Biomedical Engineering Reference
In-Depth Information
Table 6.6: Binding rate coefficients for percutaneous fiber-optic biosensor
for chronic glucose monitoring (
Liao et al., 2008
).
Analyte
Concentration
k
k
1
k
2
Percutaneous
blood glucose
9.9604 1.4599
9.509 0.737
19.975 0.199
8.0479
0.1744
7.7473
0.5424
15.722
0.2383
Table 6.7: Fractal dimensions for percutaneous fiber-optic biosensor for
chronic glucose monitoring (
Liao et al., 2008
).
Analyte
Concentration
D
f
D
f1
D
f2
Percutaneous
blood glucose
2.1816
0.8508
0.7584
0.0756
2.8938
0.02868
2.1826 0.08936 1.9072 1.9028
2.9005 0.0375
for measuring glucose to the neodymium hexacyanoferrate nanoparticle biosensor the fractal
dimension in the second phase,
D
f2
, decreases from a value of 2.8938 to 2.604, and the bind-
ing rate coefficient,
k
2
, increases from a value of 19.975 to 46.857. Similarly, as one goes
from the percutaneous biosensor for measuring glucose to the neodymium hexacyanoferrate
nanoparticle biosensor, the fractal dimension in the initial phase,
D
f1
, increases slightly from
a value of 0.7584 to 0.772, and the binding rate coefficient,
k
1
, decreases from a value of
9.509 to 4.959. In both these cases the changes in the binding rate coefficients and in the frac-
tal dimensions are in opposite directions (contrary to the general trend presented in the differ-
ent chapters throughout the topic); but this is because the analysis is of two different systems
here, to see if there is any sort of trend that may be exhibited, and what may be learnt from it.
Furthermore, one system is
in vivo
and the other is
in vitro.
Tierney et al.
(
2009a,b
)
point out the need for glucose testing in diabetics. They report that
most instruments presently available are for intermittent testing.
Kondepatu and Heise
(2007
) report that there are a few instruments available for the continuous monitoring of glu-
cose, which,
Tierney et al. (2009a,b
) report, would be required for the self-regulating insulin
system. Tierney et al. (2007) have developed an optical fiber biosensor for the continuous
monitoring of glucose
in vivo
which, is necessary for critically ill patients (
Williams et al.,
2002
). They further point out that glucose oxidase (
Malitesta et al., 1990; Hale et al.,
1991
) and glucose dehydrogenase (
Zhang et al., 2004
) have been used as also phenylboronic
acid (PBA) (
James and Shinkai, 2002
).
Hydrogels with receptors have been used as detection devices (
Asher et al., 2003; Kabilan
et al., 2005
). Asher and his group have pioneered these hydrogel-based detection devices
(
Alexeev et al., 2004; Ben-Moshe et al., 2006
). In their most recent publication
Tierney
et
al.
(2009a,b
) have used a
responsive hydrogel-based sensor,
and have used
