Content for report on micro electronic pill

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CHAPTER-1
BASICS OF MICROELECTRONIC PILL
1.1 INTRODUCTION
The invention of the transistor enabled the first radiotelemetry capsules, which utilized simple
circuits for in vivo telemetric studies of the gastro intestinal (GI) tract [1].
These units could only transmit from a single sensor channel, and were difficult to assemble due
to the use of discrete components [2]. The measurement parameters consisted of either
temperature, pH or pressure, and the first attempts of conducting real-time noninvasive
physiological measurements suffered from poor reliability, low sensitivity, and short lifetimes of
the devices. The first successful pH gut profiles were achieved in 1972 [3], with subsequent
improvements in sensitivity and lifetime. Single-channel radiotelemetry capsules have since been
applied for the detection of disease and abnormalities in the GI tract [4] where restricted access
prevents the use of traditional endoscopy.
Most radiotelemetry capsules utilize laboratory type sensors such as glass pH electrodes,
resistance thermometers, or moving inductive coils as pressure transducers [5]. The relatively
large size of these sensors limits the functional complexity of the pill for a given size of capsule.
Adapting existing semiconductor fabrication technologies to sensor development has enabled the
production of highly functional units for data collection, while the exploitation of integrated
circuitry for sensor control, signal conditioning, and wireless transmission has extended the
concept of single-channel radiotelemetry to remote distributed sensing from microelectronic
pills.
Our current research on sensor integration and onboard data processing has, therefore, focused
on the development of microsystems capable of performing simultaneous multiparameter
physiological analysis. The technology has a range of applications in the detection of disease and
abnormalities in medical research. The overall aim has been to deliver enhanced functionality,
reduced size and power consumption, through system level integration on a common integrated
circuit platform comprising

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sensors, analog and digital signal processing, and signal transmission.
Fig 1.1 A Microelectronic pill
In this report, we present a novel analytical microsystem which incorporates a four-channel
microsensor array for real-time determination of temperature, pH, conductivity and oxygen. The
sensors were fabricated using electron beam and photolithographic pattern integration, and were
controlled by an application specific integrated circuit (ASIC), which sampled the data with 10-
bit resolution prior to communication off chip as a single interleaved data stream. An integrated
radio transmitter sends the signal to a local receiver (base station), prior to data acquisition on a
computer. Real-time wireless data transmission is presented from a model in vitro experimental
setup, for the first time. Details of the sensors are provided in more detail later, but included: a
silicon diode to measure the body core temperature, while also compensating for temperature
induced signal changes in the other sensors; an ion-selective field effect transistor, ISFET, [6] to
measure pH; a pair of direct contact gold electrodes to measure conductivity; and a three-
electrode electrochemical cell, to detect the level of dissolved oxygen in solution.

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Fig 1.2 parts of an MEP
All of these measurements will, in the future, be used to perform in vivo physiological
analysis of the GI-tract. For example, temperature sensors will not only be used to measure
changes in the body core temperature, but may also identify local changes associated with tissue
inflammation and ulcers. Likewise, the pH sensor may be used for the determination of the
presence of pathological conditions associated with abnormal pH levels, particularly those
associated with pancreatic disease and hypertension, inflammatory bowel disease, the activity of
fermenting bacteria, the level of acid excretion, reflux to the oesophagus, and the effect of GI
specific drugs on target organs. The conductivity sensor will be used to monitor the contents of
the GI tract by measuring water and salt absorption, bile secretion and the breakdown of organic
components into charged colloids. Finally, the oxygen sensor will measure the oxygen gradient
from the proximal to the distal GI tract. This will, in future enable a variety of syndromes to be

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investigated including the growth of aerobic bacteria or bacterial infection concomitant with low
oxygen tension [7], as well as the role of oxygen in the formation of radicals causing cellular
injury and pathophysiological conditions (inflammation and gastric ulceration).
The implementation of a generic oxygen sensor will also enable the development of first
generation enzyme linked amperometric biosensors, thus greatly extending the range of future
applications to include, e.g., glucose and lactate sensing, as well as immune-sensing protocols.

