This project monitors important body parameters like temperature, ECG, pulse using sensors connected to a processing unit interfaced with a computer. This allows doctors to remotely analyze patient conditions and reduces their workload. It also incorporates alarms for when the saline bottle is empty or if the patient needs assistance. The hardware is built on a printed circuit board with a DSPIC30F4013 processor. It interfaces with a computer via RS232. Software is compiled using Visual Basic to modify alarm settings and record data.

1. CHAPTER 1
INTRODUCTION
ABSTRACT
This project is a working model which incorporates sensors to
measure important body parameters namely the body temperature,
respiratory temperature, pulse and ECG. The sensors are connected to a
processing unit which is interfaced to a computer so that the condition of a
patient can be analyzed by doctors wherever they are. Thus it reduces
doctor’s work load and also gives more accurate results.
. A saline monitoring system has been incorporated, which gives an
alarm when the saline bottle is about to be empty. The data collected by the
PC are recorded in separate files with date and time, which can be used for
future references by the doctors. A patient calling switch is also incorporated
which can be used by the patient to get the attention of the doctors whenever
he needs immediate medical assistance. Even when the patient is in an
unconscious condition, the above mentioned parameters will be sensed and
suitable alerts will be generated.
The hardware of this project is built on a printed circuit board,
constituting DSPIC30F4013. It is a versatile DSP processor with in-built
features such as a 12 bit multi-channel ADC, USART, synchronous serial
port, programmable low voltage detection circuit etc. This is to be interfaced
to PC system through RS232C. The necessary signals from the external
cords, like different patients’ body and respiratory temperatures can be
converted into digital form by giving them to the DSPIC. The software is
1

2. compiled using Visual Basic and can be easily modified for any alarm
setting or record intervals.
1.1 Complete Body Scanning System
The objective of patient monitoring is to have a quantitative
assessment of the important physiological variables of patients during
critical periods of biological functions. For diagnostic and research
purposes, it is necessary to know their actual values or possible trends in
changes. The long term objective of patient monitoring, is to decrease
mortality and morbidity by
(i) Organization and display of information in a meaningful
form to improve patient care.
(ii) Correlation of multiple parameters for clear demonstration of
clinical problems.
(iii) Processing of the data to set alarms on the development of
abnormal conditions.
(iv) Ensuring better care with fewer staff members.
Complete Body Scanning System deals with real time continuous
monitoring and recording of some of the parameters like body temperature,
electrocardiogram, respiratory temperature as well as their analysis. It also
incorporates an alarm system for the patient calling switch, saline level
monitoring and temperature monitoring. With the advent of computerization
in the biomedical field, this project has wide scope, as it incorporates in it,
computerized data acquisition, monitoring and control. It reduces the
workload of doctors and also gives more accurate results.
2

3. FIG 1.1 COMPLETE BODY SCANNING SYSTEM
3

4. 1.2 REPORT OUTLINE:
Chapter 2 deals with the features of Complete Body Scanning
System. Chapter 3 serves the hardware details of this project namely the
various types of transducers and detectors used, the DSPIC Processor used
and the interfacing between the processor and the PC. Chapter 4 deals with
the assembling of the complete system. Chapter 5 describes the software
implementation comprising of the assembly programming of DSPIC and
front end tool Visual Basic. Chapter 6 contains the testing and verification
results. Chapter 7 deals with the conclusion of this project and future plans.
4

5. CHAPTER TWO
FEATURES OF COMPLETE BODY SCANNING SYSTEM
2.1 HARDWARE USED:
 DSPIC30F4013
 Transducers:
 Thermistor
 Silver- Silver Chloride Electrode
 Infrared Emitter and Detector
 Signal Conditioning Circuit
 Wireless transmitter TX1 433.92MHz-S
 Wireless receiver Rx3304
 RS232
 Single and dual phase Power Supply
5

6. A Block diagram of Complete Body Scanning System is shown in fig 2.1
FIG 2.1: BLOCK DIAGRAM CBSS
It consists of the following blocks:
• Body and respiratory temperature measurement
• Electro Cardiogram (ECG) measuring unit
• Heart rate measuring system
• Saline monitoring system
• Patient calling switch
• Doctor availability system
6

