## 1 Introduction  
Close kinetic chain foot hyper--or over--promation refers to a common misalignment of the foot characterized by an excessive inward rolling of the foot, often accompanied by a flattening of the medial arch during weight-bearing activities [1]. This misalignment primarily affects the subtalar joint, the main site of normal pronation [2], and influences all joints distal and proximal to it, as the foot, according to the regional interdependence model is part of an interconnected skeletal system of muscles, tendons, and fascia, linking distant body regions [3]. Foot hyperpronation is typically associated with altered movements of joints located centrally to the subtalar joint, including internal rotation of the tibia, femur, and pelvis as well as anterior pelvic tilt, while distally, it is linked to hallmark valgus [4, 5, 6]. These biomechanical changes increase stress within the joints of the lower extremity kinetic chain and related structures, often causing musculoskeletal pain due to excessive strain on the surrounding tissues. Ultimately, these changes may predispose individuals to overuse injuries such as plantar fascitis, shin splints, and knee pain [6; 7; 8; 9; 10], exacerbating functional impairments and reducing mobility. Improper positioning of lower limb joints can also significantly alter walking and running patterns, compromising overall biomechanics and increasing the long-term risk of musculoskeletal pathologies such as knee osteoarthritis [11]. Assessing foot hyperporation is a standard component of clinical evaluation for many healthcare providers, aiming to identify potential injury causes or develop preventive intervention programs. This process often includes evaluating the foot's static posture and alignment through various methods [12], which may not be fully capable of capturing the dynamic nature of foot hyperporation during functional activities such as gait, where movements occur as part of complex joint motion. Such challenges have been addressed through kinematic analysis methods [13; 14; 15; 16; 17], which provide accurate measurements but at the cost of being time-consuming, expensive, and requiring specialized equipment and expertise for data interpretation. In recent years, the introduction of advanced methods, such as sensor technology [18], has provided the necessary validity and reliability in gait analysis [19], comparable to more demanding techniques used in kinematic and kinetic gait analysis, especially in the field of healthcare and medicine [20]. These sensors typically form matrices embedded in insoles, mats, or platforms [18], allowing for the generation of detailed spatial maps of the vertical ground reaction forces (vGRFs) exerted across different regions of the foot during various activities. By operating at high sampling rates [21], they can simultaneously detect rapid changes in vGRFs over time during dynamic movements. Furthermore, if the experimental setup allows, they can also yield information regarding spatiotemporal gait parameters using appropriate algorithms [22]. In this context, some researchers have conducted gait analysis on individuals with hyperporated feet by recording real-time measurements of the forces exerted by the foot, either using insoles during shot overground walking [23], or during shot and unshot walking on pressure mats [24; 25]. Despite the ability to accurately analyze gait, the use of insoles and pressure mats lack the capability to control gait characteristics and present several limitations, including fitting and footwear design/type issues (for insoles), as well as space requirements (for mats). The majority of other investigators have assessed overground walking using pressure sensor networks with matrices embedded within single-foot pressure platforms [26; 27; 28; 29]. These small-sized platforms are designed to accommodate only one foot at a time, making them suitable for dynamic activities like gait analysis, but not for running analysis.