development of an evanescent-field fibre optic sensor for
TRANSCRIPT
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Biosensors & Bioelectronics 16 (2001) 399408
Development of an evanescent-field fibre optic sensor forEscherichia coli O157:H7
A.P. Ferreira a,*, M.M. Werneck b, R.M. Ribeiro b
a Department of Sanitation and En6ironmental Health, National School for Public Health, Oswaldo Cruz Foundation, Rio de Janeiro, Brazilb Biomedical Engineering Program, Federal Uni6ersity of Rio de Janeiro, PO Box 68564, 21945-970, Rio de Janeiro, Brazil
Received 6 March 2000; received in revised form 14 March 2001; accepted 12 April 2001
Abstract
An intensity-modulated fibre optic sensor was developed for Escherichia coli O157:H7. The interaction between the whole
natural bacteria and the guided lightwave was carried out by means of evanescent-field coupling. A correlation between optical
response and the current number of bacteria was achieved. The device sensitivity had been calibrated for initial number of bacteria
(N0) from 10800. The sensor sensitivity was 0.016 (90.001) dB/h/N0. The sensing mechanism starts together with the log phase
leading the present sensor response to be five to ten times faster than conventional bacteriological techniques. 2001 Elsevier
Science B.V. All rights reserved.
Keywords: Fibre optic sensor; Evanescent field; Escherichia coli O157:H7
www.elsevier.com/locate/bios
1. Introduction
Escherichia coli has been recognized as a common-
place microorganism found in the intestinal tract of
human and other warm-blooded animals. E. coli typi-
cally colonizes the infant is gastrointestinal tract within
hours of life. Usually it remains harmlessly confined to
the intestinal lumen, only becoming pathogenic in the
debilitated or immunosuppressed host, or when gas-
trointestinal barriers are violated. Therefore, E. coli has
served as an indicator for faecal contamination in water
and food.
Enterohemorrhagic Escherichia coli O157:H7 is anemerging pathogen; which is the cause of foodborne
illness, the major cause of serious outbreaks and spo-
radic cases of hemorrhagic colitis and hemolytic-uremic
syndrome (Pickering et al., 1994; Siegler, 1995; Nataro
and Kaper, 1998). The major impact of bacterial in-
duced diarrhoea disease is on children under the age of
10 and on elderly people living in less-developed coun-
tries, in which bacterial diarrhoea diseases remain a
significant public-health problem. It represents also the
greatest challenge for both physician and scientific re-searches. E. coli O157:H7 is the cause of acute and
persistent diarrhoea disease and ongoing morbidity that
has malnutrition as one of its major contributors
(Huilan et al., 1991). The level of biohazard is high due
to the extremely low dose (10 microorganisms) required
for infection (Nataro and Kaper, 1998).
The greatest drawback for pathogen-detection tech-
niques is the lack of reliable and sensitive means for
measuring their presence in real time. Evanescent-wave-
coupling sensor technology is a suitable technique for
microorganism measurement in its natural form that
may be applied to the biosensor development takingadvantage of the current understanding of the whole
cell architecture of the microbial (Watts et al., 1994;
Hutchinson, 1995; Bousse, 1996; Muller et al., 1997;
Nath et al., 1997).
The biological and medical areas such as living cells
and bacteria detection remain a challenging technique.
The advantages of fibre optic sensing are well known
and have been reported in the literature (Smoczynski et
al., 1993; Ligler et al., 1993; Karube and Nakanishi,
1994). In the last few years fibre optic sensors have been
increasingly employed in biological sensing because of
their electrical isolation, electromagnetic-interference
immunity, compactness, lightweight, sensitivity, in-line
* Corresponding author. Tel.: +55-21-598-2746; fax: +55-21-270-7352.
E-mail address: [email protected] (A.P. Ferreira).
0956-5663/01/$ - see front matter 2001 Elsevier Science B.V. All rights reserved.
PII: S 0 9 5 6 - 5 6 6 3 ( 0 1 ) 0 0 1 4 9 - X
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implementation by means of evanescent-field coupling,
potential low cost and biological compatibility. The
optical sensor has revealed to present a faster response
than conventional techniques of clinical laboratory
analysis. One of the major advantages of using the
coupling with the guided lightwave evanescent field is
the development of in-line fibre optic devices. The fibre
is not interrupted and the light is not removed from the
fibre. The signal processing takes place inside the opti-cal fibre thus characterizing an intrinsic sensor.
