data acquisition unit for an implantable multi- channel...
TRANSCRIPT
eit2007 – Electro/Information Technology Conference
Chicago, IL, USA, 17-20 May, 2007.
1
Abstract— Design and development of a data acquisition unit for
an implantable multi-channel optical glucose sensor is described.
The sensing technology involves sampling of the interstitial fluid
in a micro-fabricated chamber and measurement of the
absorbance of the fluid in a non-destructive and reagent free
manner. The glucose levels are estimated based on the absorbance
data. This new technology relies on the unique optical
characteristics of glucose in a near infrared spectrum. The sensor
element will be implanted in the subcutaneous tissues of the
human body. The data acquisition unit acquires optical data from
the sensor and converts it into spectral data for processing. This
new technology will be used as the sensing technology in a
feedback controlled insulin delivery system for the in situ
treatment of diabetes. The sensor-controller system together with
an insulin pump will function as artificial pancreas and help
maintain tight glycemic control in patients suffering from
diabetes.
Index Terms— Transmission spectrum, data acquisition,
optical glucose sensor.
I. INTRODUCTION
iabetes is a potentially devastating disease [1], the
medical complications of which can be diminished by
early diagnosis and tight glycemic control. The goal of tight
control is to maintain one’s blood glucose levels within a
physiologically acceptable range. Tight control requires
frequent blood glucose measurements, which provides the
information needed to administer insulin or glucose properly.
The glucose levels are measured using a blood glucose
monitor, which is typically made of an electrochemical glucose
sensor interfaced to an electronic support unit. The pain, cost
and inconvenience of state-of-the-art glucose monitoring
technology impede frequent monitoring and are primarily
responsible for the failure of patients to maintain tight control.
It has been recognized for several decades that the ideal
treatment of diabetes would involve a closed-loop insulin
delivery system that is implanted within the patient's body. The
so-called artificial pancreas consists of an insulin delivery
pump coupled with some type of glucose-sensing technology.
Manuscript received February 16, 2007. This work is supported by a grant
from the National Institutes of Health under Grant DK64659.
K. S. Kanukurthy and M. B. Cover are students with the dept. of Electrical
& Computer Engineering at the University of Iowa, Iowa City, IA, IA 52242
USA (phone: 319-335-1608; e-mail: [email protected]).
D. R. Andersen is a Professor with the departments of Electrical &
Computer Engineering, Physics & Astronomy at the University of Iowa, Iowa
City, IA, IA 52242 USA (phone: 319-335-2529; e-mail: [email protected]).
Insulin is delivered continuously in response to detected
changes in the blood glucose concentrations. For this to work,
the glucose sensing component must be able to provide
accurate and rapid blood glucose values to a micro-processing
unit, which computes the amount of insulin required and then
controls insulin delivery. The key limitation to the successful
development of an artificial pancreas is the implantable
glucose sensing technology and the electronic support needed
to control the instrumentation.
This paper describes the design and development of a data
acquisition unit [DAU] for an implantable glucose sensor that
provides continuous and reagent-free optical analysis of
interstitial fluid (ISF). The DAU is the front-end of the
Controller [2, 3], an electronics system designed to provide the
necessary electronics support to the sensor. The Controller
operates from an inductively rechargeable battery based power
supply [4] and provides support for the sensor to work
unobtrusively for extended durations.
The sensing technology relies on the unique optical
characteristics of glucose in the near infrared spectrum [5, 6].
The optical glucose sensor [7] consists of a broadband LED
light source, an optical sampling chamber, and a spatially
variable wavelength filter bonded to an array of photodetector
elements. Transmission spectrum of the interstitial fluid (ISF)
in the NIR region is collected by modulating the LED and
measuring the currents through the photodiode channels. Each
photodiode channels corresponds to a different band of
wavelengths in the NIR spectrum with the total spectrum
covering the entire region of interest. Glucose concentration
levels are estimated using the measured transmission spectrum
based on Beer-Lambert relationship.
