Introduction Commercial membrane lungs are designed to transfer a specific amount of oxygen per unit of venous blood flow. Membrane lungs are much more efficient at removing CO2 than adding oxygen but the range of CO2 transfer is rarely reported. Methods Commercial membrane lungs were studied with the goal of evaluating CO2 removal capacity. CO2 removal was measured in 4 commercial membrane lungs under standardized conditions. Conclusion CO2 clearance can be greater than 4 times that of oxygen at a given blood flow when the gas to blood flow ratio is elevated to 4:1 or 8:1. The CO2 clearance was less dependent on surface area and configuration than oxygen transfer. Any ECMO system can be used for selective CO2 removal.

The most common technical complication during ECMO is clot formation. A large clot inside a membrane oxygenator reduces effective membrane surface area and therefore gas transfer capabilities, and restricts blood flow through the device, resulting in an increased membrane oxygenator pressure drop (dpMO). The reasons for thrombotic events are manifold and highly patient specific. Thrombus formation inside the oxygenator during ECMO is usually unpredictable and remains an unsolved problem. Clot sizes and positions are well documented in literature for the Maquet Quadrox-i Adult oxygenator based on CT data extracted from devices after patient treatment. Based on this data, the present study was designed to investigate the effects of large clots on purely technical parameters, for example, dpMO and gas transfer. Therefore, medical grade silicone was injected into the fiber bundle of the devices to replicate large clot positions and sizes. A total of six devices were tested in vitro with silicone clot volumes of 0, 30, 40, 50, 65, and 85 mL in accordance with ISO 7199. Gas transfer was measured by sampling blood pre and post device, as well as by sampling the exhaust gas at the devices' outlet at blood flow rates of 0.5, 2.5, and 5.0 L/min. Pre and post device pressure was monitored to calculate the dpMO at the different blood flow rates. The dpMO was found to be a reliable parameter to indicate a large clot only in already advanced "clotting stages." The CO concentration in the exhaust gas, however, was found to be sensitive to even small clot sizes and at low blood flows. Exhaust gas CO concentration can be monitored continuously and without any risks for the patient during ECMO therapy to provide additional information on the endurance of the oxygenator. This may help detect a clot formation and growth inside a membrane oxygenator during ECMO even if the increase in dpMO remains moderate.

Under physiological conditions, up to 97% of the oxygen in blood that is transported from lungs to tissue is bound to hemoglobin. To predict oxygen transfer in artificial lungs on a membrane fiber level with computational fluid dynamics (CFD), previous investigators have incorporated the hemoglobin-oxygen interaction into an effective diffusivity coefficient to modify the convection-diffusion equation. Based on our own simulations and experiments, these approaches tend to significantly overestimate the oxygen transfer. The present study introduces a novel approach to model the oxygen transfer in blood on a fiber level with CFD. Plasma and red blood cells were implemented as two phases and the reaction of hemoglobin and oxygen to oxyhemoglobin was included in the convection-diffusion equation in form of a source term. The model was implemented with the commercial software Ansys CFX 18.1. CFD simulations were compared with in vitro experiments on three micro oxygenators with a staggered fiber configuration under multiple blood flow conditions. To calibrate the model, a reaction rate R was introduced and experimental data was fitted to a blood flow of 50 mL/h. Our model approximated the oxygen transfer rates with a difference, relative to in vitro results, of -23.7 and +6.3% for blood flows of 20 and 90 mL/h, respectively. The effective diffusivity model, used by previous authors, was implemented for comparison and approximated oxygen transfer rates with a difference, relative to in vitro data, of +13.7, +68.8, and +121.0% for blood flows of 20, 50, and 90 mL/h, respectively. A well-established numerical mass transfer correlation approximated the gas transfer with a difference, referenced on the average in vitro data, of 31.8, 13.1, and 5.0% for blood flows of 20, 50, and 90 mL/h, respectively. Even though results are promising, a thorough validation of the model will require extensive CFD and in vitro studies of multiple fiber arrangements, fiber diameters, and therefore fiber bundle porosities in the future. This article should be understood as a first feasibility study to evaluate the potential of the novel oxygen transfer model.

Current hollow fiber membrane lungs feature a predominantly straight blood path length across the fiber bundle, resulting in limited oxygen transfer efficiency due to the diffusion boundary layer effect. Using computational fluid dynamics and optical flow visualization methods, a hollow fiber membrane lung was designed comprising unique concentric circular blood flow paths connected by gates. The prototype lung, comprising a fiber surface area of 0.28 m2, has a rated flow of 2 L/min and the oxygenation efficiency is 357 mL/min/m2. The CO2 clearance of the lung is 200 mL/min at the rated blood flow. Given its high gas transfer efficiency, as well as its compact size, low priming volume, and propensity for minimal thrombogenicity, this lung design has the potential to be used in a range of acute and chronic respiratory support applications, including providing total respiratory support for infants and small children and CO2 clearance in adults.

