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U N I V E R S I TAT I S O U L U E N S I S
ACTAC
TECHNICA
U N I V E R S I TAT I S O U L U E N S I S
ACTAC
TECHNICA
OULU 2010
C 373
Young-Dong Lee
WIRELESS VITAL SIGNS
MONITORING SYSTEM FOR
UBIQUITOUS HEALTHCARE
WITH PRACTICAL TESTS ANDRELIABILITY ANALYSIS
UNIVERSITY OF OULU,
FACULTY OF TECHNOLOGY,
DEPARTMENT OF ELECTRICAL AND INFORMATION ENGINEERING
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A CTA UNIVE RS ITA T I S O UL
C Techn i c a 37 3
YOUNG-DONG LEE
WIRELESS VITAL SIGNS
MONITORING SYSTEM FOR
UBIQUITOUS HEALTHCARE
WITH PRACTICAL TESTS AN
RELIABILITY ANALYSIS
Academic dissertation to be presented with
the Faculty of Technology of the Universitypublic defence in Auditorium TS101, Linna
December 2010, at 12 noon
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Copyright 2010
Acta Univ. Oul. C 373, 2010
Supervised byDocent Esko Alasaarela
Professor Risto Myllyl
Reviewed by
Professor Mohammed ElmusratiProfessor Jukka Vanhala
ISBN 978-951-42-6387-3 (Paperback)ISBN 978-951-42-6388-0 (PDF)
http://herkules.oulu.fi/isbn9789514263880/ISSN 0355-3213 (Printed)
ISSN 1796-2226 (Online)http://herkules.oulu.fi/issn03553213/
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Lee, Young-Dong, Wireless vital signs monitoring system for ubiquitou
with practical tests and reliability analysisUniversity of Oulu, Faculty of Technology, Department of Electrical and Engineering, P.O.Box 4500, FI-90014 University of Oulu, Finland
Acta Univ. Oul. C 373, 2010
Oulu, Finland
Abstract
The main objective of this thesis project is to implement a wireless vital signs mon
for measuring the ECG of a patient in the home environment. The research focuses o
research objectives: 1) the development of a distributed healthcare system fo
monitoring using wireless sensor network devices and 2) a practical test and
evaluation for the reliability for such low-rate wireless technology in ubiquitous hea
applications.
The first section of the thesis describes the design and implementation of
healthcare system constructed from tiny components for the home healthcare of el
The system comprises a smart shirt with ECG electrodes and acceleration senso
sensor network node, a base station and a server computer for the continuous monit
signals. ECG data is a commonly used vital sign in clinical and trauma care. The
displayed on a graphical user interface (GUI) by transferring it to a PDA or a term
smart shirt is a wearable T-shirt designed to collect ECG and acceleration signals fr
body in the course of daily life.
In the second section, a performance evaluation of the reliability of IEEE 802
wireless ubiquitous health monitoring is presented. Three scenarios of performan
applied through practical tests: 1) the effects of the distance between sensor no
station, 2) the deployment of the number of sensor nodes in a network and 3) data
using different time intervals. These factors were measured to analyse the reli
developed technology in low-rate wireless ubiquitous health monitoring application
The results showed how the relationship between the bit-error-rate (BER) and s
ratio (SNR) was affected when varying the distance between sensor node and base-st
the deployment of the number of sensor nodes in a network and through data trans
different time intervals.
Keywords: BER, ECG, IEEE 802.15.4, acceleration signal, personal are
reliability analysis, vital signs monitoring
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Acknowledgements
I wish to express my warm and sincere thanks to the University o
Dongseo University for giving me the opportunity and resources t
thesis through their excellent dual-degree program. This work wou
been possible without support from the dual-degree program b
University of Oulu and Dongseo University.
I would also like to express my deep and sincere gratitude to myProfessor Esko Alasaarela, for his understanding, encouragement a
throughout the work of this thesis. His wide knowledge and techni
have been of great value to me.
I am, as well, deeply grateful to my second supervisor, Pro
Myllyl, Head of the Optoelectronics and Measurement Techniques
for his important support throughout this work.
Furthermore, I wish to express my sincere thanks to Professor H
who gave me important guidance and untiring help during my difficul
Additionally, during this work I have collaborated with many co
whom I have great regard, and I wish to extend my warmest thanks
who have helped me with my work in the Optoelectronics and M
Techniques laboratory at the University of Oulu, and the USN l
Dongseo University, Korea.
Finally, I would like to convey my loving thanks to my wife Mi
my son Hyeong-Gyu, for their encouragement and understanding.
