Biomedical implants with graded elastic modulus are promising alternatives to simultaneously minimize the stress shielding effect and shear-stresses, that evolve from high and low implant stiffness, respectively. To optimize stress distribution, the elastic modulus tailoring of Ti-35Nb-xSn (wt%) alloys, processed by laser remelting and by laser welding to Ti-6Al-4V, is investigated in this thesis, along with the resulting corrosion resistance. Results show that the elastic modulus of Ti-35Nb and Ti-35Nb-2Sn alloys can be locally increased in up to 20 GPa by laser remelting, with no detriment to corrosion resistance. In these alloys, the elastic modulus was reduced to 58 and 52 GPa, respectively, due to abundant formation of stress-induced ?" martensite with ?" texture during cold rolling. With laser remelting, reversion of stress-induced ?" martensite occurred in fusion zone (FZ) and heat affected zones (HAZ), where the elastic modulus was reestablished. Small Sn additions promoted solid solution strengthening and increased the corrosion potential, by stabilization of the more noble ? phase. The elastic modulus was also successfully modeled by laser welding of Ti-35Nb to Ti-6Al-4V. A gradual increase from about 58 GPa, in the base metal of Ti-35Nb, up to about 117 GPa, in Ti-6Al-4V alloy, was observed due to reversion of stress-induced martensite and progressive increase in the fraction of the stiff ?/?' phases, with chemical composition changes. This welded joint presented low corrosion potential differences between adjacent zones, minimizing the susceptibility of galvanic corrosion. Although 4 wt% Sn reduced the elastic modulus of homogenized and quenched alloys to about 63 GPa, by suppression of ? phase formation, it stabilized ? phase and prevented further elastic modulus reduction by stress-induced martensitic transformation. Nevertheless, the elastic modulus of this alloy could be locally increased up to 110 GPa, by laser remelting with low protective gas flow, due to local increase in the content of interstitials. In Ti-35Nb-4Sn alloy, despite solid solution strengthening, the mechanical resistance was decreased by suppression of second phase formation (? and ?" martensite) and by microstructure coarsening after laser processing, due to a reduced melting temperature. As Sn accelerates dissolution of the passive film, Ti-35Nb-4Sn alloy developed higher corrosion current densities and lower polarization resistance. Besides, in FZ, chemical composition partitioning led to preferential pitting corrosion in Sn enriched interdendritic regions and shifted the corrosion potential to more negative values, making FZ anodic. In the welded joints of Ti-6Al-4V and Ti-35Nb-2Sn and Ti-35Nb-4Sn alloys, corrosion potential difference between FZ and HAZ of Ti-35Nb-xSn alloys reached up to 70 and 120 mV, respectively, increasing the susceptibility of galvanic corrosion in fusion zone. These results contribute to engineer Ti alloys with graded elastic modulus for biomedical applications.