Abstract
Abstract Woven compression bandage (CB) is one of the elastic textiles that exert pressure on muscles. With a defined tensile strength, it is possible to create the required compression on the given body parts. This work aims to investigate the relationship between woven fabric deformation, porosity, and tensile stress properties of three main types of woven CBs. All bandage samples are applied on human leg using two- and three-layer bandaging techniques. Bandage porosity is calculated for all frames at different weave angles using NIS software. Woven bandage construction parameters which are given by the preparation of warp and weft yarns, twist, count, and density along with woven fabric weave, type of weaving, and finishing process are the main factors that influence the bandage properties. Several methods considering thread distributions have been developed to determine the woven fabric's porosity during the tensile stress. Experimental results confirm that bandage porosity is directly proportional to the bandage extension and weave angle that ranges from 44° to 90°. The novelty of candidate study is to introduce practical remarks to the patient for optimizing the required bandage pressure by suitable extension or applied tension or weave angle for two- and three-layer bandaging systems.
Highlights
IntroductionMedical textiles and garments are designed to meet both the safety and the comfort of human beings [1, 2]
compression bandage (CB) are produced with optimum stretch using highly twisted warp yarns such as 100% cotton or elastomeric filament (Lycra or Spandex) with cotton or viscose such as cotton/polyamide/ polyurethane (CO-PA-PU) or using two or more polymeric yarns having different melting points such as viscose/polyamide (VIPA) by steaming heat setting
The factors affecting bandage porosity such as warp and weft yarn count, density, twist, cover factor (CF), and fabric structure are changing during bandage extension
Summary
Medical textiles and garments are designed to meet both the safety and the comfort of human beings [1, 2]. Fabric porosity can be defined as follows: the volume of voids among fibers [3, 4]. Medical compression bandages (MCBs) are the cornerstone in the treatment of chronic venous ulcers. MCBs aim to provide graduated compression to the lower limb from the ankle to the knee to improve venous return, accelerate venous flow, reduce venous reflux by realignment of valves, improve venous pump action, and reduce edema [5, 6]. To design effective compression bandages (CBs), researchers have attempted to describe the interface pressure applied by these bandages using mathematical models [6,7,8,9]. CBs are produced with optimum stretch using highly twisted warp yarns such as 100% cotton or elastomeric filament (Lycra or Spandex) with cotton or viscose such as cotton/polyamide/ polyurethane (CO-PA-PU) or using two or more polymeric yarns having different melting points such as viscose/polyamide (VIPA) by steaming heat setting
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