A fibre optic biological sensor has been designed in
our laboratory and was described elsewhere (Ferreira et
al., 1999a,b). In this work, using the same measurement
principle, the sensor has been employed to quantify E.
coli O157:H7.
This paper describes for the first time, to the best of
our knowledge, experimental results on sensitivity cali-
bration of an intensity-modulated fibre optic evanescent
sensor for the E. coli O157:H7 as a whole bacterium.
The complete bacteria growth phases were optically
sensed and time resolved with reproducibility. Electronand optical microscopy were also employed for a de-
tailed understanding of the interaction dynamics be-
tween the bacteria and the optical fibre probe.
2. Principles
2.1. The bacteria growth e6olution
As reported from the literature (Pelczar et al., 1993),
the bacterium growth evolution follows a well-knownpattern that comprises four phases, as is briefly de-
scribed below. The LAG phase begins once the bacteria
are isolated in a suitable biological culture medium.
Growth is very slow at first (little or no division), while
the organism is adjusting its metabolism to the food
and nutrients in its new environment.
The log (or logarithmic) phase starts once the
metabolic machinery is running and the bacteria start
multiplying exponentially, doubling in number (binary
fission) at every few minutes. The time required for the
bacteria population to double after the lag phase is
called generation time g:
g=t
n. (1)
Where n is the number of generations that occur in
the period of time t (in min). A more practical formula
may be derived from the definition stated above and
gives:
g=t
3.3(log10N log10N0). (2)
Where, N is the current number of bacteria at time t
and N0 is the initial number of bacteria. The current
population N(t) at the log phase can be derived from
Eq. (2):
N(t)=No2t/g (3)
As more and more bacteria are competing for food
and nutrients the booming growth stops and the num-
ber of bacteria stabilizes in the stationary phase. At the
same time dying and dividing the organisms are at
equilibrium. Death is due to reduced nutrients, pHchanges, toxic waste and reduced oxygen. In some cases
cells do not die but they are not multiplying. Eventu-
ally, when the death rate exceeds the growth rate, the
cells enter the death phase. The population is dying in
a geometric fashion so there is more death than new
cells, and the population may be entirely destroyed.
2.2. The sensing mechanism of the sensor
The sensing mechanism of the sensor described here
relies upon the attenuation of a guided lightwave by
means of evanescent-field coupling that takes place atthe sensitive fibre. As the bacteria grow in the neigh-
bourhood of the sensitive fibre, the guided lightwave is
changed in intensity.
The culture medium is adherent to the cladding of
the almost unclad sensitive fibre. Normally, light travel-
ling inside the fibre experiences total internal reflection
when light beams strike the interface between the fibre
core and the cladding. This occurs when the angle of
incidence is greater than the critical angle. Thus, a
propagating optical wave through the optical fibre is
bounded in its core, but allowed to interact with theoutside medium by evanescent-field coupling when this
field is exposed (Rahnavardy et al., 1997). The evanes-
cent field of the guided lightwave penetrates beyond the
core surface and exponentially decreases in its magni-
tude an order of a wavelength away from the core/clad-
reflecting interface. The evanescent-wave penetration
depth (dp) is calculated by:
dp=u
2y(n
2 sin2qn cl2 )1/2
, (4)
Where dp is the distance by which the magnitude of
the electric field decays of l/e to its intensity at thecore/clad interface, q is the internal incident-ray angle
with the normal to the core/cladding interface, u is the
vacuum wavelength of the light beam and nco and nclare the core and cladding index of refraction,
respectively.
The evanescent-field coupling interaction mechanism
will cause optical attenuation of the guide lightwave
when any material (gas, liquid or solid) gets into con-
tact with the surface of the etched fibre clad. The loss of
power is proportional to the intrinsic bulk absorption
and scattering (Rayleigh and Mie). Thus, as a light ray
progresses down the multimode fibre by bouncing off
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the core-cladding interface, it loses power at each
bounce. While the loss per bounce is small, the accumu-
lated loss after a large number of bounces can be
significant even fbr a modest length of the probe fibre.
When a light ray travelling in a medium of a particu-
lar refractive index impinges on the boundary of an-
other slightly attenuation medium of lower refractive
index, it suffers the following approximate fractional
loss of power on refraction:
T=4(q/q c
2)
qc2q2 uh
4yncl
. (5)
Where T is the fractional loss of power, qc is the
critical angle of two media, q is incidence angle at the
boundary between the media (measured with respect to
the plane of the interface, rather than its normal), u is
the optical wavelength, h is the bulk-attenuation coeffi-
cient of the culture medium at the region of contact,
and ncl is the (real part of the) refractive index of theclad at the boundary (Snyder and Love, 1983).