Oulu, March 2010 Youn
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List of terms, symbols and abbreviations
A/D Analog/Digital
ACK Acknowledgement
ADC Analog-to-Digital Converter
AWGN Additive White Gaussian Noise
BAN Body Area Network
BASN Body Area Sensor NetworkBER Bit Error Rate
BMAC Berkeley MAC
BSN Body Sensor Network
CCITT International Telegraph and Telephone Consultative Com
CRC Cyclic Redundancy Check
CTS Clear to Send
dB Decibels
dBm Decibels per Milliwatt
DMAC Distributed MAC
DSDV Destination Sequence Distance Vector
DSMAC Differential Service MAC
Eb/No Energy per Bit to Noise power spectral density ratio
ECG Electrocardiogram
EMT Emergency Medical Technician
g Gravitational constant
GHz Giga Hertz
GPRS General Packet Radio Service
GUI Graphic User Interface
HPF High Pass FilterI/O Input/Output
ID Identification
ISM Industrial Scientific Medical
ISP In System Programmer
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MB Mega Byte
MHz Mega Hertzmm Millimeter
NACK Negative Acknowledgement
nesC Network Embedded System C
O-QPSK Offset Quadrature Phase-Shift Keying
PCB Printed Circuit Board
PDA Personal Digital AssistantPER Packet Error Rate
PHY Physical Layer
PSK Phase-Shift Keying
QoS Quality of Service
RAM Random Access Memory
RF Radio Frequency
RS-232 Recommended Standard 232
RTS Request to Send
Rx Receiver
SMAC Sensor MAC
SNR Signal-to-Noise Ratio
SPI Serial Peripheral Interface Bus
SpO2 Oxygen Saturation
TCP/IP Transmission Control Protocol/Internet Protocol
TinyOS Tiny Micro Threading Operating System
TMAC Timeout MAC
Tx Transmitter
uA Micro-Ampere
UART Universal Asynchronous Receiver/TransmitterUbiMon Ubiquitous Monitoring Environment for Wearab
Sensors
UMTS Universal Mobile Telecommunication System
USB Universal Serial Bus
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List of original papers
I Lee Y-D, Lee D-S, Chung W-Y & Myllyl R (2006) A wireless se
platform for elderly persons at home. Rare metal materials and engin
9599.
II Amit P, Lee Y-D & Chung W-Y (2008) Triaxial MEMS acceleromet
monitoring of elderly person. Sensor Letters 6(6): 10541058.
III Lee Y-D & Chung W-Y (2009) Wireless sensor network based wearab
for ubiquitous health and activity monitoring. Sensors and Actuators140(2): 390395.
IV Walia G, Lee Y-D, Chung W-Y & Myllyl R (2006) Distribut
monitoring in an ad-hoc network using a wireless sensor network. P
11th International Meeting on Chemical Sensors, Brescia, Italy.
V Lee Y-D, Lee D-S, Walia G, Myllyl R & Chung W-Y (2006) Query
vital signal monitoring system using wireless sensor network fo
healthcare. Proceedings of World Congress on Medical Physics an
Engineering, Seoul, Korea: 396399.
VI Lee Y-D, Lee D-S, Walia G, Alasaarela E & Chung W-Y (2007
evaluation of query supported healthcare information system using w
ad-hoc network. Proceedings of International Conference on
Information Technology, Gyeongju, Korea: 9971002.
VII Lee Y-D, Alasaarela E & Chung W-Y (2007) A wireless health monito
multi-hop body sensor networks. Proceedings of 2nd International S
Medical Information and Communication Technology (ISMICT'07), OVIII Chung W-Y, Lee Y-D & Jung S-J (2008) A wireless sensor netwo
wearable u-healthcare monitoring system using integrated ECG, acce
SpO2. Proceedings of 30th Annual International Conference o
Engineering in Medicine and Biology Society (EMBC 2008), Vancou
15291532.