7. 2.2 BODY AND RESPIRATORY TEMPERATURE MEASUREMENT
Thermistor is used to sense the body and respiratory temperature. Its
good sensitivity, ruggedness and low cost make it an apt choice. Thermistor
is a passive transducer whose O/P depends on the excitation voltage applied
to it. If the excitation voltage changes with respect to the supply voltage
change, O/P of the thermistor changes in spite of no change in the body
temperature. Essentially a constant excitation voltage source is provided to
the thermistor which will not change with respect to the supply voltage
change
2.3 ELECTRO CARDIOGRAM (ECG) MEASURING UNIT:
The electrocardiogram, or ECG / EKG is a surface measurement of
the electrical potential generated by electrical activity in cardiac tissue.
Current flow, in the form of ions, signals the contraction of cardiac muscle
fibers leading to the heart's pumping action.
A three lead ECG monitoring system is used whose inputs are
voltages from three sensors kept at various parts of the body all signal
conditioned by an external card and given to the PC through the DSPIC. An
interactive program in Visual Basic is developed to read the voltage signals
and study them with the help of a waveform pattern. The three leads used are
silver electrodes. Fig 2.2 shows a block diagram of the ECG circuit.
7

8. FIG 2.2: BLOCK DIAGRAM OF ECG CIRCUIT
FIG 2.3: ECG MONITORING
2.4 HEART RATE MEASURING SYSTEM:
The heartbeat rate of a patient can be measured using this system. The
heart beat rate is measured in beats per minute. A heart beat sensor is used
for the purpose of measuring the heart beat rate. The patient’s finger is
inserted into the infrared-based sensor as shown in fig 2.4, which counts the
number of beats per minute.
8

9. FIG 2.4: HEART BEAT RATE MEASURING SYSTEM
2.5 SALINE MONITORING SYSTEM:
Saline monitoring is the process of monitoring the level of saline
solution in the saline bottle used for the patient. When the level goes
below a preset value [finishing stage], information is passed on to the
centralized computing center for further actions like changing to a new
bottle or stopping the flow permanently
For saline level monitoring, infrared emitter and detector are used
which are placed in such a way that the saline bottle passes between
them. They are placed near the neck of the saline bottle. As long as saline
solution is present, the path of the infrared rays is blocked and the
infrared detector is blocked from collecting infrared rays from the
infrared emitter. And so the output will be a logical low. When the saline
level drops, the output will be a logical high. The Block diagram of saline
9

10. monitoring system is shown in fig 2.5. The software is developed to give
an alarm when the logical high output is attained and given to the DSPIC
Processor. A differential voltage comparator LM 339 is used to compare
the voltages produced in the circuit. It is a very high precision
comparator, which can even compare to a precision of 1mV and produce
sufficient output.
FIG 2.5: BLOCK DIAGRAM OF SALINE MONITORING UNIT
2.6 PATIENT CALLING SYSTEM:
Patient call switch is used to implement total automation. In case of
assistance required by the patient, they can use the switch to call the
hospital personnel. Four switches are forced to logical high state through
a 1KΩ resistor. When the switch is not pressed, switch contact will be
logical high. The other end of each of the switches is connected to the
ground. So whenever the switch is pressed, port will get a logical low.
Fig 2.6 shows a basic clock diagram of the Patient call switch.
The software is designed in such a way that it will produce a call message
whenever the port receives a low logic circuit. When two or more
10

11. switches are simultaneously pressed all the messages will be displayed
one after the other and will be held as long as the switch is pressed.
A warning alarm is also raised while the switch is pressed. This enables
easy understanding and annunciation.
FIG 2.6: BLOCK DIAGRAM OF PATIENT CALLING SWITCH
2.7 DOCTOR AVAILABILITY MONITORING SYSTEM:
Whenever a critical care is required, there should be a ready reckoner
to see the availability of concerned doctors. Doctor availability
monitoring system does this with the help of 4 infrared emitters, which
can provide 16 different input combinations. The doctors are provided
with unique punch cards each of which corresponds to a particular
combination of binary input to the infrared emitter. Out of these 16
combinations, all zeros and all ones conditions are not taken into
consideration.
11

12. CHAPTER THREE
HARDWARE DESCRIPTION
3.1 DSPIC30F4013
We have used DSPIC30F4013 as the processing integrated circuit in
this project. Some of the features of this processor are as described below:
 High-Performance Modified RISC CPU:
• Modified Harvard architecture
• C compiler optimized instruction set architecture
• Flexible addressing modes
• 84 base instructions
• 24-bit wide instructions, 16-bit wide data path
• Up to 48 Kbytes on-chip Flash program space
• 2 Kbytes of on-chip data RAM
• 1 Kbyte of non-volatile data EEPROM
• 16 x 16-bit working register array
• Up to 30 MIPs operation:
- DC to 40 MHz external clock input
- 4 MHz-10 MHz oscillator input with
PLL active (4x, 8x, 16x)
• Up to 33 interrupt sources:
- 8 user selectable priority levels
- 3 external interrupt sources
- 4 processor traps
12