II. DAU SYSTEM
The DAU provides the physical interface between the optical
sensing elements and the glucose related data. The DAU is
interfaced to the photodiode channels of the sensor on one end
and the user electronics such as a PDA or a PC on the other
end. The DAU performs the function of converting the
instantaneous output currents of the sensor’s photodiodes into
meaningful glucose concentration values and conveying that
information to the user. During the measurement process, LED
of the sensor is modulated by the DAU. Each detector element
reacts accordingly by producing an output current. The optical
sensor has 32 photodiode channels that output currents of the
magnitude of the order of 10 nA. The current is converted to a
voltage with preset transimpedance gain and digitized by a
Data Acquisition Unit for an Implantable Multi-
Channel Optical Glucose Sensor
Kiran Kanukurthy, Student Member, IEEE, Mathew B. Cover, David R. Andersen, Member, IEEE
D
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Chicago, IL, USA, 17-20 May, 2007.
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high resolution A/D converter (ADC). The transimpedance
gain and sampling rate can be varied as required. This process
occurs simultaneously for all the photodiode channels. The
results of the A/D conversion from all of the channels are used
to determine the glucose concentration. The following are the
requirements for the DAU interfaced to the glucose sensor.
a) Transimpedance gain: A transimpedance gain of 108 Ω is
required in order for the converted voltage to be about half the
full scale range of the ADC to achieve high SNR.
b) SNR: High SNR is required to obtain quality spectral data.
Preliminary calculations show that a SNR of 48 dB is
necessary to obtain good quality spectral data so that changes
in glucose concentration levels can be accurately measured.
Sources of noise in this case are the Johnson noise from the
electronic components, shot noise of the detector, and the
environment noise.
c) Multiple Channels Support: As each channel corresponds to
a different wavelength region, all 32 photodiode channels of
the sensor need to be sampled and converted simultaneously
by the DAU.
d) Resolution of Data: Output data of each channel should
have a resolution greater than 16-bits to result in high SNR.
III. IMPLEMENTATION
The following section discusses the hardware and software
aspects of the DAU system design along with the device
selection criteria for the front-end of an optical data
acquisition system with photodiodes as sources at its input
channels.
A. Transimpedance Amplifier Selection
Primary parameters in interfacing any sensor to an electronic
device are the voltage levels of the sensor, current output of
the sensor, and the impedance of the sensor. These factors
contribute significantly to the decision to use a particular type
of electronic device, mostly a particular kind of ADC and/or
an operational amplifier. Other factors such as the real estate
are to be considered as well when multi-channel sensors are
involved. The real estate being the cost of the circuit, the
size/area of the circuit, complexity, and the power supply
consumption. For an optical sensor whose output signal is a
current, the electronic circuit traditionally consists of a
transimpedance amplifier followed by an ADC. The detector
elements of the sensor output currents of a magnitude of the
order of 10 nA. A transimpedance gain of about 108 Ω is
required to output a voltage of half the full scale range of the
A/D converter. There are two choices for the transimpedance
amplifier vis-à-vis transresistance amplifier and switched
capacitor transimpedance amplifier. In the case of a
transresistance amplifier, the gain is provided by a resistor in
the feedback loop. A gain of 108 Ω translates to a resistance in
the range of 100 MΩ. Transresistance amplifiers with such
huge resistors in the feedback loop suffer from instabilities
apart from requiring dual power supplies. Besides, a circuit
consisting of transresistance amplifiers followed by ADCs for
32 photodiode channels requiring dual power supply is
expensive in terms of the real estate and is not a suitable
choice for an implantable sensor system.
Switched capacitor transimpedance amplifiers provide the
transimpedance gain by integrating the current on a capacitor
over a period of time. The transimpedance gain can be varied
by varying the capacitance of the integrating capacitor and the
integration window. High transimpedance gains of the order of
108 Ω can be achieved easily by using a switched capacitor
circuit. The integrating behavior of a switched capacitor
amplifier reduces noise by averaging the input noise of the
sensor, amplifier, and external sources. Integration of the input
signal for a fixed period produces a deep null (zero response)
at the frequency 1/TINT and its harmonics, where TINT is the
duration of integration. An AC input current at this frequency
(or its harmonics) has zero average value and therefore
produces no output. This property can be used to position
response nulls at critical frequencies. For example, a 16.67ms
integration period produces response nulls at 60Hz, 120Hz,
180Hz, etc., which will reject ac line frequency noise and its
harmonics. Response nulls can be positioned to reduce
interference from system clocks or other periodic noise.
