The first roller pump was patented in 1855 by Porter and Bradley and was hand operated. A modification first named "surgical pump", designed and manufactured by E. E. Allen in 1887, was intended for direct blood transfusion. Truax, who also distributed and promoted the Allen pump with one roller, developed the first double roller pump in 1899. In the following decades, several researchers, including Beck, Van Allen, Bayliss and Müller as well as Henry and Jouvelet, refined the apparatus and recommended the use of roller pumps for blood transfusion and other applications. After further modifications made by DeBakey in 1934, and application of this pump in one of the first heart-lung machines constructed by Gibbon, DeBakey's name became inseparably attached to this type of pump. For perfusion experiments, an electrically powered roller pump was first used by Fleisch in 1935. Today, the roller pump is the most frequently used blood pump for cardiopulmonary bypass worldwide, having prevailed against the early pulsatile tube compression pumps and ventricular pumps. In recent years, centrifugal pumps have increasingly competed with roller pumps as systemic blood pumps for cardiopulmonary bypass and have become the preferred arterial pump in a variety of centers. Application of mechanical cardiac assistance has evolved from nonpulsatile roller pump support, followed by an era of pulsatile ventricular pumps to the rediscovery of the nonpulsatile flow mode with modern axial flow pumps.
- This study assessed how well different types of arterial and venous cannulae perform in a pediatric ECMO setup under both pulsatile and non-pulsatile flow conditions.
- The researchers found that in pulsatile flow, lower pump speeds were needed, and the flow increase in the mock circuit was less significant, while non-pulsatile conditions resulted in higher pressures and overall energy levels.
- The conclusion suggested that non-pulsatile conditions offer better support with higher total hemodynamic energy, but pulsatile conditions are more physiological and are recommended for testing ECMO systems.
Soft peristaltic pumps, which use soft ring actuators instead of mechanical pistons or rollers, offer advantages in transporting liquids with non-uniform solids, such as slurry, food, and sewage. Recent advances in 3D printing with flexible thermoplastic polyurethane (TPU) present the potential for single-step fabrication of these pumps, distinguished from handcrafted, multistep traditional silicone casting methods. However, because of the relatively high hardness of TPU, TPU-based soft peristaltic pumps contract insufficiently and thus cannot perform as well as silicone-based ones.
Objectives: Extracorporeal circulation induces pronounced effects on haemostasis and rheology. To study these, an ex vivo simulation model is an attractive alternative but often requires large amounts of blood. We sought to create a miniaturized roller pump circuit requiring minimal amounts of blood and to test if the circuit could be used to compare coagulation, platelet function and blood rheology between a dextran-based and a crystalloid-based priming solution.
Background: To accommodate a wider range of medical device sizes, a larger in vitro flow loop thrombogenicity test system using 9.5 -mm inner diameter (ID) tubing was developed and evaluated based on our previously established 6.4 -mm ID tubing system.