Thus, the fractional power reflected back into the
original medium is (1T) and the fraction of the
original power remaining after N reflections is (1T)N.
In this formula qBqc and should not be too close to it
for the approximation to be valid. This means that it
applies to rays that would have been well guided in the
absence of loss. Furthermore the tighter such guidance
(i.e. the smaller q/qc), the lower the loss on reflection.
The optical attenuation can be generated by two
interrelated physical mechanisms: variation of the cladrefractive index ncl as well as of its absorption coeffi-
cient h. When the bacteria are allowed to grow around
the optical fibre, both effects can occur:
1. In the lag phase enzymes are released because of the
bacteria metabolism, causing the change of the in-
dex of refraction. Although this issue is not the aim
of this paper, the interdependence between absorp-
tion coefficient and index of refraction has been
experimentally shown and is theoretically described
by the Kramers-Kronig Eqs. (Nussenzveig, 1972).
2. Due to the existence of an increasing number of
bacteria in contact with the fibre during the logphase, the medium becomes more opaque as time
goes by. Consequently the intrinsic absorption also
changes.
Both effects may change the mechanism of interac-
tion between the evanescent field and the outside mate-
rial medium, coupling out different amounts of the
fibre-guided lightwave. Therefore, the measurement of
the light power at the exit of the fibre shows indirectly
the bacteria growth. As explained in more detail in
Section 4, the decreased optical power is mainly related
to the number of bacteria present in the volume occu-
pied by the evanescent field around the fibre.
3. Experimental
The sensor described here may be envisaged as com-
prising by three parts: The optical circuitry, the evanes-
cent probe fibre (sensitive fibre) and the biological
culture medium.
3.1. The optical circuitry set -up
Fig. 1 shows a schematic drawing of the biosensor
set-up. The optical source is a 3-mW CW GaAlAs laser
(AsGa Microeletronica, Brasil) with graded-index mul-
timode fibre pigtail, emitting at 840 nm. The output
fibre was spliced with a bi-directional optical fibre
coupler (CPqD Telebras, Brasil). Half of the emitted
optical power propagates over the probe fibre (sensing
element). The light modulated by the growing bacteria
exits the fibre and is detected by the photodiode PD2providing the electrical signal Samplein. The other half
of the optical power is detected by the photodiode PD1from which an electrical reference signal Refin is gener-
ated. Both electrical signals are amplified and measured
by a twochannel calibrated optical-power meter
(Graseby Optronics, USA). An AID board controlled
by the LabVIEW software (National Instruments Cor-
poration) digitises both output signals from the optical-
power meter (Sampleout. and Refout) by means of its
IEEE-488 interface. The AID board collects 800 points
per min of both Sampleout and Refout recording and
storing the respective averages for a period of 24 h per
measurement cycle.
3.2. The e6anescent optical probe fibre
In order to expose the evanescent lightwave field, 20
cm of a graded-index multimode optical fibre (62.5/125
mm) was clad-stripped by chemical etching. The etching
was performed by means of hydrofluoric acid solution
(38%) during 11 min in order to leave between 0.5 to 1
mm of clad over the core of the fibre. After this time,
the chemical reaction was stopped by immersion in
demonised water and then in phosphate-buffered saline
(PBS) with pH 7.4 for 15 min, in order to remove allremains of water from the probe. The exact etching
Fig. 1. Optical circuitry of the sensor.
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time was determined by monitoring diameters in a
previous measurement using a calibrated optical micro-
scope. This method has been detailed described by
Muller and co-workers (Muller et al., 1998).
After the chemical etching the fibre was wound into
a single loop, with a total sensitive surface area of
approximately 40.0 mm2, in which the evanescent
field can be accessed. The probe fibre was put over
the culture medium in which the bacteria grew, selec-tively.
3.3. Selecti6e culture medium for E. coli O157:H7
All of the described experiments in this paper were
performed using Escherichia coli O157:H7 CDC EDL-
933 (ATCC 43894), which was supplied by the Centre
for Disease Control and Prevention (CDC/USA).