13.  Peripheral Features:
• High current sink/source I/O pins: 25-mA/25 mA
• Up to five 16-bit timers/counters; optionally pair up
16-bit timers into 32-bit timer modules
• Up to four 16-bit Capture input functions
• Up to four 16-bit Compare/PWM output functions
• Data Converter Interface (DCI) supports common
audio Codec protocols, including I2S and AC’97
• 3-wire SPI™ module (supports 4 Frame modes)
• I2C™ module supports Multi-Master/Slave mode
and 7-bit/10-bit addressing
• Up to two addressable UART modules with FIFO
buffers
• CAN bus module compliant with CAN 2.0B
standard
 Analog Features:
• 12-bit Analog-to-Digital Converter (A/D) with:
- 100 Ksps conversion rate
- Up to 13 input channels
- Conversion available during Sleep and Idle
• Programmable Low Voltage Detection (PLVD)
• Programmable Brown-out Detection and Reset generation
13

14.  Special Microcontroller Features:
• Enhanced Flash program memory:
- 10,000 erase/write cycle (min.) for industrial temperature range,
100K (typical)
• Data EEPROM memory:
- 100,000 erase/write cycle (min.) for industrial temperature range,
1M (typical)
• Self-reprogrammable under software control
• Power-on Reset (POR), Power-up Timer (PWRT) and Oscillator Start-up
Timer (OST)
• Flexible Watchdog Timer (WDT) with on-chip low power RC oscillator or
reliable operation
• Fail-Safe Clock Monitor operation:
- Detects clock failure and switches to on-chip low power RC oscillator
• Programmable code protection
• In-Circuit Serial Programming™ (ICSP™)
• Selectable Power Management modes:
- Sleep, Idle and Alternate Clock modes
 CMOS Technology:
• Low power, high-speed Flash technology
• Wide operating voltage range (2.5V to 5.5V)
• Industrial and Extended temperature ranges
• Low power consumption
14

15.  DSP Features:
• Dual data fetch
• Modulo and Bit-reversed modes
• Two 40-bit wide accumulators with optional saturation logic
• 17-bit x 17-bit single cycle hardware fractional/ integer multiplier
• All DSP instructions are single cycle
- Multiply-Accumulate (MAC) operation
• Single cycle ±16 shift
15

16. FIG 3.1: PIN DIAGRAM dsPIC30F4013
Refer appendix 1 for pin out I/O descriptions.
3.2 INTERFACE WITH PC
In order to display all the parameters fed to the DSPIC effectively, we
interface it with a PC. In order to Interface a PC with the DSPIC, We need a
RS232 interface. Here we have used MAX232 as a serial interface chip.
3.2.1 MAX 232:
The Max 232 is a dual RS-232 receiver / transmitter that meets all
EIA RS232C specifications while using only a +5V power supply. It has 2
onboard charge pump voltage converters which generate +10V and –10V
16

17. power supplies from a single 5V power supply. It has four level translators,
two of which are RS232 transmitters that convert TTL CMOS input levels
into + 9V RS232 outputs. The other two level translators are RS232
receivers that convert RS232 inputs to 5V. Fig 3.2.1 shows pin diagram of
MAX 232.
FIG 3.2.1: PIN DIAGRAM OF MAX 232
TTLCMOS output level: These receivers have a nominal threshold of 1.3V,
a typical hysterisis of 0.5V and can operate upto + 30V input.
 Suitable for all RS232 communications.
 +12V power supplies required.
 Voltage quadrapular for input voltage upto 5.5V (used in power
supply Section of computers, peripherals, and modems).
Three main sections of MAX232 are:
 A dual transmitter
 A dual receiver
17

18.  +5V to + 10V dual charge pump voltage converter.
POWER SUPPLY SECTION:
The MAX232 power supply section has 2 charge pumps the first uses
external capacitors C1 to double the +5V input to +10V with input
impedance of approximately 200Ω. The second charge pump uses external
capacitor to invert +10V to –10V with an overall output impedance of 45Ω.
The best circuit uses 22µF capacitors for C1 and C4 but the value is
not critical. Normally these capacitors are low cost aluminium electrolyte
capacitors or tantalum if size is critical. Increasing the value of C1 and C2 to
47µF will lower the output impedance of +5V to+10V doubler by about 5Ω
and +10V to -10V inverter by about 10Ω. Increasing the value of C3 and C4
lowers the ripple on the power supplies thereby lowering the 16KHz ripple
on the RS232 output. The value of C1 and C4 can be lowered to 1µF in
systems where size is critical at the expense of an additional 20Ω impedance
+10V output and 40Ω additional impedance at –10V input.
3.2.2 WIRELESS TRANSMITTER MODULE TX1-433.92MHz-S
18