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CHAPTER- 2
MICROELECTRONIC PILL DESIGN AND FABRICATION
2.1 SENSORS
The sensors were fabricated on two silicon chips located at the front end of the capsule. Chip 1
[Fig. 1(a), (c), (e)] comprises the silicon diode temperature sensor, the pH ISFET sensor and a
two electrode conductivity sensor. Chip 2 [Fig. 1(b), (d), (f)] comprises the oxygen sensor and an
optional nickel-chromium (NiCr) resistance thermometer. The silicon platform of Chip 1 was
based on a research product from Ecole Superieure D’Ingenieurs en Electrotechnique et
Electronique (ESIEE, France) with predefined n-channels in the p-type bulk silicon forming the
basis for the diode and the ISFET. A total of 542 of such devices were batch fabricated onto a
single 4-in wafer. In contrast, Chip 2 was batch fabricated as a 9X9 array on a 380- m-thick
single crystalline 3n silicon wafer with <100> lattice orientation, precoated with 300 nm Si3N4,
silicon nitride, (Edinburgh Microfabrication Facility, U.K.). One wafer yielded 80, 5X5 mm2
sensors (the center of the wafer was used for alignment markers).
2.1.1 Sensor Chip 1:
An array of 4X2 combined temperature and pH sensor platforms were cut from the wafer and
attached on to a 100- m-thick glass cover slip using S1818 photoresist (Microposit, U.K.) cured
on a hotplate. The cover slip acted as temporary carrier to assist handling of the device during the
first level of lithography (Level 1) when the electric connection tracks, the electrodes and the
bonding pads were defined. The pattern was defined in S1818 resist by photolithography prior to
thermal evaporation of 200 nm gold (including an adhesion layer of 15 nm titanium and 15 nm
palladium). An additional layer of gold (40 nm) was sputtered to improve the adhesion of the
electroplated silver used in the reference electrode. Liftoff in acetone detached the chip array
from the cover slip. Individual sensors were then diced prior to their re-attachment in pairs on a
100- m-thick cover slip by epoxy resin.

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Fig 2.1- The microelectronic sensors
2.1(a) schematic diagram of Chip 1, measuring 4.75X5 mm2, comprising the pH (ISFET) sensor
(1), the 5X10-4 mm2 dual electrode conductivity sensor (3) and the silicon diode temperature
sensor (4);
2.1(b) schematic diagram of Chip 2, measuring 5X5 mm2 , comprising the electrochemical
oxygen sensor (2) and a NiCr resistance thermometer (5). Once integrated in the pill, the area
exposed to the external environment is illustrated by the 3-mm-diameter circle

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2.1(c) Photomicrograph of sensor Chip 1
2.1(d) Sensor chip 2. The bonding pads (6), which provide electrical contact to the external
electronic control circuit.
2.1(e) Close up of the pH sensor consisting of the integrated 3X10-2 mm Ag/AgCl reference
electrode (7), a 500-µm-diameter and 50–µm-deep, 10-nL, electrolyte chamber (8) defined in
polyimide, and the 15X600 µm floating gate (9) of the ISFET sensor
2.1(f) The oxygen sensor is likewise embedded in an electrolyte chamber (8). The three-electrode
electrochemical cell comprises the 1X10-1 mm counter electrode (10), a microelectrode array of
57X10 µm diameter (4.5X103 mm2 ) working electrodes (11) defined in 500-nm-thick PECVD
Si3N4 , and an integrated 1.5x10-2 mm Ag/AgCl reference electrode (12).

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In Fig. 1(c) the left-hand-side (LHS) unit comprised the diode, while the right-hand-side
(RHS) unit comprised the ISFET. The 15x600 µm (LxW) floating gate of the ISFET was pre-
covered with a 50-nm-thick proton sensitive layer of Si3N4 for pH detection.
Photo curable polyimide (Arch Chemicals, Belgium) defined the 10-nL electrolyte
chamber for the pH sensor (above the gate) and the open reservoir above the conductivity sensor
(Level 2).
The silver chloride reference electrode (3x10-2 mm2) was fabricated during Levels 3 to 5,
inclusive. The glass cover slip, to which the chips were attached, was cut down to the size of the
4.75x5 mm2 footprint (still acting as a supporting base) prior to attachment on a custom-made
chip carrier used for electroplating. Silver (5 µm) was deposited on the gold electrode defined at
by chronopotentiometry (300 nA, 600 s) after removing residual polyimide in an barrel asher
(Electrotech, U.K.) for 2 min. The electroplating solution consisted of 0.2 M, 3MKI and 0.5M.
Changing the electrolyte solution to 0.1 M KCl at Level 4 allowed for the electroplated silver to
be oxidized to AgCl by chronopoteniometry (300 nA, 300 s). The chip was then removed from
the chip carrier prior to injection of the internal 1 M KCl reference electrolyte required for the
Ag AgCl reference electrode (Level 5). The electrolyte was retained in a 0.2% gel matrix of
calcium alginate [8].
The chip was finally clamped by a 1-mm-thick stainless-steel clamp separated by a 0.8- m-
thick sheet of Viton fluoroelastomer (James Walker, U.K.). The rubber sheet provided a uniform
pressure distribution in addition to forming a seal between the sensors and capsule.
2.1.2 Sensor Chip 2
The level 1 pattern (electric tracks, bonding pads, and electrodes) was defined in 0.9 m
UV3 resist (Shipley, U.K.) by electron beam lithography. A layer of 200 nm gold (including an
adhesion layer of 15 nm titanium and 15 nm palladium) was deposited by thermal evaporation.
The fabrication process was repeated (Level 2) to define the 5- m-wide and 11-mm-long
NiCr resistance thermometer made from a 100-nm-thick layer of NiCr (30- resistance). Level 3