In order to promote the E. coli O157:H7 growth, the
selective culture medium employed was MacConkey
Sorbitol Agar (SMAC) Difco 0079177 (Difco Labo-
ratories, Brasil) at an incubation temperature of 35 C.After optical measurements with the sensor, the bacte-
ria underwent microbiological identity tests in order to
ensure that only that specific microorganism had grown
on each Petri plate. The identity tests were made in
accordance with Farmer and Davis (1985).
Although biochemical characteristics associated
with the great majority of E. coli O157:H7 serotypes
are well known, there are not much data available on
their identification. It must be stressed that about 75 to
94% of E. coli strains quickly ferment D-sorbitol,
while the O157:H7 strain does not (Thompson et al.,1990).
It is also referred to this pathogen its inability to
produce b-glucuronidase which hydrolyses-4-methyl-
umbelliferyl-D-glucuronide. This does not happen with
other serbtypes of E. coli. Another parameter is that
more than 90% of E. coli O157:H7 strains produce one
or two unique biochemical profile numbers on a Mi-
croScan conventional gram-negative identification
panel (Baxter Diagnostics, Inc., California) and other
D-sorbitol negatives were not detected by this technique
(Abbott et al., 1994).
Finally, E. coli is a facultative anaerobe, whichmeans that it can survive in the presence or absence of
oxygen, it is a gram-negative bacterium and is not
fastidious in its nutritional requirements.
3.4. Bacteriological preparations for the sensor
calibration
In order to calibrate the sensor for its sensitivity,
several tests were performed using different N0.
E. coli O157:H7, available lyophilised in ampoules,
was restored with 1.0 ml of PBS, pH 7.4, inoculated in
several Petri plates with SMAC and incubated at 35 C
for 24 h. At the end of this period, the purity of the
material was checked and the Petri plates were stored at
4 C for further dilution.
For obtaining a dilution with N0=10, 20, 30, 40, 50,
60, 70, 80 and 90 microorganisms, were used 100 ml of
PBS, pH 7.4, whereas for N0=100, 200, 400 and 800
the volume used was 500 ml of PBS, pH 7.4. For each
sample the cells were counted using the Coulter Coun-
ter (Beckman, USA), which allows an accuracy of91%. Finally, the probe fibre was rested upon the Petri
plates with the culture as described above, the dilution
with a known number of microorganisms was poured
onto the sensitive area of the probe and the hardware
and software were started.
In all cases the SMAC was supplemented with glyc-
erol at 0.2%, which allows the maintenance of the
residual humidity and provides a better interaction
between the microorganisms and the sensitive area.
This was done in order to avoid the culture going dry
during the tests and thus inserting another variable into
the process.
3.5. Taking pictures of the process
For a direct observation of the microorganisms in-
teraction with the probe fibre, photographs were taken
employing the scanning electron microscope and the
optical microscope.
3.5.1. Scanning electron microscopy
Micrographs were taken at 316 min (N0=400) and
410 min (N0=20), corresponding to the elapsed timeafter which the sensor reaches half of the optical-signal
drop. Cells were fixed with 2% (v/v) glutaraldehyde in
PBS, pH 7.4, for 3 h at 4 C. After washing 3 times
with PBS, pH 7.4, 4% (v/v) of osmium tetroxide was
added to each sample during 1 h at 4 C. After dehy-
dration in a graded series of ethanol dilutions, cells
were subjected to a critical point drying with CO2(Samdri-780A, Tousimis Research Corporation). Sam-
ples were covered with ag 0 Id thin film by an ion
sputtering (JFC-1 100 Ion Sputter, JEOL) and exam-
ined under a digital scanning microscope (Carl Zeiss
DSM94OA). Photographs were taken with Agfa APX100 black and white film.
3.5.2. Optical microscopy
The optical microscopy pictures were taken after 398
min (N0=100), corresponding to the stationary optical
signal. Cells were fixed with 2% (v/v) glutaraldehyde in
PBS, pH 7.4, for 3 h at 4 C and then washed 3 times
with PBS, pH 7.4. The images in differential interfer-
ence contrast were obtained with the Zeiss Axioplan 2
microscope (Carl Zeiss) and photographed with a Po-
laroid MC2OO (Carl Zeiss) using Kodak Tmax 100
film.
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Fig. 2. Scanning electron micrograph of E. coli O157:H7 (log phase)
that are in physical contact with the probe fibre. Two levels of
magnification are shown.
