strength, hardness, and minimum percentage of elongation in length value, cryogenically treated samples exhibited the lowest tensile strength, hardness, and highest percentage of elongation value [21]. In refs. [22; 23], a failure investigation of a cemented femoral stem hip implant made of double-tapered stainless steel 316L was carried out. Fracture tomography, visual observations, material characterization, and morphological analysis were performed to verify fatigue as the failure mechanism. The fatigue initiation point was a surface flaw or defect that formed an indentation on the upper portion of the stem's neck. The pattern of the beach markings, which showed the development of two separate regions, \"rough\" and \"smooth\", which evolved more quickly and slowly, respectively, indicates that low cycle loads were most likely the cause of the failure. The impact of deformation on the magnetic characteristics of high interstitial steel FeCr18.2 Mn18.9-0.96C + N at low temperatures was examined in ref. [24]. Tensile testing started at room temperature and stopped at 10, 20, and 30% deformations. Vibrating Sample Magnetometry (VSM) was used to quantify magnetic fields. Microstructural, morphological, and crystalline structural investigations revealed that the material was homogeneous and stably austenitic in structure, lacking \(\alpha\)- or \(\varepsilon\)-martensite. Below Neel temperature, the material displays a paramagnetic/antiferromagnetic transition. It was measured that the distorted material's magnetization and magnetic susceptibility had decreased. The magnetic contribution was determined to impact the SFE of about 5 mJ/m\({}^{2}\). Ref. [25] examined the impact of austenite stability on the microstructure and mechanical characteristics of three types of austenitic stainless steel during cold rolling. Samples with varying grain sizes characterized the microstructures during deformation.