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defined the 500-nm-thick layer of thermal evaporated silver used to fabricate the reference
electrode. An additional sacrificial layer of titanium (20 nm) protected the silver from oxidation
in subsequent fabrication levels. The surface area of the reference electrode was mm, whereas
the counter electrode made of gold had an area of mm . Level 4 defined the microelectrode array
of the working electrode, comprising 57 circular gold electrodes, each 10 m in diameter, with an
inter-electrode spacing of 25 m and a combined area of 4.5x10-3 mm2. Such an array promotes
electrode polarization and reduces response time by enhancing transport to the electrode surface
[9]. The whole wafer was covered with 500 nm plasma-enhanced chemical vapor deposited
(PECVD) Si3N4. The pads, counter, reference, and the microelectrode array of the working
electrode was exposed using an etching mask of S1818 photoresist prior to dry etching with
C2F6. The chips were then diced from the wafer and attached to separate 100- m-thick cover slips
by epoxy resin to assist handling. The electrolyte chamber was defined in 50- m-thick polyimide
at Level 5. Residual polyimide was removed in an O2 barrel asher (2 min), prior to removal of
the sacrificial titanium layer at Level 6 in a diluted HF solution (HF to RO water, 1:26) for 15 s.
The short exposure to HF prevented damage to the PECVD layer.
Thermally evaporated silver was oxidized to Ag AgCl (50% of film thickness) by
chronopotentiometry (120 nA, 300 s) at Level 7 in the presence of KCl, prior to injection of the
internal reference electrolyte at Level 8. A 5.5 mm2 sheet of oxygen permeable teflon was cut out
from a 12.5- m-thick film and attached to the chip at Level 9 with epoxy resin prior to
immobilization by the aid of a stainless steel clamp.
2.2 CONTROL CHIP
The ASIC was a control unit that connected together the external components of the microsystem
(Fig. 2). It was fabricated as a 22.5 mm2 silicon die using a 3-V, 2-poly, 3-metal 0.6- µm. CMOS
process by Austria Microsystems (AMS) via the Europractice initiative.

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Fig 2.2: Photograph of the 4.75x4.75 mm2 application specific integrated Circuit control
chip
2.2(a) The associated explanatory diagram
2.2(b) Schematic of IC control chip of the architecture
2.2(c) Illustrating the interface to external, MUX(four-channel multiplexer), ADC, DAC and
OSC(32-kHz oscillator).

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It is a novel mixed signal design that contains an analog signal conditioning module operating
the sensors, a 10-bit analog-to-digital (ADC) and digital-to-analog (DAC) converters, and a
digital data processing module. An RC relaxation oscillator (OSC) provides the clock signal.
The analog module was based on the AMS OP05B operational amplifier, which offered a
combination of both a powersaving scheme (sleep mode) and a compact integrated circuit
design. The temperature circuitry biased the diode at constant current, so that a change in
temperature would reflect a corresponding change in the diode voltage. The pH ISFET sensor
was biased as a simple source and drain follower at constant current with the drain-source
voltage changing with the threshold voltage and pH. The conductivity circuit operated at direct
current measuring the resistance across the electrode pair as an inverse function of solution
conductivity. An incorporated potentiostat circuit operated the amperometric oxygen sensor with
a 10-bit DAC controlling the working electrode potential with respect to the reference. The
analog signals had a full-scale dynamic range of 2.8 V (with respect to a 3.1-V supply rail) with
the resolution determined by the ADC. The analog signals were sequenced through a multiplexer
prior to being digitized by the ADC. The bandwidth for each channel was limited by the
sampling interval of 0.2 ms.
The digital data processing module conditioned the digitized signals through the use of a
serial bitstream data compression algorithm, which decided when transmission was required by
comparing the most recent sample with the previous sampled data. This technique minimizes the
transmission length, and is particularly effective when the measuring environment is at
quiescent, a condition encountered in many applications [10].
The entire design was constructed with a focus on low power consumption and immunity
from noise interference. The digital module was deliberately clocked at 32 kHz and employed a
sleep mode to conserve power from the analog module. Separate on-chip power supply trees and
pad-ring segments were used for the analog and digital electronics sections in order to discourage
noise propagation and interference.