Fig. 3. Optical phase-contrast micrograph of the E. coli 0 1 57:H7
after Iout(t ) reached the stationary state. Two levels of magnification
are shown on 3(ab).
physical contact with the probe fibre. The optical mi-
crograph shows an almost physical isolation of the E.
coli O157:H7 cluster (on top of the probe fibre) from
the others colonies. Because of the short range of the
evanescent field, the former were optically probed whilethe later were not.
In order to characterize the sensitivity of the sensor,
several measurements were carried out, each one during
a 24 h interval (1440 min), employing thirteen different
values of N0. These values were varied from 10800 E.
coli O157:H7 bacteria samples. Fig. 4 shows the plot of
4. Results and discussion
4.1. Presentation of the experimental results
Fig. 2 and Fig. 3 display micrographs of the probe
fibre showing the physical contact with the E. coli
O157:H7 growing around it.
Fig. 2 shows the micrograph taken by means of the
scanning electron microscopy on two levels of magnifi-
cation. It displays the fibre-bacteria physical contact
during the Iout(t) drop (log phase) as shown in Fig. 4and Fig. 5. Fig. 2(a) shows an island-like cluster of E.
coli O157:H7 on top of the probe fibre. Notice that the
optical fibre, as evaluated by the scale shown at the left
of the picture, is only about 60 mm in diameter, which
is approximately the same as the one of the core. Fig.
2(b) shows with a greater spatial resolution an as-like
amorphous structure of the E. coli O157:H7 cluster in
which the bacteria are stacked as foam.
Fig. 3 shows a micrograph taken from a phase-con-
trast optical microscopy with two levels of magnifica-
tion. It displays the fibre-bacteria physical contact, after
Iout(t) has reached the stationary phase, which are inFig. 4. Optical response Iout(t) of the sensor parameterised by theinitial number N0=0, 10, 80 and 800 of E. coli O157:H7.
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Fig. 5. Line 1 and line 2: The optical response Iout(t) of the sensor for two similar tests with N0=200, referred to the left vertical axis (the
superimposed straight lines are averaging of the data used to calibrate the sensor). Line 3: The estimated number of bacteria, as predicted by Eq.
(3), referred to the right axis.
the temporal optical response Iout(t) (in arbitrary units)of three of such measurements (N0=10, 80 and 800)
plus the blank test (N0=0).
Fig. 5 shows two separated tests for N0=400 (lines 1
and 2) and the theoretical current number of bacteria
N(t) representing the population of the colony along its
life evolution, as previewed by Eq. (3) (line 3). The
superimposed straight lines are eye-guide lines repre-
senting an averaging of the experimental plot used to
calibrate the sensor (see Section 4.6). The theoretical
plot also shown at Fig. 5 is the representation of Eq.
(3).
As explained on the text (see Sections 4.2 and 4.6) the
superimposed straight lines represent a mathematical
idealization that helps on the sensor calibration. The
arrows guide the reader for the correct vertical axis
corresponding the two plots.
As seen from the two tests performed with N0=200
shown in Fig. 5 it is possible to infer that the results of
the optical measurements were quite reproducible. The
good reproducibility of the optical response of the
sensor is guaranteed by the systematic procedure that
was employed for the biological culture as well the
sensing probe fibre insertion.
4.2. Analysis of the sensor response Iout
(t) in the lag
phase of the culture
The plots displayed in Fig. 4 show different phases of
Iout(t) for any used N0. In the first phase, it may be
observed a DC level Iout(t)=ILAG with an almost simi-
lar time range. The ILAG level is assigned to the sensor
response in which the E. coli O157:H7 remains in its lag
phase during ZtLAG time delay.
Fig. 6 shows a plot of DtLAG
against N0
for all
measurements. The linear relationship with an almost
null angular coefficient was fitted with an average of27094 min or approximately 4.5 h, meaning a re-
peatability of $1.5%. DtLAG may be attributed to the
time range that E coli 0 1 57:H7 spent in its lag phase,
despite their initial number N0.
Since enzymes are usually released by E. coli
O157:H7 along the lag phase, the average refractive
index of the culture medium ncm is likely to vary with
time. As described in Section 2, the variation of ncmmay cause changes in Iout(t), as stated by Eq. (5).
However, the measurements shown in Fig. 6 suggest
that the sensor, while probing the lag phase, is insensi-
tive to this effect. A possible explanation for this is that
the refractive index changed very little and the variation
of the optical response was buried into the noise. It is
possible to observe in Fig. 2 that the optical signals
present a slight slope during this phase. Therefore it
possible to infer that the technique used in this work is
Fig. 6. Time delay in the lag phase DtLAG (min) against the initialnumber N0 of E. coli O157:H7.
