1.2.1 History
To perform delicate surgery on the human heart, for many interventions it is essential to stop the heart beating (e.g. for any surgery on the heart valves), and for all procedures the stoppage greatly facilitates the work of the surgeon. The heart with its four chambers pumps the blood through body and brain, which consume oxygen and produce carbon dioxide, and through the lungs simultaneously, where carbon dioxide is exhaled and oxygen taken up. If during a cardiac surgery procedure the heart is still then the lungs are also at rest. This means that the blood not only needs to be pumped through body and brain to continue their supply, but also needs to be oxygenated artificially. Therefore, for any cardiac surgery procedure where the heart is stopped, a device to oxygenate the blood and to remove the carbon dioxide is also needed.
A good overview of the development of the blood oxygenator is given by Leonard.1 The first heart–lung machines have worked with film or bubble oxygenators.2,3 In film oxygenators, blood was passed over sieves, plates or discs in pure oxygen or an oxygen-rich atmosphere. Oxygen and carbon dioxide were exchanged on this large surface. The second generation of oxygenators, bubble oxygenators, simply consisted of a bubble chamber where oxygen was dispersed into the patient’s blood and a defoamer which removed the majority of gaseous residuals from the blood. Both procedures were a major insult to the patient and their blood, and therefore a more gentle procedure had to be found.
In the 1940s, Kolff observed that the blood in his rotating drum kidneys turned to a brighter red during treatment. This was simply due to take up of oxygen through the cellophane membrane he used to separate the blood from the dialysis solution, which was exposed not only to the dialysate, but also to the open air. In a way, the first clinical application of an artificial kidney also was the first application of a membrane artificial lung. From this starting point, Kolff et al. developed a membrane oxygenator, the first clinical application of which was described in 19564.
The first membrane oxygenators incorporated various membrane materials, among them cellophane, polyethylene (PE) and Teflon, all of which were comparatively impermeable to oxygen. In the 1960s, the first oxygenators with silicone membranes were developed.5 For these, thin films of polysiloxane (silicone) were supported by meshes or sieves, then wrapped to a roll or stacked to a pile to incorporate sufficient surface in a volume that could still be handled. Those oxygenators had large priming volumes and large surfaces and consequently resulted in considerable blood dilution and blood damage.
In the 1980s, the first oxygenators with microporous membrane sheets were produced. The preferred material for microporous membranes in blood oxygenation was and remains polypropylene (PP).6 Owing to the presence of pores, the permeability of these membranes to oxygen was much higher than that of any other material before, so that the limiting factor for gas transfer was no longer the membrane, but the gas transport within the blood films directly adjacent to the membrane (see also page 10).
The next breakthrough in oxygenator performance was the introduction of capillary membranes. Those had the same pore size and same polymer (PP) as the flat sheet microporous membranes introduced. Similar to the development with haemodialysers, the introduction of capillary membranes reduced the priming volume of the oxygenator and turned a bulky space consumer into a handy device. The first capillary membrane oxygenators worked with blood flow inside the capillaries, but soon the trend to blood flow outside the capillaries prevailed: blood side pressure drop always used to be a limiting factor for ‘blood inside’ oxygenators, and the ‘blood outside’ models were smaller and more handy, and demanded less priming and thus less haemodilution. Finally, this was also welcomed from the manufacturer’s perspective, as it saves about half the amount of membrane.
These microporous membranes provide excellent performance, but compared with the older silicone membranes are more prone to plasma breakthrough. Around the year 2000, the first oxygenators with a membrane from polymethyl-pentene (PMP) with a very thin dense outer skin on a microporous body were introduced. These provide performance on the same level as the microporous PP membranes, but do not show the phenomenon of plasma breakthrough.
Today, almost all commercially available blood oxygenators incorporate capillary membranes and have the blood flow outside and the gas flow inside the capillaries. Most of the oxygenators have microporous membranes of PP, and a growing share is equipped with the dense PMP membrane type. Only one silicone membrane oxygenator is still commercially available.