19. FIG 3.2.2: WIRELESS TRANSMITTER MODULE
PIN DETAILS:
PIN 1: RF OUT
PIN 2: DATA IN
PIN 3: GROUND
PIN 4: Vcc
FEATURES OF TX1-433.92MHz-S :
 Complete RF Transmitter Module no external components and no
tuning required.
 High Performance SAW Based Architecture with a Maximum Range
of 100 feet at 4800 bps data rate.
 Interface directly to Encoders and Microcontrollers with ease.
 Low Power Consumption suitable for battery operated devices.
Refer appendix 2 for specifications of wireless transmitter module TX1-
433.92MHz-S
19

20. 3.2.3 WIRELESS RECEIVER RX-3304
FIG 3.2.3 RECIEVER RX-3304
PIN 1: GND
PIN 2: Digital Output
PIN 3: Linear Output (For Testing)
PIN 4: VCC (5V DC)
PIN 5: VCC (5V DC)
PIN 6: GND
PIN 7: GND
PIN 8: ANT
Refer appendix 3 for specifications of receiver RX 3304.
20

21. FIG 3.2.4WIRELESS RECEIVER SECTION
21

22. 3.3 POWER SUPPLY UNIT:
Power supply is essential to activate any invention of the latest
technology. All the electronic components starting from diode to Intel IC’s
work with a DC supply ranging from -+5V to -+12V. We have used the
following components:
• 230V-50Hz step down transformer
• rectifier unit – diode -IN4007
• filtering unit -- capacitors
• voltage regulator - IC7812 and IC7912
The circuit diagram is as shown in fig 3.3.
FIG 3.3 : POWER SUPPLY UNIT
Refer appendix 4 for specifications of power supply.
22

23. STEP DOWN TRANSFORMER
When AC is applied to the primary winding of the power transformer,
it can either be stepped down or up depending on the value of DC needed. In
our circuit the transformer of 230v/15-0-15v is used to perform the step
down operation where a 230V AC appears as 15V AC across the secondary
winding. The change in the input causes the top of the transformer to
become positive and the bottom negative. The next alteration will
temporarily cause the reverse. The current rating of the transformer used in
our project is 2A. Apart from stepping down AC voltages, it isolates the
power source from the power supply circuitries.
RECTIFIER UNIT:
In the power supply unit, rectification is normally achieved using a
solid-state diode. Diode has the property that will let the electron flow easily
in one direction at proper biasing condition. As AC is applied to the diode,
electrons only flow when the anode and cathode is negative. Reversing the
polarity of voltage will not permit electron flow. A commonly used circuit
for supplying large amounts of DC power is the bridge rectifier. A bridge
rectifier of four diodes (4*IN4007) are used to achieve full wave
rectification. Two diodes will conduct during the negative cycle and the
other two will conduct during the positive half cycle. The DC voltage
appearing across the output terminals of the bridge rectifier will be less than
90% of the applied rms value. Normally, change in the input voltage will
reverse the polarities. Opposite ends of the transformer will therefore always
23

24. be 180 deg out of phase with each other. During the positive cycle, one of
the two diodes, which are connected to the positive voltage at the top
winding conducts while at the same time the other of the two diodes
conducts for the negative voltage that is applied from the bottom winding
due to the forward bias for that diode. In this circuit due to positive half
cycle D1 & D2 will conduct to give 10.8V pulsating DC. The DC output has
a ripple frequency of 100Hz. Since each altercation produces a resulting
output pulse, frequency = 2*50 Hz. The output obtained is not a pure DC
and therefore filtration has to be done.
FILTERING UNIT:
Filter circuits which are usually capacitors acting as a surge
arrester always follow the rectifier unit. This capacitor is also called as a
decoupling or a bypassing capacitor. It is used not only to ‘short’ the ripple
with frequency of 120Hz to ground but also to leave the frequency of the DC
to appear at the output. A load resistor R1 is connected so that a reference to
the ground is maintained. C1 R1 is for bypassing ripples. C2 R2 is used as a
low pass filter, i.e. it passes only low frequency signals and bypasses high
frequency signals. The load resistor should be 1% to 2.5% of the load.
1000 µf/25V: used for the reduction of ripples from the pulsating
signal.
10 µf/25V: used for maintaining the stability of the voltage at the load
side.
O.1 µf: used for bypassing the high frequency disturbances.
24

25. VOLTAGE REGULATORS:
The voltage regulators play an important role in any power supply
unit. The primary purpose of a regulator is to aid the rectifier and filter
circuit in providing a constant DC voltage to the device. Power supplies
without regulators have an inherent problem of changing DC voltage values
due to variations in the load or due to fluctuations in the AC liner voltage.
With a regulator connected to the DC output, the voltage can be maintained
within a close tolerant region of the desired output. IC7812 and IC7912 are
used in this project for providing +12v and –12v DC supply.
3.4 THERMISTOR:
Thermistor is used for the measurement of body and Respiratory
temperature. It is a passive transducer whose output depends on the
excitation voltage applied to it. Thermistors are thermally sensitive resistors
and have, according to type, a negative (NTC), or positive (PTC)
resistance/temperature coefficient.
The thermistor acts as a potential driver in the circuit. It exhibits a large
change in resistance with a change in the body temperature. Initially the
hardware is calibrated to room temperature. The thermistor part is attached
to the patient whose temperature is to be measured. The change in resistance
caused due to change in temperature is analyzed and the corresponding
temperature change is displayed on the monitor. If the temperature exceeds a
25