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more sensitive to the bacteria division (growth) than to
the variation of the index of refraction of the culture
medium itself.
4.3. Analyses of the sensor response Iout
(t) in the log
phase
Following the lag phase, E. coli O157:H7 starts the
log phase in which the size growth and replication takeplace. The curves displayed in Fig. 4 show that just
after approximately 270 min the sensor output signal
Iout(t) begins to drop gradually. The linear decreasing
of Iout(t) may be attributed to the sensor tracking of the
log phase evolution when the optical attenuation, as
sensed by the evanescent field, monotonically increases.
It should be carelully examined from the electron scan-
ning micrograph shown in Fig. 2 that the colony does
not cover the lull surface of the probe fibre.
If the attenuation coefficient h and the refractive
index ncm of the culture medium change in opposite
directions, as the bacteria grow, the critical angle qcincreases. As a consequence, shown by Eq. (5), the
effect of increasing the attenuation coefficient is par-
tially offset by improved optical guidance, for rays of a
given incidence angle, and the final effect on the optical
power output is unnoticeable. However if the attenua-
tion coefficient h and the refractive index ncm of the
culture medium change in the same direction, as bacte-
ria grow, the critical angle qc decreases. Both effects are
now coherently summing up and the fractional loss T is
reinforced, for rays of a given incidence angle, and the
final effect is a decrease of Iout(t).By extrapolation from the lag phase, it is unlikely
that the enzymes produced by the E. coli O157:H7,
even in the log phase, may affect the sensor Iout(t) for
all N0 employed. In this way, along the log phase, only
the attenuation coefficient a suffered appreciable
changes, thus affecting Iout(t). In other words, the sen-
sor described here seems to be insensitive to the average
refractive index changes, if it changes at all. Only
intrinsic absorption as well Rayleigh and Mie scattering
affect the optical signal Iout(t).
4.4. Analyses of the sensor response Iout(t) in thestationary phase
All plots displayed in Fig. 4 show that after the end
of the Iout(t) drop, the sensor response reaches another
DC level (ISTAT). Following the log phase, the E. coli
0157:117 stops their size growth and replications, thus
reaching the stationary phase in which Iout(t)=ISTAT.
A careful examination of Fig. 4 and Fig. 5 shows
that, in the so-assigned log phase Iout(t) turn to a lower
derivative, a little before reaching the stationary phase,
it is likely that between the purely log and stationary
phase, a transition region takes place. From some
instant of time, a fraction of E. coli O157:H7 stops its
growth and replication, thus reaching its own station-
ary phase. In this way, the smaller derivative of Iout(t)
is assigned to the coexistence of E. coli O157:H7 clus-
ters over the probe fibre, at both the log and the
stationary phase thus affecting the optical response of
the sensor.
It is also noticeable in Fig. 4, for all measurements
performed with different N0 (until N0=800), that ISTATis always smaller than the previous one. The sensor
response Iout(t) has shown an optical-dynamic reserve
in the log phase that makes it clear that E. coli
O157:H7 really reached the stationary phase. Thus, the
ISTAT level (lower than ILAG) may be assigned to the
stationary phase of the E. coli O1 57:H7 evolution,
when the attenuation, as sensed by the evanescent field,
remains unchanged.
After the clad was stripped from the probe fibre, a
surface area of approximately 40.0 mm2 has been
achieved, and the evanescent field was exposed. On the
other hand, it should be carelully examined from theoptical micrograph shown by Fig. 3(a) and (b), that E.
coli O157:H7 at the stationary phase were able to cover
almost all the surface area of the probe fibre.
4.5. Analyses of the sensor response Iout
(t) in the death
phase
For a 24 h monitoring, the optical sensor response
Iout(t) did not show any remarkably change after the
stationary phase was reached.
Although the E. coli O157:H7 starts its death phasesome time after the end of the log phase, the sensor
described here does not seem to optically discriminate
the stationary phase from the death phase.
4.6. Calibration of the sensor
In Fig. 5 three eye guidelines were drawn for each
Iout(t) regime of the sensor and E. coli O157:H7 phase.
Along with the lag phase, an averaged unitary normal-
ized straight line was outlined. Just at the beginning of
the log phase, Iout(t) suddenly dropped with a sharp
derivative. It was smoothed by a non-null angular-co-efficient straight line. A similar procedure was per-
formed at the stationary phase extrapolated from
t=. But the steady state straight line outlined had an
ISTAT DC level lower than the ILAG DC level.
