Personal resource gains: Effective coping builds academic buoyancy, and academic buoyancy builds achievement.

In 2005, an estimated 1.6 million people in the United States were living with limb loss, including approximately 0.6 million with major lower-limb loss. In the Netherlands, 22% of lower limb amputations are performed at the transtibial level, and 14% at the transfemoral level. Transition to a well-fitting prosthesis can enable a person to regain independence and engage in daily activities again. A transtibial prosthesis (i.e., below-knee prosthesis) typically consists of a socket, suspension system, and foot. A transfemoral prosthesis (i.e., above-knee prosthesis) includes these components, together with a knee joint. In both prostheses, the socket serves as an integral interface connecting the human body to the prosthesis. Achieving an optimal socket fit remains one of the main challenges in prosthetic care. Poor fit can cause excessive limb-socket interface stresses and skin problems, aggravated by limb volume changes and heat accumulation within the socket. These issues reduce function and quality of life and often require frequent socket adjustments, increasing clinical workload and health care costs. The process of developing a prosthetic socket involves 3 key phases. First, the shape of the residual limb is captured, referred to here as shape capture. Second, the socket is designed using modifications to obtain a socket with adequate load transfer, referred to here as the socket shape design. Designing the socket consists of different aspects: (1) the socket type (e.g., specific weight-bearing or total surface-bearing socket for transtibial prostheses), (2) the socket shape design (i.e., defining its spatial characteristics and inner surface dimensions in relation to the residual limb shape), and (3) the proximal and distal parts of the socket (i.e., the socket brim and adapter, respectively). Last, the socket is manufactured. This review will focus on the shape capture and socket shape design.