Children with end-stage lung failure awaiting lung transplant would benefit from improvements in artificial lung technology allowing for wearable pulmonary support as a bridge-to-transplant therapy. In this work, we designed, fabricated, and tested the Pediatric MLung-a dual-inlet hollow fiber artificial lung based on concentric gating, which has a rated flow of 1 L/min, and a pressure drop of 25 mm Hg at rated flow. This device and future iterations of the current design are designed to relieve pulmonary arterial hypertension, provide pulmonary support, reduce ventilator-associated injury, and allow for more effective therapy of patients with end-stage lung disease, including bridge-to-transplant treatment. Keywords extracorporeal life support; hollow fiber oxygenator; wearable artificial lung One in five children with end-stage lung failure (ESLF) die while awaiting transplant. 1 Hollow fiber oxygenators or artificial lungs (ALs) are commonly used to provide pulmonary support in acute and bridge-to-transplant applications. In these devices, blood flows around a bundle of hollow fibers, while a sweep gas supplied to the fibers' lumens facilitates gas transfer via diffusion through the fiber wall. The benefits of a particular AL depend on the design properties and engineering of the AL, and device development must be thoughtfully targeted to the intended patient population to achieve optimal results. In this work, we design, fabricate, and test the performance of a paracorporeal, pumpless device intended for pediatric patients. This device, called the "Pediatric MLung," can be used as a bridge to transplant for children with ESLF.

Extracorporeal membrane oxygenation (ECMO) is mainly used for the therapy of acute respiratory distress syndrome and chronic obstructive lung disease. In the last years, the development of these systems underwent huge steps in optimization, but there are still problems with thrombus formation, clogging, and thus insufficient gas exchange. One idea of ECMO optimization is a pulsatile blood flow through the oxygenator, but this is still a controversy discussion. Analyzing available publications, it was not possible to identify a general statement about the effect of pulsatile blood flow on the gas exchange performance. The variety of parameters and circuit components have such a high influence on the outcome that a direct comparison of the studies is difficult. For this reason, we performed a structured study to evaluate the effects of pulsatile blood flow on the gas exchange performance of oxygenator. In in vitro tests according to DIN EN ISO 7199, we tested a small oxygenator (0.25 m exchange surface, polymethylpentene fibers, 33 mL priming volume) with constant and pulsatile blood flow in comparison. Therefore, we varied the mean blood flow from 250 to 1200 mL/min, the amplitude of 0, 20, and 50%, and the frequency of 30, 60, and 90 bpm. The results demonstrate that the gas transfer for pulsatile and constant blood flow was similar (oxygen: 36-64 mL /L ; carbon dioxide 35-80 mL /L ) for the same mean blood flow ranges. Over all, the results and analyses showed a statistically nonsignificant difference between pulsatile and nonpulsatile flow. Consequently, we conclude that the implementation of pulsatile blood flow has only a small to no effect on the gas exchange performance in an oxygenator. As the results were obtained using an oxygenator with a coiled fiber bundle, the test must be verified for a stacked fiber oxygenator.

Wearable extracorporeal membrane oxygenation (ECMO) circuits may soon become a viable alternative to conventional ECMO treatment. Common device-induced complications, however, such as blood trauma and oxygenator thrombosis, must first be addressed to improve long-term reliability, since ambulatory patients cannot be monitored as closely as intensive care patients. Additionally, an efficient use of the membrane surface can reduce the size of the devices, priming volume, and weight to achieve portability. Both challenges are linked to the hemodynamics in the fiber bundle. While experimental test methods can often only provide global and time-averaged information, computational fluid dynamics (CFD) can give insight into local flow dynamics and gas transfer before building the first laboratory prototype. In this study, we applied our previously introduced micro-scale CFD model to the full fiber bundle of a small oxygenator for gas transfer prediction. Three randomized geometries as well as a staggered and in-line configuration were modeled and simulated with Ansys CFX. Three small laboratory oxygenator prototypes were built by stacking fiber segments unidirectionally with spacers between consecutive segments. The devices were tested in vitro for gas transfer with porcine blood in accordance with ISO 7199. The error of the predicted averaged CFD oxygen saturations of the random 1, 2, and 3 configurations relative to the averaged in-vitro data (over all samples and devices) was 2.4%, 4.6%, 3.1%, and 3.0% for blood flow rates of 100, 200, 300, and 400 ml/min, respectively. While our micro-scale CFD model was successfully applied to a small oxygenator with unidirectional fibers, the application to clinically relevant oxygenators will remain challenging due to the complex flow distribution in the fiber bundle and high computational costs. However, we will outline our future research priorities and discuss how an extended mass transfer correlation model implemented into CFD might enable an a priori prediction of gas transfer in full size oxygenators.

This comment on an article that appeared in this journal (Potkay, Lab Chip, 2014, 14, 4122-4138) presents an alternative view on the feasibility and clinical application of current microfluidic artificial lungs.