Two crossing points among the three straight lines
may be viewed in Fig. 5. The first one fix the boundary
between the lag and the log phase and the second one,
analogously, fix the boundary between the log and the
stationary phase.
The ordinate difference between the two cross points
provides the optical attenuation DIout
(in dB) for each
N0. Similarly, the abscissa difference between the two
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Fig. 7. Sensor calibration curve. It is shown the time derivative iLOGof Iout(t) in the log phase against N0. A linear dependence was fitted.
ference on the detection of E. coli 0 1 57:H7 was
observed.
Although not shown here, it was also carried out a
measurement in which none E. coli Ol 57:H7 were
present in the culture mediumnegative control or
blank measurement. In this case, the output signal
Iout
(t) did not change even after 24 h of monitoring,
and the noise pattern observed was similar to the one
presented in Fig. 4 (with the presence of E. coliO157:H7). In other words, none microorganism (except
E. coli O157:H7) could grow.
It is difficult to infer the causes of the noise superim-
posed in the output signal seen in Fig. 4 particularly
because it is an ultra-low-frequency noise. Nevertheless
it is possible to point out possible mechanisms that
could cause it:
1. Thermal and acoustic instabilities, affecting the op-
tical circuitry in every point, perturb the lightwave
before it reaches the multimode fibre optic 3dB
coupler. This may cause deviations of the coupler
ratio from the expected value of 3dB. The deviations
may be specifically caused by the mode coupling
and polarization-dependent loss (PDL) effects (Ren-
ner, 1998).
2. Electronic noise, due to instabilities of the detection
and amplification circuitry.
The sensor response relies on the interaction between
the lightwave and the bacteria causing the optical atten-
uation at the probe fibre. The optical interaction arises
from the evanescent-field coupling since there is a phys-
ical contact between the fibre and the bacteria, as
shown in Fig. 2 and Fig. 3. The physical contactbetween the SiO2 (probe fibre) and the whole E. coli
O157:H7 occurs because the bacteria are allowed to
grow around the probe fibre. This mechanism greatly
simplifies the construction of the sensor, when com-
pared with 6ther processes, for instance the silanization
technique employed by Weetall (1993) for a true
biosensor.
A bacteria colony may grow indefinitely if an infinite
amount of nutrients would be available, as well as if
other conditions, such as temperature, pH etc., would
be optimised. However, using culture medium in a Petriplate, it is obvious that there is a strong limitation and
the biological medium constrains the bacteria growth in
an available time range. In this study, preliminary
experiments have shown that E. coli O157:H7 is able to
grow for up to about 72 h, using similar Petri plates
and culture medium as those employed for the optical
measurements shown in Fig. 4. Therefore, the question
that arises is: why, since all conditions remains the
same, E. coli O157:H7 reached the stationary phase in
an average of 5 h (see Fig. 4), when this should happen
only in about 72 h? This behaviour may be explained in
the following way:
cross points provides the time width DtLOG (in h) of the
log phase for each N0. The indirectly measured (from
Fig. 5) time derivative iLOG of Iout(t) in the log phase
varies with N0 and may be calculated from:
iLOG(N0)DIout
DtLOG. (6)
Fig. 7 shows a plot of the sensor sensitivity bLOG(dB/h) at the log phase when the initial number of
bacteria is changed from N0=10N0=400. Although
the available data is not enough to draw statistical
conclusions it is possible to fit the data with a straight
line with a regression coefficient of 0.985 and standard
deviation of 0.351. This gives us a provisional calibra-
tion curve as shown in Fig. 7.
By employing the slope of optical response at the log
phase, i.e. the rate of increase in bacterial numbers, the
angular coefficient was calculated to be DiLOG/DN0=
(0.016 i 0.001) dB/h/N0. It means that for each E. coli
O157:H7 bacterium inoculated upon the Petri plate the
speed of the sensor response at the log phase increases
by 0.016 dB/h. For N0=800 the angular coefficient is
given as iLOG(800)$6 dB/h.
Therefore, it is possible to extract from the output
signal Ii(t), the N0 by measuring the angular coefficient
iLOG of the log phase. The N0 is directly related to the
degree of contamination of the sample, when applyingthe system in vivo.