A suitable choice for the front-end of a DAU for a multi-
channel photodetector array would consist of a switched
capacitor transimpedance amplifier IC operating on a single
power supply while providing multiple input channels. A
single IC offering more than one input channel with each
channel consisting of a switched capacitor transimpedance
amplifier circuit followed by an ADC would be an ideal
solution for a multi-channel photodetector array. DDC118 [8],
a current input ADC from Texas Instruments Inc., is one such
IC that can work with up to 8 photodiode channels. Since the
ADCs are current-input, additional transimpedance amplifiers
for current-to-voltage conversion are not needed. The photo
detector currents are integrated over time, converted to a
voltage, sampled and measured by the A/D converter, and
output as high precision 20-bit digital codes. Transimpedance
gain, the gain involved in current-to-voltage conversion, is
varied by varying the integration times and integrator
capacitances.
B. Hardware Design
The architecture and implementation of the DAU is shown in
the block diagram in Fig. 1.
Fig. 1. Block diagram of DAU
The design is composed of four DDC118 ICs, each of which
interfaces to eight photodiode channels. Channels are not
connected sequentially but in a way so as to achieve a clean
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Chicago, IL, USA, 17-20 May, 2007.
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layout. Odd channels are connected to the DDC118 ICs on the
left of the sensor while the even channels are connected to the
ones on the right. Each DDC118 input has two independent
integrators (sides A & B) followed by one ADC. This feature
can be utilized in such a way that continuous integration of the
input signal becomes possible eliminating the possibility of the
loss of a portion of the signal. While side A is being integrated
with the input signal, side B undergoes conversion and a flag is
generated indicating that the results are available on the SPI
interface. At the end of integration time, side B is put under
the integration mode and side A undergoes conversion. The
DDC118s have an SPI interface for communication with a
microcontroller and function as a slave device. The
microcontroller used is AT89C51ID2 [9], an 8-bit
microcontroller based on Intel’s 8051 architecture. The
microcontroller was chosen based on the ready availability of
the device and related compiler tools. The DDC118 ICs are
cascaded so that the digital data output of one IC is connected
to the digital data input of the other. The advantage of a
cascaded design is that the microcontroller in charge of the
unit has to communicate with only one DDC118 for the data
corresponding to all DDC118 ICs. Thus the hardware
connections are made simple with just one SPI slave connected
to the microcontroller. The reference voltage for the ADCs is
generated by REF3140 [10] voltage reference IC followed by
an OPA350 [11] operational amplifier in a buffer
configuration. The devices are low output noise components
and are ideal for the reference voltage circuit of the DDC118
IC. A FIFO/USB interface based on FT2232C [12], a USB
serial communication IC from FTDI Technologies Inc., is
provided to handle high data transfer rates. The
microcontroller reads the data from the DDC118s via the SPI
interface and transfers the data to a PC via the FIFO/USB
interface. The data is read from the USB interface and written
into a file for data analysis. An RS-232 interface is provided to
be used primarily for configuring the system and also for
programming and debugging purposes. A prototype of the
DAU along with the photodetector array is shown in Fig. 2.
Fig. 2. Prototype of DAU with the photodetector array connected to the DAU
via a custom 1” x 1” header. The gold square is a standard microscope glass
slide coated with gold and the blobs on either side are wire bonds from the
header to the photodetector array, the small black unit in the center.
C. Firmware Design
LED modulation, integration time, integration capacitance,
and data acquisition without loss of data are controlled by
features implemented in the firmware. The integration
capacitors on side A and side B are not guaranteed to be
identical on the DDC118 devices. The mismatch is
compensated for in the firmware. The firmware makes use of
the dual integrators on DDC118 IC (sides A & B) in the
following way. The LED is enabled and the integration process
is started on side A. At the end of the integration time,
integration process is halted on side A and started on side B.