The objective of paper I was to design and implement a small size
healthcare system for the home care of elderly persons. The system
wireless sensor network node, base station and server computer for th
monitoring of ECG signals. ECG data, important vital heart sign
commonly used in clinical and trauma care, were displayed on a gr
i f (GUI) b f i h d PDA i l PC
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Wearable sensor devices are proposed in paper III that are
into a shirt, which are of small size, low power consumption awireless sensor network communication based on IEEE
mainly consists of sensors for continuous monitoring o
conductive fabrics to get the body signal, functioning as electr
Paper IV describes the development of a distributed healt
prototype for clinical and trauma patients using a commercial
sensor network platform. The system has been designed to msigns of the patients and transfer the health status wirelessl
station which was connected to a doctors PDA and terminal P
Paper V discusses the design issue for a query driven he
its implementation using a wireless sensor node in an ad-hoc
describes the system's architecture, including hardware desig
experimental setup, and results and performance analysis are
Papers VI and VII present a wireless health monitoring
body sensor networks using our ubiquitous sensor networ
based 3-electrodes ECG monitoring system operates in wirel
The ECG signal from multiple patients was relayed wireless
routing scheme to a base-station. The design and developm
Healthcare monitoring system using integrated ECG, accele
saturation sensors is introduced in paper VIII.
The author defined the research plan and carried out the l
wrote a manuscript presented in papers I-VIII. Experiment
were done by the author in association with the co-authors.
papers I, III-VIII, was written by the author with the kind he
The authors contribution to paper II was to design and
accelerometer sensor system using wireless sensor nodes. Thout the accelerometer sensor measurements together with Am
the first version of the manuscript, after discussions with the c
to the reviewers comments, the author wrote the revision of t
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Contents
Abstract
Acknowledgements
List of terms, symbols and abbreviations
List of original papers
Contents
1 Introduction 1.1 Related works ...........................................................................1.2 Objectives and outline of the thesis ........................................
2 Healthcare system requirements 2.1 Node lifetime ...........................................................................2.2 Packet recovery .......................................................................2.3 Data collection ........................................................................2.4 Dependent and independent waveforms .................................2.5 Scalability ................................................................................
3 Vital signs monitoring system 3.1 System architecture of a general u-Healthcare system ............3.2 MICAz node and ECG interface circuit ...................................3.3 USN platform for wireless sensor networking ........................3.4 Sensor boards for vital signs monitoring.................................
3.4.1 Single ECG interface circuit for MICAz node .............3.4.2 ECG & accelerometer sensor board ..............................3.4.3 Wearable sensor node with sensor board ......................
3.5 Sensor node software ..............................................................3.5.1 Sampling time for the ECG signal ................................3.5.2 Packet format ................................................................3.5.3 Routing protocol ............................................................
4 Reliable medical data transmission 4.1 Need for reliable medical data transmission ...........................4.2 Low-rate wireless personal area networks ..............................
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5.5 Reliability analysis .....................................................5.5.1 Reliability test in function of distance between
nodes ................................................................
5.5.2 Reliability test in the function of the number onodes ................................................................
5.5.3 Reliability test for different time intervals .......6 Discussion
6.1
Multi-hop network for wireless body area network ...6.2 Electrocardiogram and accelerometer sensor .............6.3 Wearable system for ubiquitous healthcare ................
7 Conclusion References
Original Papers
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1 Introduction
An increasingly aging population has raised the concern of many cou
its impact on health care systems. This has led to an urgent need
cheaper and smarter ways to provide health care for suffers of age rel
Recent advances in sensor, communication and information techno
enabled the development of novel vital signs monitoring system
various vital health parameters can be measured, like electrocardiog
body temperature, heart rate, blood pressure and oxygen saturation.
wireless healthcare related applications using wireless sensor network
assist residents and caregivers by providing non-invasive and invasiv
health monitoring with a minimum interaction of doctors and patient
there are some significant disparities, such as node lifetime, packet r
medical data collection between existing wireless sensor network
required for healthcare [5, 6]. In addition to the basic requiremen
wireless, a future healthcare system based on wireless sensor network
support for ad-hoc [7] networks, the mobility of patients or elderly p
ranges of data rates and a high degree of reliability. Also, these system
miniature in size, and should be easily wearable, thus causin
inconvenience to the patients.
The design of a sensor network is application-specific, aapplications have different reliability [8] requirements. Re
communication is an important factor for the dependability and quali
(QoS) [911] in several applications of wireless sensor networks. I
this is the case for critical care applications of hospitals that allow the
monitoring of a patients vital signs. We must consider the reliabi
sensors, the sampling rate, the number of nodes in the same netwopacket sizes, as well as the reliability of the medical devices themse
closely related to the performance of the system in medical applicatio
1 1 Related works
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continuously monitored and receive advice when needed
patient/user is equipped with different vital constant sensors,pulse rate and ECG, interconnected via the healthcare BAN. T
is the central point of healthcare BAN, acting as a gateway
sensor measurements (intra-BAN communication based on
like Bluetooth [18] and Zigbee [19]) and transmitting the
system (extra-BAN communication based on GPRS and UM
located within the health broker premises or be part of a wirelFrom there, the measurements are dispatched to the healthca
medical personnel monitor them.
