CFD analysis is initiated by transforming the computer aided design (CAD) geometry into a virtual prototype, through which the time-varying, incompressible and isothermal flow of blood is computed. The flow of blood, assumed to be Newtonian, is modeled by the Navier-Stokes equations, and solved by the Deformable-Spatial-Domain/Stabilized-Space-Time finite element method. A special purpose mesh-update scheme---shear slip mesh update method---is employed to handle the impeller rotation efficiently. The pump flow rate and impeller speed are ramped up from zero to the desired values, and stationary flow state is determined by analyzing the forces on the impeller. Several clinical operating conditions of the pump---combinations of impeller speeds and flow rates---are simulated on meshes of varying refinement levels. Mesh convergence is determined by analyzing the forces on the impeller. The pump characteristics, for example, regions of high shear, are studied with the help of pathlines and velocity vectors. The extent of hemolysis (in terms of normalized index of hemolysis) caused by the flow in the pump is predicted by using a tensor-based blood damage model, which tracks the strain (tensor) experienced by the red blood cells along the pathlines. Regions of high shear and slow-moving flow, which are important for predicting and thereby minimizing platelet activation and thrombosis, are also identified