The result of the integration on side A with the LED on,
denoted by is acquired during integration of the signal on side
B. At the end of the integration period, the LED is disabled
and integration of the signal on side B is halted. Integration of
the signal with the LED off is begun on side A. The result
from side B integration, BON is acquired and added to AON to
result in data corresponding to the duration the LED is on. The
process is repeated with the LED disabled. The net results of
(AON + BON) and (AOFF + BOFF) are stored in long integer
arrays ON and OFF respectively. Each array has one element
corresponding to the particular channel. Preset number of
samples corresponding to the configured average time are
accumulated and transferred to a PC via the USB interface.
This technique reduces the load on the 8-bit microcontroller by
transmitting data once every few seconds (configured average
time) as opposed to continuously transmitting data via the
USB-FIFO device. Timing jitters because of delays due to full
buffers on the USB-FIFO are eliminated resulting in uniform
integration windows for both LED on as well as off cases. The
signal however is continuously acquired without loss although
at a reduce sample frequency. Limited resources of the 8-bit
microcontroller are efficiently used and the averaging
mechanism improves the noise performance. The LED is
modulated at 50 % duty cycle at the sample frequency
configured by the user. The integration signal that controls
which side is being integrated is modulated at 50 % duty cycle
at twice the frequency of the LED signal. The integration
period is set by an interrupt based timer to result in uniform
integration windows. Subtracting the LED disabled data from
the LED enabled data eliminates constant background noise.
Averaging the sampled data improved noise performance. The
signals from the photodiodes are continuously integrated with
no loss of signal.
IV. RESULTS
The DAU was successfully implemented and integrated with a
prototype of glucose sensor as shown in Fig. 3. An adapter
board was designed to accommodate the change in the glucose
sensor module packaging. A heat sink and temperature
controller were mounted on the glucose sensor for efficient
heat dissipation and to maintain constant working temperature
respectively. Experiments were conducted to evaluate the
performance specifications of the DAU particularly with
respect to noise characteristics and SNR characteristics in the
presence of a signal. Since ISF is composed mainly of water,
spectral data were recorded with water as the analyte in the
initial stages. The results are as follows.
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Chicago, IL, USA, 17-20 May, 2007.
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Fig. 3. Prototype of the Sensor-DAU system. Glucose sensor module is
plugged in a ZIF socket on the modified header of the DAU board. The red
and black wires are LED terminals; the other two wires (thin) are for
monitoring the temperature of the sensor module. The clear tube is the flow
channel for the analyte. Wires on the DAU board are to monitor signals
during the debugging phase.
A. Noise Characteristics
Two experiments were conducted to evaluate the noise
characteristics of the system. The first experiment measured
the noise under open circuit conditions with all of the 32
channels open i.e. no connections to the sensor at all. The
second experiment measured the noise in closed circuit
conditions under the absence of a signal. Since photodiodes
are sensitive to ambient light and can produce small currents
even when shielded from light, a suitable way to measure noise
is to simulate the presence of a photodiode by connecting a
resistor and a capacitor in parallel in lieu of the diode. A
photodiode can be modeled as a current source in parallel with
a resistor and a capacitor. Thus, such an arrangement is a
valid. Resistors of different values were connected across a
channel chosen arbitrarily from the 32 channels and the noise
was measured. The results from the open channel experiment
are depicted in Fig. 4.
Fig. 4. Noise measured with the input channels open-circuited. Noise values
are for sensor capacitance of 100 pF.
The manufacturer’s specifications for device noise (from
DDC118 data sheet) are plotted for comparison. Results of the
closed channel noise measurement are depicted in Fig. 5a and
Fig. 5b.
Fig. 5a. Noise measured across resistors connected to the input channels
of the DDC118. The open channel noise is provided for comparison.