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2.3 RADIO TRANSMITTER
The radio transmitter was assembled prior to integration in the capsule using discrete surface
mount components on a single sided printed circuit board (PCB). The footprint of the standard
transmitter measured 8x5x3 mm including the integrated coil (magnetic) antenna. It was
designed to operate at a transmission frequency of 40.01 MHz at 20 C generating a signal of 10
kHz bandwidth. A second crystal stabilized transmitter was also used. This second unit was
similar to the free running standard transmitter, apart from having a larger footprint of 10x5x3
mm, and a transmission frequency limited to 20.08 MHz at 20 C, due to the crystal used. Pills
incorporating the standard transmitter were denoted Type I, whereas the pills incorporating the
crystal stabilized unit were denoted Type II. The transmission range was measured as being 1
meter and the modulation scheme frequency shift keying (FSK), with a data rate of 1 kbs-1.
2.4 CAPSULE
The microelectronic pill consisted of a machined biocompatible (noncytotoxic), chemically
resistant polyether-terketone (PEEK) capsule (Victrex, U.K.) and a PCB chip carrier acting as a
common platform for attachment of the sensors, ASIC, transmitter and the batteries. The
fabricated sensors were each attached by wire bonding to a custom made chip carrier made from
a 10-pin, 0.5-mm pitch polyimide ribbon connector.
The ribbon connector was, in turn, connected to an industrial standard 10-pin flat cable
plug (FCP) socket (Radio Spares, U.K.) attached to the PCB chip carrier of the microelectronic
pill, to facilitate rapid replacement of the sensors when required. The PCB chip carrier was made
from two standard 1.6-mm-thick fiber glass boards attached back to back by epoxy resin which
maximized the distance between the two sensor chips. The sensor chips were connected to both
sides of the PCB by separate FCP sockets, with sensor Chip 1 facing the top face, with Chip 2
facing down. Thus, the oxygen sensor on Chip 2 had to be connected to the top face by three
200- m copper leads soldered on to the board. The transmitter was integrated in the PCB which
also incorporated the power supply rails, the connection points to the sensors, as well as the

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transmitter and the ASIC and the supporting slots for the capsule in which the chip carrier was
located.
The ASIC was attached with double-sided copper conducting tape (Agar Scientific, U.K.) prior
to wire-bonding to the power supply rails, the sensor inputs, and the transmitter (a process which
entailed the connection of 64 bonding pads). The unit was powered by two standard 1.55-V
SR44 silver oxide cells with a capacity of 175 mAh. The batteries were serial connected and
attached to a custom made 3-pin, 1.27-mm pitch plug by electrical conducting epoxy
(Chemtronics, Kennesaw, GA).
The connection to the matching socket on the PCB carrier provided a three point power
supply to the circuit comprising a negative supply rail ( 1.55 V), virtual ground (0 V), and a
positive supply rail (1.55 V). The battery pack was easily replaced during the experimental
procedures.

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Fig 2.3 Schematic diagram (top) of the remote mobile analytical microsystem comprising
the electronic pill.

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In the figure, the prototype is 16x55 mm, weights 13.5 g. The Type I unit consist of the
microelectronic sensors at the front enclosed by the metal clamp and rubber seal (1) which
provide a 3-mm-diameter access channel to the sensors (2). The front section of the capsule,
physically machined from solid PEEK, is illustrated (3) with the rear section removed to
illustrate the internal design. The front and rear section of the capsule is joined by a screw
connection sealed off by a Viton-rubber O-ring (4). The ASIC control chip (5) is integrated on
the common PCB chip carrier (6) which incorporates the discrete component radio transmitter
(7), and the silver oxide battery cells (8).
The battery is connected on the reverse side of the PCB (9). The Type II unit is identical to
the Type I with exception of an incorporated crystal stabilized radio transmitter (10) for
improved temperature stability.
The capsule was machined as two separate screw-fitting compartments. The PCB chip
carrier was attached to the front section of the capsule (Fig. 3). The sensor chips were exposed to
the ambient environment through access ports and were sealed by two sets of stainless steel
clamps incorporating a 0.8-m thick sheet of Viton fluoroelastomer seal. A 3-mm-diameter access
channel in the center of each of the steel clamps (incl. the seal), exposed the sensing regions of
the chips. The rear section of the capsule was attached to the front section by a 13-mm screw
connection incorporating a Viton rubber O-ring (James Walker, U.K.). The seals rendered the
capsule water proof, as well as making it easy to maintain (e.g., during sensor and battery
replacement). The complete prototype was 16x55 mm and weighted 13.5 g including the
batteries. A smaller pill suitable for physiological in vivo trials (10x30 mm) is currently being
developed from the prototype.