26. preset limit, an alarm indicates it. In our project we have used bead type
thermistor.
FIG 3.4 : TEMPERATURE MEASURING CIRCUIT
3.5 SILVER-SILVER CHLORIDE ELECTRODE:
For the measurement of ECG, silver-silver chloride electrode is used.
One of the important desirable characteristics of the electrodes designed to
pick up signals from biological objects is that they should not polarize. This
means that the electrode potential must not vary considerably even when
current is passed through them. Electrodes made of silver- silver chloride
have been found to yield acceptable standards of performance. By properly
preparing and selecting electrodes, pairs have been produced with potential
differences between them of only fractions of a milli volt. Standing voltage
of not more than 0.1mv with a drift over 30 min of about 0.5 mV was
achieved in properly selected silver-silver chloride. Silver-Silver chloride
electrodes are also nontoxic and are preferred over other electrodes like
26

27. Zinc-Zinc Sulphate, which also produce low offset potential characteristics,
but are highly toxic to exposed tissues. Silver-Silver chloride electrodes
meet the demands of medical practice with their highly reproducible
parameters and superior properties with regard to long-term stability.
FIG 3.5: ECG CIRCUIT.
SIGNAL CONDITIONING CIRCUIT FOR ECG:
In order to amplify 20mV from the transducer to 5V, a two stage
instrumentation amplifier is designed with an overall gain of 250.
27

28. Af =A1*A2 = OUTPUT = 5000 = 250
INPUT 20
Assume A2 = 10 , Then A1 = 250 = 25
10
3.6 INFRARED EMITTER AND DETECTOR:
A pair of infrared emitter and detector is used for detection of saline
level. Normally infrared emitters are made up of Gallium Arsenide
material, which produce infrared rays by accepting electric current. It is
quite complex to differentiate the colour of the saline solution from the
bottle colour because both are the same. Only by viewing molecular density
of the materials, they can be differentiated. If rays pass through glass
material the output will be like a beam/ however, if the same rays pass
through a liquid whose viscosity is less than one, the output will be a
spectrum. Infrared detector accepts the infrared rays thereby completing the
circuit.
28

29. FIG 3.6: SALINE MONITORING CIRCUIT
SALINE LEVEL MONITORING:
In the saline monitoring circuit, we use a 220Ω resistor in series with
the 2KΩ potentiometer and connected to the infrared emitter to adjust the
density of rays from the emitter. The current to the emitter is derived by the
following formula.
I = V/R
R = 220 to 2200 Ω
V = 5V (5000 mV)
I = 5000 = 23 mA to 2.3 mA
220 to 2200
Infrared detector accepts infrared rays if more rays falls on it making
the detector act as a conductor. As long as the level of IR rays goes down, it
finds more insulation level. An empty bottle was placed and the voltage
across the detector was found to be approximately 1V. This is because more
rays fall on it as a beam. When a bottle with saline solution was placed, the
spectrum reading was found to be 2V.
EMPTY BOTTLE VOLTAGE = 1V
BOTTLE WITH SALINE = 2V
A differential voltage comparator LM 339 is used. it is a very high
precision comparator which can even compare to a precision of 1mV and
produce sufficient output. The output of the infrared detector is
29

30. connected to the negative input of the comparator and the positive is
connected to the reference potentiometer, which is varied from 0 to 2.5
V. Voltage across reference potentiometer is set as 1.5V.
REF = 1.5V
EMPTY BOTTLE = 1V
Then the O/P is HIGH
BOTTLE WITH SALINE = 2V
REF. = 1.5V
Then the O/P is LOW
By viewing the above data, when saline is present, comparator will
produce a low output and when no saline solution is present, comparator will
produce a high output. The output of the comparator is connected to the
Schmitt trigger in order to avoid low level triggering and spurious noises.
The output of Schmitt trigger is connected to DSPIC. By using software
algorithm, the saline status can be displayed on the screen and alarm is
generated when saline status is empty.
3.7 HEART BEAT MEASURING SENSOR
An Infra Red based sensor is used in the heart rate monitoring. As the
heart pumps blood, the concentration of Red Blood Corpuscles (RBC) in the
finger increases thereby blocking the infrared transmission. When the blood
is sucked in, the finger becomes devoid of blood and a signal is generated.
The transmitter periphery that works at a frequency 20 KHz depends on the
concentration of the RBC and receiver periphery varies according to the
30