Fig. 5b. DAU noise plotted as a function of the impedance. Impedance of the
photodiodes of the sensor is about 1 kΩ.
B. Spectral Data
Spectral data acquired using the DAU system with water as the
analyte is depicted in Fig. 6.
Fig. 6. Transmission spectrum of water in the NIR region collected using the
DAU system. The data shown are 5s averages collected over a period of 10
minutes. The thickness of the curve is an estimate of the drift or noise of the
system. The picture also shows mismatch in hardware conditions among the
DDC118s.
Resistor Terminated Channel Noise
-50
0
50
100
150
200
250
1 13 25 37 49 61 73 85 97 109 121 133 145 157 169 181 193 205 217 229 241 253 265 277 289 301 313 325
Sample No.
No
ise
in
mV 1K
10K
47K
Open
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Chicago, IL, USA, 17-20 May, 2007.
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The input signal was continuously integrated as explained in
the firmware design. Transimpedance gain was set at 8 x 107
Ω. The data corresponds to 5 second averages collected for
about 10 minutes. The thickness of the spectrum shows the
drift or noise of the DAU system with SNR of about 20 dB.
Also, saw edges can be noticed for channels 1-16. The crests
are even channels 2-16 connected to one DDC118 while the
troughs are odd channels 1-15 connected to a different
DDC118. This could be due to variations seen in reference
voltage and analog power supply seen at the two DDC118s
and also due to difference in capacitor sizes on different
DDC11s resulting in slightly different full scale range. We
continue to investigate the issue.
C. Discussion
It can be seen from the noise characteristics that the DAU
performs well when the channels are open-circuited but the
performance deteriorates when interfaced to the glucose
sensor, irrespective of the presence or absence of a signal. This
behavior can be attributed to the bias voltage applied by the
DDC118 to each of its input channels. The following
experiment justifies the reasoning. The input channels of the
DAU were terminated with resistors of different values and
subjected to the same integration times, and integrating
capacitances with no external signal applied to them. The data
collected in such a way is primarily composed of the Johnson
noise across the resistors along with the noise internal to the
DDC118 IC.
As shown by Fig. 5a and Fig. 5b, it can be seen that the
measured noise decreases with increasing resistance. This
counter-intuitive scenario can be explained as follows. The
DDC118 IC is a current input device whose input channel
circuitry can be modeled as shown by Fig. 7.
Fig. 7. Model of a resistor connected to the input channel of DDC118
It can be seen that the actual current being integrated on the
integrator capacitor is the sum of the resistor noise current and
the bias noise current, the current induced in the resistor
because of the bias voltage. The resistor noise increases with
resistance. However, in the case of low valued resistors, the
resistor noise is very small when compared to the bias current
shot noise. Thus the measured data primarily reflects the noise
current due to the bias voltage. The effect of the bias voltage
i.e. the noise current induced in the resistor, decreases with
resistance and becomes negligible for large values of
resistance. The DDC118 is designed for use with commercial
silicon photodiodes generally under reverse bias conditions to
with impedance (Rd in Fig. 8) in the order of few tens of
Megaohms. Reverse bias increases both the dark current as
well as the response time. For commercial photodiodes, signal
current is very high compared to the dark current and increase
in the dark current is generally not an issue compared to the
faster response times achieved due to reverse bias. Due to the
high impedance in such a scenario, the noise current induced
by Vbias is very small and can be neglected compared to the
signal current. In our case, the photodiodes operate under zero
bias conditions with impedance of the order of 1 KΩ thus
leading to low signal to noise ratios. The photodetector array
[13] is not a production part but a research grade prototype
with performance improvements being achieved over each
implementation. Zero bias is necessary to limit the shot noise
component due to the dark current.
Fig. 8. Model of a photodiode connected to the input channel of DDC118
D. Bias Compensation & Improved DAU
The DDC118 IC is designed for photodiodes often working
under reverse bias conditions and thus having impedances in
the mega ohms range. Because of the high impedance, the bias
voltage applied to the photodiode at the input channel does not
cause performance degradation. The photodiodes in the
detector array of the glucose sensor operate under zero bias
conditions to limit the magnitude of the dark current and have
impedance in the range of 1 kΩ. Dark currents under reverse
bias conditions can be in the order of few µA. A high dark
current increases the shot noise, one of the components of the
noise generated by a photodiode the other two being Johnson
noise and flicker noise.