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CHAPTER-3
MATERIAL AND METHODS
3.1 GENERALEXPERIMENTALSETUP
All the devices were powered by batteries in order to demonstrate the concept of utilizing the
microelectronic pill in remote locations (extending the range of applications from in vivo sensing
to environmental or industrial monitoring). The pill was submerged in a 250-mL glass bottle
located within a 2000-mL beaker to allow for a rapid change of pH and temperature of the
solution. A scanning receiver (Winradio Communications, Australia) captured the wireless radio
transmitted signal from the microelectronic pill by using a coil antenna wrapped around the
2000-mL polypropylene beaker in which the pill was located.
A portable Pentium III computer controlled the data acquisition unit (National Instruments,
Austin, TX) which digitally acquired analog data from the scanning receiver prior to recording it
on the computer. The solution volume used in all experiments was 250 mL. The beaker, pill,
glass bottle, and antenna were located within a 25x25 cm container of polystyrene, reducing
temperature fluctuations from the ambient environment (as might be expected within the GI
tract) and as required to maintain a stable transmission frequency. The data was acquired using
LabView (National Instruments, Austin, TX) and processed using a MATLAB (Mathworks,
Natick, MA) routine.
3.2 SENSOR CHARACTERIZATION
The lifetime of the incorporated Ag AgCl reference electrodes used in the pH and oxygen
sensors was measured with an applied current of 1 pA immersed in a 1.0 M KCl electrolyte
solution. The current reflects the bias input current of the operational amplifier in the analog
sensor control circuitry to which the electrodes were connected. The temperature sensor was
calibrated with the pill submerged in reverse osmosis (RO) water at different temperatures. The
average temperature distribution over 10 min was recorded for each measurement, represented as
9.1ºC, 21.2ºC, 33.5ºC, and 47.9ºC. The system was allowed to temperature equilibrate for 5 min

17
prior to data acquisition. The control readings were performed with a thin wire K-type
thermocouple (Radio Spares, U.K.). The signal from the temperature sensor was investigated
with respect to supply voltage potential, due to the temperature circuitry being referenced to the
negative supply rail. Temperature compensated readings (normalized to 23ºC) were recorded at a
supply voltage potential of 3.123, 3.094, 3.071, and 2.983 mV using a direct communication
link. Bench testing of the temperature sensor from 0ºC to 70ºC was also performed to investigate
the linear response characteristics of the temperature sensor. The pH sensor of the
microelectronic pill was calibrated in standard pH buffers [28] of pH 2, 4, 7, 9, and 13, which
reflected the dynamic range of the sensor. The calibration was performed at room temperature
(23ºC) over a period of 10 min, with the pill being washed in RO water between each step. A
standard lab pH electrode was used as a reference to monitor the pH of the solutions (Consort
n.v., Belgium). The pH channel of the pill was allowed to equilibrate for 5 min prior to starting
the data acquisition. Each measurement was performed twice. Bench test measurements from pH
1 to 13 were also performed using an identical control circuit to the ASIC.
The oxygen sensor was bench tested with a standard laboratory potentiostat (Bioanalytical
Systems, West Lafayette, IN), over its dynamic range in phosphate buffered saline (PBS) using a
direct communication link at 23ºC. Cyclic voltammetry with a sweep potential from 0.1 to
0.45V(versus Ag AgCl)was performed in 1-mM ferroscene monocarboxylic acid (FMCA) as a
model redox compound, to test the performance of the microelectrode array. A three-point
calibration routine was performed at oxygen concentrations of 0 mg L-1 (PBS saturated with 2 M
Na2S2O3), 4 mg L-1 (PBS titration with 2 M Na2S2O3) and 8.2 mg L-1 (oxygen saturated PBS
solution). The solution saturated with dissolved oxygen was equilibrated overnight prior to use.
The dissolved oxygen was monitored using a standard Clark O2 electrode (Orion Research Inc.,
Beverly, MA). The reduction potential of water was assessed in oxygen depleted PBS, to avoid
interference from oxygen, at the same time assessing the lower potential limit that could be used
for maximizing the efficiency of the sensor. The voltage was then fixed above this reduction
potential to assess the dynamic behavior of the sensor upon injection of saturated Na2S2O3 in
oxygen saturated PBS.