31. transmitter pulse, thus resulting in of the number of heartbeats being
counted.
The output of the heart beat sensor is 12 V, which is not suitable for
the DSPIC, which works within the range of 5V.
Hence, a potential divider circuit is included to provide a 4 V input to the
DSPIC.
FIG 3.7: POTENTIAL DIVIDING CIRCUIT FOR HEART BEAT
MEASUREMENT
The conversion formula is given as V*R2 120
= = 4V
R1+R2 30
31

32. Thus 12V is converted into 4V. Whenever the finger is inserted, an output of
waveform is obtained and below 72bpm and above 84bpm, the
alarm will be activated.
32

33. CHAPTER FOUR
FINAL EXPERIMENTAL SETUP
In the last section, we have seen detailed descriptions of the different
hardware that have been used in constructing the complete body scanning
system. In this section, an effort has been made to consider the circuit as a
whole and understand it.
The pin assignment of the DSPIC is described in fig 4.1.
FIG 4.1: PIN ASSIGNMENT FOR DSPIC30F4013
33

34. From fig 4.1 we infer that we have used the following pins of the DSPIC in
our project for the specified purposes:
• Pins 20 and 21to single-phase power supply.
• Pins 1,2,3,4 namely RB0, RB1, RB2 and RB4 are connected to the
output of the doctor identification unit
• Pin 6 namely AN4 is connected to the output of the Heart Beat Rate
monitoring sensor.
• Pins 7 and 8 namely AN5 and AN6 to the outputs of the two
thermistors.
• Pins 9 and 10 namely AN7 and AN8 to the outputs of the ECG
electrodes.
• Pins 13 and 14 namely OSC1/CLKIN and OSC2/CLK0 are connected
to the 10MHz crystal oscillator which provides clock pulse to the
circuit.
• Pin 15 namely RC13 is the latch 13 timer which is connected to the
heart beat sensor.
• Pin 16 namely RC14 is connected to the buzzer alarm.
• Pin 25 namely U1TX is connected to the wireless transmitter TX1-
433.92MHz-S
• Pin 38 namely RB9 is connected to the output of the saline level
detector.
• Pins 19,22,33,34 namely RD3, RD2, RD1 and RD0 are connected to
patient calling switch.
34

35. The various units studied in the previous sections are put together to
assemble the working complete body scanning system which is shown in
fig 4.2.
FIG 4.2: COMPLETE BODY SCANNING SYSTEM: CIRCUIT
DIAGRAM
35

36. CHAPTER FIVE
SOFTWARE IMPLEMENTATION
FIG 5.1: FLOW CHART INDICATING PROCESS FLOW
36

37. 37

38. The process flow diagram shown above depicts the sequence of
occurrence of events in the project. The implementation of this process flow
chart is carried out using hi tech C language. In other words, the
programming of the DSPIC is accomplished using hi tech C language. Refer
appendix 5 for the complete program.
38

39. 5.2: VISUAL BASIC AS FRONT END:
Visual Basic has been used to develop the project. With the visual
Basic programming system, windows - based applications can be developed
with ease rapidly.
Advanced features in Visual Basic such as optimizing native code
compilation, accelerated form rendering, and enhanced database access
allow developers to create fast, high-performance applications and
components. Add to these features the new customizable development
environment with IntelliSense technology, and developers will work with
even greater productivity. Visual Basic also enables us to easily transit into
new technological frontiers such as the Internet without abandoning our
existing code and development skills. One can use both Internet and intranet
technology by creating ActiveX Controls, deploying browser-based Visual
Basic applications as Active Documents, or evolving your client-based
business logic into server-side ActiveX components
39

40. CHAPTER SIX
TESTING AND VERIFICATION
6.1 TESTING PROCEDURE
The complete body scanning system is tested experimentally.
• The wireless receiver kit is interfaced to the computer.
• Supply is given to the transmitter side and receiver end kit
• The Visual basic program is invoked on the computer and is executed.
• The ECG leads are placed on the patient’s arms and leg and the online
graph is studied.
• The thermistor leads are placed on the patient and the body and
respiratory temperatures are made available on the PC.
• The Patient’s finger is placed within the heart beat sensing unit and
the pulse is displayed every minute on the PC
• The working of saline monitoring unit is checked by removing and
replacing the saline bottle. An alarm is set off when the saline bottle is
empty or unavailable, and a display is available on the screen stating
the saline status.
• The working of the patient calling switches is checked by pressing the
switches in turns. An alarm goes off indicating the patient’s demand
for attention, and a display on the screen gives details of the particular
patient.
• The doctor identification system is checked by varying the inputs to
the IR sensors. A photograph And details of the corresponding doctor
is displayed on the screen.
40

