Biomedical Engineering Reference
In-Depth Information
8.2.1
Total artificial heart (TAH)
About 12 years later, in 1969, the first pneumatically actuated TAH was imple-
mented clinically by Cooley and Akutsu (Frazier and Macris, 1994). In 1972,
Jarvik introduced first artificial heart out of aluminium, polyester and a plastic
named Jarvik-3 (Hajar, 2005). In 1982, the first permanent TAH, the Jarvik-7, a
two-chamber device made of polyethylene, was implemented (Joyce et al.,
2004). It was used as a bridge to transplantation. Between 1985 and 1992, eight
different brands of TAH as a bridge to transplantation were implemented:
Phoenix, Berlin, Pennsylvania State, Brno, Vienna, Unger, Poisk and
Cardiowest (Frazier and Macris, 1994).
8.2.2
Ventricular assist devices (VADs)
Ventricular support devices, including counterpulsation (Papaioannou and
Stefanadis, 2005), centrifugal (Iijima et al., 1997; Curtis et al., 1999), and axial
(Nos et al., 2000), aimed to offer a short-term support to recovery or long-
term bridge to transplant. In 1961, Dennis et al. initiated roller pump to assist
the left ventricle (Frazier and Macris, 1994). Moulopoulos et al. (1962)
introduced the intraaortic balloon pump (IABP) in 1962. Kantrowitz et al.
(1968) announced the first clinical application of an IABP in 1968. Currently
IABPs are widely used as a cardiac assist device (Frazier et al., 2008). In
1990s, the records indicate several successful VAD implementations that
enabled patients to recover from heart failure. In 1993, US Food and Drug
Administration (FDA) approved the first VAD, the Abiomed BVS 5000, for
commercial use (Frazier and Macris, 1994), which will be described in detail in
the following sections.
8.3 Characterization of biomaterials: interaction
with blood and tissue surface
A biomaterial is implemented and used to assist human health. Therefore, it
must be sufficiently safe. Identification of fundamental biological requirements
and characterization of biomaterials are explained and the complications are
then reported.
Investigation of mechanical and functional properties of a biomaterial is
important in order to meet the requirements of a successful cardiac device. For
example, it has to be mechanically strong to withstand the flex-time of 42
million flexes per year and be capable of interacting with blood as well as tissue
cells without any damage.
Another important criterion for material choice is the intended clinical
application of the biomaterial. The requirements of the same material would be
different for different medical applications. For example, the material perform-
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