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3.3 TRANSMISSION
The pill’s transmission frequency was measured with respect to changes in temperature.
The Type I pill (without crystal) was submerged in RO water at temperatures of 1ºC, 11ºC, 23ºC,
and 49ºC, whereas the Type II pill (with crystal) was submerged in temperatures of 2ºC, 25ºC,
and 45ºC. The change in frequency was measured with the scanning receiver, and the results
used to assess the advantage of crystals stabilized units at the cost of a larger physical size of the
transmitter.
3.4 DYNAMIC MEASUREMENTS
Dynamic pH measurements were performed with the pill submerged in a PBS solution at
23 C. The pH was changed from the initial value of 7.3 by the titration of 0.1 M H2SO4 and 0.1
M NaOH, respectively. Subsequently, the pH was changed from pH 7.3 to pH 5.5 (after 5 min),
pH 3.4 (after 8 min) to pH 9.9 (after 14 min) and back to pH 7.7 (after 21 min). A standard
(bench-top) pH electrode monitored the pH of the solution. The solutions were sampled after the
pH change, and measured outside the experimental system to prevent electronic noise injection
from the pH electrode. The temperature channel was recorded simultaneously.
3.5 SENSOR AND SIGNAL DRIFT
Long term static pH and temperature measurements were performed to assess signal drift
and sensor lifetime in physiological electrolyte (0.9% saline) solutions. A temperature of 36.5 C
was achieved using a water bath, with the assay solutions continuously stirred and re-circulated
using a peristaltic pump. The sensors were transferred from solutions of pH 4 to pH 7, within 2 h
of commencing the experiment, and from pH 7 to pH 10.5, after 4 h. The total duration of the
experiment was 6 h. Each experiment was repeated twice.

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CHAPTER-4
PERFORMANCE
The power consumption of the microelectronic pill with the transmitter, ASIC and the
sensors connected was calculated to 12.1 mW, corresponding to the measured current
consumption of 3.9 mA at 3.1-V supply voltage. The ASIC and sensors consumed 5.3 mW,
corresponding to 1.7 mA of current, whereas the free running radio transmitter (Type I)
consumed 6.8 mW (corresponding to 2.2 mA of current) with the crystal stabilized unit (Type II)
consuming 2.1 mA. Two SR44 batteries used provided an operating time of more than 40 h for
the microsystem.
4.1 TEMPERATURE CHANNEL PERFORMANCE
The linear sensitivity was measured over a temperature range from 0 C to 70 C and found
to be 15.4 mVºC-1. This amplified signal response was from the analog circuit, which was later
implemented in the ASIC. The sensor [Fig. 4(a)], once integrated in the pill, gave a linear
regression of 11.9 bitsºC-1 (f(T0c) = 11.9(T0C) – 42.7, R2 = 0.99), with a resolution limited by the
noise band of 0.4ºC [Fig. 4(b)]. The diode was forward biased with a constant current (15 A)
with the n-channel clamped to ground, while the p-channel was floating.
Since the bias current supply circuit was clamped to the negative voltage rail, any change
in the supply voltage potential would cause the temperature channel to drift. Thus, bench test
measurements conducted on the temperature sensor revealed that the output signal changed by
1.45 mV per mV change in supply voltage ( f(mV) = -1.45 (mV) + 2584, R2 = 0.99) with f(mV)
expressed in millivolts, corresponding to a drift of -21 mVh-1 in the pill from a supply voltage
change of -14.5 mVh-1 .

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Fig 4.1 Temperature sensor
4.1(a). Temperature recording over a range from 9.1 C to 47.9 C, represented by digital data
points
4.1(b). High-resolution plot of a temperature change from 49.8ºC to 48.7ºC

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4.2 pH CHANNEL PERFORMANCE
The linear characteristics from pH 1 to 13 corresponded to a sensitivity of -41.7mV pH-1
unit at 23ºC, which is in agreement with literature values [6] although the response was lower
than the Nernstian characteristics found in standard glass pH electrodes (-59.2 mV pH-1 unit).
The pH ISFET sensor operated in a constant current mode (15 µA), with the drain voltage
clamped to the positive supply rail, and the source voltage floating with the gate potential. The
Ag AgCl reference electrode, representing the potential in which the floating gate was referred
to, was connected to ground. The sensor performance, once integrated in the pill [Fig. 5(a)],
corresponded to 14.85 bits pH-1 which gave a resolution of 0.07 pH per datapoint. The calibrated
response from the pH sensor conformed to a linear regression (f(pH) = -14.85(pH) + 588, R2 =
0.98), although the sensor exhibited a larger responsivity in alkaline solutions. The sensor
lifetime of 20 h was limited by the Ag/AgCl reference electrode made from electroplated silver.
The pH sensor exhibited a signal drift of -6 mV h-1. (0.14 pH), of which -2.5 mV h-1 was
estimated to be due to the dissolution of AgCl from the reference electrode. The temperature
sensitivity of the pH-sensor was measured as 16.8 mVºC-1 . Changing the pH of the solution at
40ºC from pH 6.8 to pH 2.3 and pH 11.6 demonstrated that the two channels were completely
independent of each other and that there was no signal interference from the temperature channel
[Fig. 4.2(b)].