41. • In addition to this, an online graph of the body temperature,
respiratory temperature and heart beat rate I also displayed on the
screen.
• Patient data can be added or modified on screen for the purpose of
keeping a record.
• The testing is carried out as many times as desired
• The supply is switched off and the transmitting and receiving kits are
disconnected.
FIG 6.1: ECG RESULTS
41

42. CHAPTER SEVEN
CONCLUSION AND FUTURE PLANS
The temperature sensor used, that is, the thermistor can be replaced by
a better sensor without the disadvantages that the current one has. Instead of
using the traditional temperature sensors, we can also incorporate a CMOS-
compatible integrated pressure and temperature sensor with a PWM output.
This can be connected to an ASIC (application specific integrated circuit)
design for suitable modulation and on-board data storage. Methods to
monitor arterial oxygen saturation also can be incorporated.
42

43. APPENDIX 1
Table A1 provides a brief description of device I/O pinouts and the functions that
may be multiplexed to a port pin. Multiple functions may exist on one port pin.
When multiplexing occurs, the peripheral module’s functional requirements may
force an override of the data direction of the port pin.
TABLE A1 PINOUT I/O DESCRIPTIONS
43

44. TABLE A1 CONTINUED: PINOUT I/O DESCRIPTIONS
44

45. APPENDIX 2
TABLE A2
SPECIFICATIONS OF WIRELESS TRANSMITTER MODULE TX1-
433.92MHz-S
PARAMETER MINIMUM TYPICAL RANGE UNITS
Modulation method ON-OFF KEYED (OOK) Modulation (AM)
Voltage 2.7 3 5.2V DC
Supply Current 5 5.5 mA
Stand by Current 3 micro A
Output power into
50ohms
-2 0 0 dBm
Overall frequency
accuracy
-250 250 KHz
Data input low 0 0.8 Volts
Data input High >0.8 Vcc Volts
Operating temp.
range
0 70 Deg. Cel
Operating
frequencies
433.67 433.92 434.17 MHZ
Max. Data rate 2400 bps
Antenna External1/4 Wave Whip, Helical or PCB Trace
Package SMD
45

46. APPENDIX 3
TABLE A3: SPECIFICATIONS OF WIRELESS RECIEVER
RX 3304.
Model SR
mode
POWER Data
Rate (bps)
SENSITIVIT
Y
DBm
POWER
CONSUMPTION
(mA)
Modulatio
n
Band
Width
RX-3304 SR +5V DC 300~5K - 100 2.70 AM 12MHZ
Notes:
SR: Super-Regenerative; AM: Amplitude Modulation
46

47. APPENDIX 4
SPECIFICATIONS OF POWER SUPPLY
Resistors R1 and R2 maintain line load regulation.
At the secondary side of the transformer,
Applied voltage = 15v
Conducting drop across the diodes = 2*0.6= 1.2v.
Without capacitor:
Vavg = (15-1.2)v = 13.8c pulsating DC
Frequency = 100Hz
With capacitor:
V=Vavg *1.414(form factor) = 19.51v.
Frequency = 0Hz
With 7812 voltage regulator:
V0= +12v
With 7912 voltage regulator:
V0= -12v
47

48. APPENDIX 5
HI TECH C PROGRAM FOR PROGRAMMING OF DSPIC
#include "p30f4013.h"
#include <stdlib.h>
void Delay10ms();
void Delay1sec();
void Delay1();
int ctr,i,j,Hbc,Hbr,Hbval;;
unsigned char Inmsg[] = {"dsPIC30F4013"};
unsigned char PCStr[300],Ostr[6];
short int Eval[35] = {0x05, 0x06, 0x07, 0x06, 0x05, 0x05, 0x03, 0x05, 0x08,
0x0b, 0x0e, 0x0b, 0x08, 0x05, 0x03, 0x01,
0x03, 0x05, 0x05, 0x05, 0x07, 0x09, 0x07, 0x05, 0x06, 0x07, 0x06, 0x05,
0x05, 0x05, 0x05, 0x05, 0x05, 0x05, 0x05};
unsigned char *Txptr;
unsigned int ADCValue,Snd,Ecg1;
short int Strt,cnt;
int main (void)
{
for(ctr =0; ctr <= 20; ctr++)
48

49. {
Delay10ms();
}
ADPCFG = 0xffe0;
TRISA = 0xffff;
TRISB = 0xffff;
TRISC = 0x0000;
TRISD = 0x000f;
TRISF = 0x0000;
LATB = 0xff00;
LATF = 0x0000;
LATC = 0x0000;
IPC0 = 0x0006;
INTCON2bits.INT0EP = 0;
IFS0bits.INT0IF = 0;
IEC0bits.INT0IE = 1;
U1MODE = 0x8000;
U1STA = 0x0000;
U1BRG = 64;
U1STAbits.UTXEN = 1;
Txptr = &Inmsg[0];
49