4.7. General analyses
It has been reported that fibre optic evanescent-field
coupling presents some drawbacks when used as a
biological sensor (Ramsden, 1997). In other biological
processes as well, some bio-components may interfere
in the detection of the true target. However, as was
already explained at Section 3.3, the biological proce-
dures herein employed were not only intrinsically highly
selective, but also absolute. This explains why no inter-
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It is known that E. coli O157:H7, as well as some
other bacteria, do not grow inside the bulk of the
culture medium, but only at the surface. However, a
careful examination of Fig. 2(b) suggests that E. coli
O157:H7 grows and stacks one over each other, up to 3
layers, generating voids like foam. The as-like amor-
phous structure of E. coli O157:H7 cluster means that
the lightwave evanescent field would not be attenuated
(absorbed and scattered) in the voids or in places wherethe stacked bacteria are \\1 mm far away from the
surface of the probe fibre.
The cells of E. coli O157:H7 that happen to be all
over the Petri plate, without physical contact with the
probe fibre, go on growing for 72 h because there are
enough nutrients. However, these optically isolated
bacteria do not affect the sensor response Iout(t), since
they are out of reach of the sensing mechanism, the
evanescent field, that extends only about one or slightly
over a, wavelength from the core-clad interface. On the
other hand, the bacteria that touched the fibre during
the inoculation, together with those that happen togrow over and around the fibre, are within the evanes-
cent field, and are sensed and monitored.
However, since the probe fibre was rested upon the
surface of the biological medium prior to the optical
measurements, the lightweight probe fibre was not com-
pletely buried inside the gel-like culture medium, be-
cause of the superficial tension and the nutrients in
excess slowly slide down from the top of the probe
fibre. Also due to the surface tension, only a thin film
of culture medium will remain touching the fibre.
Therefore, the bacteria that happen to be isolated in theprobe fibre will grow and reproduce until the exhaus-
tion of this limited amount of nutrients. The mi-
crograph shown in Fig. 2(a), taken while the sensor
reached half of the optical-signal drop, show the bacte-
ria clusters isolated along the centre of the fibre width.
This is the initial level of the culture, but due to
evaporation the level drops leaving the clusters behind.
The calibration of the sensor sensitivity with N0, as
shown by Fig. 7, features a linear dependence of
iLOG(=DIout/DtLOG) from N0=10 until N0=400. For
N0=800 a deviation was observed from the linear
dependence, which suggests a possible saturation of thesensor response.
4.8. Possible impro6ements of the sensor
In order to increase the sensitivity and the time
derivative (speed at the log phase) of the sensor in its
presently basic configuration, some simple improve-
ments are suggested:
1. Optimisation of the wavelength for a better sensitiv-
ity. For instance, by using a longer wavelength we
would have a larger sensitivity volume because the
evanescent field would also be larger;
2. The use of a longer probe fibre (the actual measures
20 cm) will attenuate more light and therefore will
present a higher sensitivity for the same bacteria
concentration;
3. At present, it is possible to detect only one microor-
ganism per Petri plate at a time. One approach to
overcome this limitation would be the miniaturiza-
tion of the probe fibre such as that an array of them
might be employed. Several different microorgan-isms may be selectively sensed, for instance, by
multiplexing different wavelengths into a single opti-
cal fibre bus (wavelength-division multiplexing
WDM).
5. Conclusions
An evanescent-field and intensity-modulated fibre op-
tic sensor for detection and monitoring of E. coli
O157:H7 has been described and calibrated. These bac-
teria have been successlully detected and quantified inits natural form, 510 times faster than conventional
bacteriological techniques. With this system it is possi-
ble to conclude which bacteria have been inoculated
and its concentration. The development of this highly
sensitive and selective probe for real-time pathogen
detection has improved biological sensing. With minor
modifications the method can be used to test for food
contamination as well as for clinical essays and envi-
ronmental monitoring. Further investigations are under
way in our laboratories and will be object of luture
publications.
Acknowledgements
We would like to thank the Escola Nacional de
Saude Publica of the Fundacao Oswaldo Cruz (ENSP/
FIOCRUZ) for the bacteriological support on this
work; the Foundation for the Research Support of the
State of Rio de Janeiro (FAPERJ) and the Brazilian
National Research Centre (CNPq/PADCT) for finan-
cial support. We are also in dept with Mr. Jose Roberto
da Rocha Bernardo, MSc, and Dr. Ulisses GarciaCasado Lins, from the Federal University of Rio de
Janeiro, for their assistance in electron scanning and
optical microscopy, respectively.
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