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Fig 4.2 pH SENSOR
4.2(a) pH recording in the range of pH 2 to 13, represented by digital datapoints
4.2(b) dynamic recording of temperature (1) and pH (2) using a direct communication link

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4.3 OXYGEN SENSOR PERFORMANCE
The electrodes were first characterized using the model redox compound FMCA, showing
that the oxygen sensor behaved with classic microelectrode characteristics [9]. The reduction
potential of water was subsequently measured at 800 mV (Versus the integrated Ag AgCl) by
recording the steady-state current in oxygen-depleted PBS, thereby excluding any interfering
species. In order to calibrate the sensor, a three point calibration was performed (at saturated
oxygen, and with oxygen removed by the injection of Na2S2O3 to a final concentration of 1 M).
The steady state signal from the oxygen saturated solution was recorded at a constant
working electrode potential of -700 mV (versus Ag AgCl), which was below the reduction
potential for water. This generated a full-scale signal of 65 nA corresponding 8.2 mg O2 L-1 . The
injection Na2S2O3 of into the PBS after 90 s provided the zero point calibration. This fall in the
reduction current provided corroborative evidence that dissolved oxygen was being recorded, by
returning the signal back to the baseline level once all available oxygen was consumed. A third,
intermediate point was generated through the addition of 0.01M Na2S2O3. The resulting
calibration graph conformed to a linear regression (f(MgO2) = 7.9(MgO2), R2 = 0.99) with
expressed in nanoamperes. The sensitivity of the sensor was 7.9 nA mg-1 O2, with the resolution
of 0.4 mg L-1 limited by noise or background drift. The lifetime of the integrated Ag/AgCl
reference electrode, made from thermal evaporated silver, was found to be to 45 h, with an
average voltage drift of -1.3 mV h-1 due to the dissolution of the AgCl during operation. Both
measurements of FMCA and oxygen redox behavior indicated a stable Ag AgCl reference.
4.4 CONDUCTIVITY SENSOR PERFORMANCE
The prototype circuit exhibited a logarithmic performance from 0.05 to 10 mS/cm which
conformed to a first-order regression analysis (f(mS/cm)= 165 ln (mS/cm) + 850), R2=0.99) with
f(mS/cm) expressed in millivolts. The sensor saturated at conductivities above 10 mS/cm due to
the capacitive effect of the electric double layer, a phenomena commonly observed in
conductimetric sensor systems [12].

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4.5 CONTROL CHIP
The background noise from the ASIC corresponded to a constant level of 3-mV peak-to-
peak, which is equivalent to one least significant bit (LSB) of the ADC. Since the second LSB
were required to provide an adequate noise margin, the 10-bit ADC was anticipated to have an
effective resolution of 8 bits.
4.6 TRANSMISSION FREQUENCY
Frequency stabilized units were essential to prevent the transmission drifting out of range,
particularly if the pill was subject to a temperature change during operation. The standard Type I
transmitter exhibited a negative linear frequency change from 39.17 MHz at 1 C to 38.98 MHz at
49 C. The transmitter’s signal magnitude was not affected with the pill immersed in the different
electrolyte solutions or RO water, compared to the pill surrounded by air only. Tests were also
conducted with the pill immersed in the large polypropylene beaker filled with 2000 mL of PBS
without the signal quality being compromised. The electromagnetic noise baseline was measured
to 78 dB of S/N in the 20 MHz band of the crystal stabilized transmitter.
4.7 DUAL CHANNEL WIRELESS SIGNAL TRANSMISSION
Dual channel wireless signal transmission was recorded from both the pH and temperature
channels at 23ºC, with the pill immersed in a PBS solution of changing pH. The signal from the
pH channel exhibited an initial offset of 0.2 pH above the real value at pH 7.3. In practice, the
pH sensor was found to exhibit a positive pH offset as the solution became more acidic, and a
negative pH offset as the solution became more alkaline. The response time of the pH sensor was
measured to 10 s. The temperature channel was unaffected by the pH change, confirming the
absence of crosstalk between the two channels in Fig. 4.2(b).