When using DDC118 with low impedance photodiodes, the
effect of the bias voltage has to be compensated. Doing so
using a dedicated circuit in hardware is not suitable due to the
following reasons. Firstly, additional components increase the
real estate, which is not suitable for an implantable system.
Secondly, it is not possible to design a simple circuit that can
compensate for the bias voltage without itself applying a
voltage to the photodiode or loading the photodiode. However,
the effect of bias voltage can be compensated in software using
the same existing hardware set-up. The collected data can be
processed through a digital filter to estimate the contribution
from the actual signal. A better way is to incorporate a digital
filter in the firmware. A first order recursive Butterworth filter
with coefficients that are powers of 2 can be incorporated in
firmware [14]. A SNR of about 38 dB can be achieved with
such a filter. Though the filter coefficients are powers of 2, the
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Chicago, IL, USA, 17-20 May, 2007.
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compiler has to be smart to differentiate between coefficients
that are powers of 2 and coefficients that are not. A second
order recursive Butterworth filter [15] with a lower cut-off
frequency than the first order filter provides even better
performance and would be ideal for the sensor-DAU system.
The calculations involving a 2nd
order filter are too complex to
be implemented on an 8-bit microcontroller. The filter
coefficients were calculated using Matlab and the raw data was
processed using the filter on a PC. SNR of about 50 dB was
achieved using such a filter. The following figure depicts the
performance of the system with the second order digital filter.
Fig. 9. Digitally filtered water transmission spectrum with improved SNR.
The picture shows reduction in the thickness of the plot indicating better
noise performance.
V. FUTURE WORK
The processing requirements necessary to incorporate digital
filtering in firmware are beyond the feature set of an 8-bit
microcontroller. An improved DAU design based on a 16-bit
microcontroller with a dual core, a microcontroller core in
addition to a DSP core, has been developed and being tested
currently. The new PCBs are laid out in a way that limits the
digital switching noise induced in the analog side. The other
sources of noise are thermal noise, shot noise, and flicker noise
of the photodiodes. Thermal (or Johnson noise) is inversely
related to the impedance of the photodiode. Improving the
impedance of the photodiodes will lower the thermal noise and
also limit the effect of the bias voltage at the input channels of
DDC118 leading to better SNR. Flicker noise possesses a 1/f
spectral density and may dominate when the bandwidth of
interest contains frequencies less than 100 Hz. Higher
sampling rates will limit the flicker. A new generation of
photodetector array with impedance an order of magnitude
more than the present array is being developed by the research
group in charge of the fabricating the photodiodes. This will
decrease the effect of the bias voltage and improve the SNR by
an order of magnitude. Also, the DSP based design will permit
high sampling rates and make it possible to run complex filter
algorithms to further improve the SNR.
Efforts are being made to collect ISF spectral data and
measure glucose concentration levels under in-vivo conditions
using a laboratory rat.
VI. CONCLUSION
A DAU prototype supporting 32 photodiode channels has
been successfully implemented and interfaced with the glucose
sensor. The spectral data collected using the system was of a
quality comparable to the data collected using a commercial
state of the art National Instruments data acquisition bench top
module. Average SNR of 20.2 dB was obtained with the
existing set-up and the current generation photodetectors prior
to digital filtering. SNR of 50.7 dB was achieved using digital
filtering techniques with a scope of at least 15 dB enhancement
in the near future with improved photodetector array, better
processing capabilities, and improved hardware design.
ACKNOWLEDGMENT
The authors would like to thank Jon Olesberg of the Optical
Science & Technology Center and Dan Cooley of the
Embedded Systems & Non-Linear Optics Lab at the Iowa
Advanced Technology Labs of the University of Iowa for their
help during the course of the project.
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