50. while(*Txptr)
{
if(!U1STAbits.UTXBF)
{
U1TXREG = *Txptr;
Txptr++;
}
}
while(1)
{
strcpy(PCStr,"");
strcat(PCStr,"{");
ADCON1 = 0x00E0;
ADCHS = 0x0002;
ADCSSL = 0;
ADCON3 = 0x1F02;
ADCON2 = 0;
ADCON1bits.ADON = 1;
ADCON1bits.SAMP = 1;
while(!ADCON1bits.DONE);
ADCValue = ADCBUF0;
sprintf(Ostr,"%4d,",ADCValue);
50

51. strcat(PCStr,Ostr);
ADCON1 = 0x00E0;
ADCHS = 0x0003;
ADCSSL = 0;
ADCON3 = 0x1F02;
ADCON2 = 0;
ADCON1bits.ADON = 1;
ADCON1bits.SAMP = 1;
while(!ADCON1bits.DONE);
ADCValue = ADCBUF0;
sprintf(Ostr,"%4d,",ADCValue);
strcat(PCStr,Ostr);
Hbval++;
if(Hbval >= 10)
{
Hbval = 0;
Hbr = Hbc;
Hbc = 0;
}
// sprintf(Ostr,"%4d,",Hbval);
// strcat(PCStr,Ostr);
51

52. sprintf(Ostr,"%4d,",Hbr);
strcat(PCStr,Ostr);
sprintf(Ostr,"%5d,",PORTB);
strcat(PCStr,Ostr);
sprintf(Ostr,"%5d,",PORTD);
strcat(PCStr,Ostr);
ADCON1 = 0x00E0;
ADCHS = 0x0000;
ADCSSL = 0;
ADCON3 = 0x1F02;
ADCON2 = 0;
ADCON1bits.ADON = 1;
ADCON1bits.SAMP = 1;
while(!ADCON1bits.DONE);
ADCValue = ADCBUF0;
if(ADCValue > 50)
{
Snd = 1;
}
else
{
Snd = 0;
52

53. }
cnt = 1;
while(cnt <= 50)
{
cnt++;
Ecg1 = Eval[Strt];
Strt++;
if(Strt > 34) Strt = 0;
if(Snd)
{
sprintf(Ostr,"%4d,",Ecg1);
}
else
{
sprintf(Ostr,"%4d,",0);
}
strcat(PCStr,Ostr);
}
strcat(PCStr,"}");
53

54. if( !PORTDbits.RD0 || !PORTDbits.RD1 || !
PORTDbits.RD2 || !PORTDbits.RD3 || PORTBbits.RB9 )
LATCbits.LATC14 = 1;
else
LATCbits.LATC14 = 0;
for(i = 1; i <= 5; i++)
{
while(U1STAbits.UTXBF) continue;
U1TXREG = 0xaa;
Txptr = &PCStr[0];
while(*Txptr)
{
if(!U1STAbits.UTXBF)
{
U1TXREG = *Txptr;
Txptr++;
}
}
}
}
return 0;
}
54

55. void Delay10ms()
{
int i;
for(i = 0; i < 800; i++) // 1000
{
asm("NOP");
}
}
void Delay1()
{
int i;
for(i = 0; i < 2; i++)
{
asm("NOP");
}
}
void Delay1sec()
{
int i;
for(i = 0; i < 100; i++)
{
Delay10ms();
}
55

56. }
/* Interrupt Service Routine 3: INT0Interrupt */
/* Save and restore variables var1, var2, etc. */
void __attribute__((__interrupt__)) _INT0Interrupt(void)
{
/* Interrupt Service Routine code goes here */
if(IFS0bits.INT0IF)
{
IFS0bits.INT0IF = 0;
Hbc++;
LATCbits.LATC13 = !LATCbits.LATC13;
}
}
56

57. BIBLIOGRAPHY
1. Handbook of Bio-Medical Instrumentation - R.S.Khandpur
2. Bio-Medical Instrumentation - Dr. M. Arumugam
3. Principles of Internal Medicines (VOL I) - Wilson Brawnwall
- Isselbacher
- Peterstrorf
4. Bio-Medical Instrumentation
and measurements - Leslie Cromwell
- Fred. J. Wejnbell
- Erich . A. Pleiffer
5. Linear Integrated Circuits - Roy Chowdary
6. National Semi Conductor TTL Data Manual
7. IBM PC Handbook - IBM Corporation
8. IBM PC Techinical References Guide
57

58. 9. Linear Data book by Texas corporation
58