25
CHAPTER-5
ADVANTAGES
 It is beneficial to detect the diseases and malfunctioning in the remote areas of gastro
intestinal tract just like pancreatic disease, inflammatory bowel disease, activity of
fermented bacteria, acidic level and oesophagus reflux which is out of reach for
conventional endoscopic device.
 It can be used in corrosive surrounding of GI tract.
 It consumes very less power as it operates in Programmable Standby Mode.
 Its practical application is very simple as it has very small in size.
 The battery lasts for 40 hours which is sufficient to carry out any type of complete
internal diagnosis.
 The transmission length is limited to a distance of only one meter, so it has zero noise
interference.

26
CHAPTER-6
DISADVANTAGES
 The ultrasonic activities and impedance topographies cannot be performed by this.
 It is unable to detect radiation abnormalities.
 The treatment through Micro Pill is very expensive and is not available in many regions.
 The size of pill is small but it is not as small that can be digested by small babies.

27
CONCLUSION
Human body is very sensitive even for small changes. Many times the doctors fail to interpret the
diseases and abnormalities which make the curing of diseases more difficult, so the Micro
Electronic pill is developed by the scientists to overcome from this problem and quick diagnosis
is possible by this innovation. To carry out above process efficiently a radio system of high
capacity is needed for this technology to get real time video of digestive system wirelessly, this
requires Upper Wide Bandwidth Transmitter and Receiver. But tissue damage at high frequency
limited its usage. Research work is carried out to get the detailed images of internal parts through
high frequency transmission and reception of data without damage to tissues of human body.

28
REFERENCES
[1] S. Mackay and B. Jacobson, “Endoradiosonde,” Nature, vol. 179, pp. 1239–1240, 1957.
[2] H. S.Wolff, “The radio pill,” New Scientist, vol. 12, pp. 419–421, 1961.
[3] S. J. Meldrum, B. W. Watson, H. C. Riddle, R. L. Bown, and G. E. Sladen, “pH profile of gut
as measured by radiotelemetry capsule,” Br. Med. J., vol. 2, pp. 104–106, 1972.
[4] S. S. Kadirkamanathan, E.Yazaki, D. F. Evans, C. C. Hepworth, F. Gong, and C. P. Swain,
“An ambulant porcine model of acid reflux used to evaluate endoscopic gastroplasty,” Gut, vol.
44, no. 6, pp. 782–788, June 1999.
[5] S. Mackay, “Radio telemetering from within the body,” Science, vol. 134, pp. 1196–1202,
1961.
[6] C. Cane, I. Gracia, and A. Merlos, “Microtechnologies for pH ISFET chemical sensors,”
Microelectr. J., vol. 28, no. 4, pp. 389–405, May 1997.
[7] L. E. Bermudez, M. Petrofsky, and J. Goodman, “Exposure to low oxygen tension and
increased osmolarity enhance the ability of Myobacterium avium to enter intertestinal epithelial
(HT-29) cells,” Infect. Immun., vol. 65, no. 9, pp. 3768–3773, Sep. 1997.
[8] H. Suzuki, N. Kojima, A. Sugama, F. Takei, and K. Ikegami, “Disposable oxygen electrodes
fabricated by semiconductor techniques and their applications to biosensors,” Sens. Actuators B,
vol. 1, no. 1–6, pp. 528–532, Jan. 1990.
[9] M. E. Sandison, N. Anicet, A. Glidle, and J. M. Cooper, “Optimization of the geometry and
porosity of microelectrode arrays for sensor design,” Anal. Chem., vol. 74, no. 22, pp. 5717–
5725, Oct. 2002.
[10] L.Wang, T. B. Tang, E. A. Johannessen, A. Astaras, A. F. Murray, J. M. Cooper, S. P.
Beaumont, and D. R. S. Cumming, “An integrated sensor microsystem for industrial and
biomedical applications,” in Proc. IEEE Instrumentation Measurement Technology Conf., vol. 2,
Anchorage, AK, 2002, pp. 1717–1720.
[11] R. M. C. Dawson, D. C. Elliott, W. H. Elliott, and K. M. Jones, Data for Biochemical
Research, 3rd ed. Oxford, U.K.: Clarendon, 1986, pp. 1–580.
[12] H. Morgan and N. Green, AC Electrokinesis: Colloids and Nanoparticles. Baldock, U.K.:
Research Studies Press Ltd, 2003, pp. 1–324.

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