The ubiquitous monitoring environment for wearable and
project (UbiMon) [20] at Imperial College London aims to p
and unobtrusive monitoring system for patients in order to c
life threatening events. The basic framework of the UbiMon
sensor network (BSN) design. The system consists of five
namely the BSN nodes, the local processing unit, the centra
database and the workstation. With the current UbiMon str
wireless biosensors including 3-leads ECG, 2-leads ECG
saturation (SpO2) sensors have been developed. To facilitate
context information, sensor-based context awareness, includ
temperature and skin conductance sensors are also integrated
Furthermore, a compact flash BSN card is developed
assistants (PDAs), where sensor signals can be gathered, dis
by the PDA.
CodeBlue [21] has been designed to operate across a wi
including low power motes, PDAs and PCs, and addresses th
and security requirements of medical care settings. The dMICA2 [22] mote with a pulse oximetry signal processing
transmits periodic packets containing heart rate, SpO2 and p
waveform data. Vital sign data from multiple patients can
adaptive, multi-hop routing scheme either to a wired base-sta
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1.2 Objectives and outline of the thesis
The main objective of this thesis project is to implement a wireles
monitoring system for measuring the ECG of a patient in the home e
The research focuses on two specific research objectives: 1) devel
distributed healthcare system for vital signs monitoring using wir
network devices and 2) a practical test and performance evalua
reliability for such low-rate wireless technology in ubiquitous health
applications.
The content of this thesis is summarized as follows:
Chapter 2 addresses the requirements for a ubiquitous healthcare
main requirements for wireless healthcare such as node lifetime, pack
data collection, waveform and scalability are presented.
Chapter 3 presents the design and implementation of a ubiquitou
system that applies small-size components for the home care of elde
Two kinds of health monitoring systems have been developed; a
interface circuit for a MICAz [23] node and multiple sensors
accelerometer sensor systems. In addition to this, a wearable
healthcare system for vital signs monitoring is presented.
Chapter 4 discusses reliable medical data transmission for im
quality-of-service, including the need for reliable medical data transmrate wireless personal area networks (LR-WPAN) and error rate
reliability.
Chapter 5 presents the experimental results with a focus on
monitoring and performance evaluation.
Chapter 6 provides a summary of this work.
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2 Healthcare system requirements
Wireless healthcare should satisfy the main requirements such as no
packet recovery, data collection, waveform and scalability.
2.1 Node lifetime
The lifetime of a wireless sensor network is application-specific. With
healthcare application, it is necessary to monitor a patient
continuously (keep the wakeup sensor active) because
(electrocardiogram and heart rate) can occur at any time. An impor
wireless sensor networks for continuous healthcare application is to m
node lifetime while maintaining application or other constraints, su
and reliability [24, 25]. In order to maximize node lifetime for
healthcare application, power saving techniques should be conside
avoiding unnecessary packet recovery, efficient data collection a
packet losses.
2.2 Packet recovery
In continuous healthcare application, it is not necessary to use a pacmechanism because of packet loss, as it wastes resources. Any lost pa
replaced by the most recent update in the next transmission. Also, re
of packets will require more storage memory at the motes, which
limited. Since this is a healthcare scenario, where each node attached
transfers data independently of other nodes in the network, protocols
[26], TMAC [27] and DSMAC [28], which need RTS/CTS packet exlost packet recovery and have synchronized sleep and wake periods, a
SIFT [29] is a MAC protocol for event-driven wireless sens
environments. Although SIFT [29] achieves low latency at the c
increase in energy consumption, it needs a system-wide synchroni
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2.3 Data collection
While designing wireless sensor networks, the choice of a M
also depends on the application requirements, topology use
routing protocol. A healthcare system generally requires a sin
station, therefore a convergent type communication patter
choice, where data from the entire sensor network is finally
base-station. For convergent type communication, the DMA
good choice as it achieves very good latency compared
periods. Although DMAC does not avoid collision detection
collision are reduced by the fact that in healthcare environm
trigger all nodes simultaneously. The BMAC [31] protoc
possible choice, as it avoids packet collision and has a
scheme via low power listening, but unlike SMAC, it does no
retransmission or hidden terminal avoidance using RTS/CTS
best thing about BMAC is that it offers control to the protoco
the routing and application layers to change control paramet
communication is highly demanded in the designing
applications, where often each communication layer not on
with the intermediate layer, but also with the other layers dire
2.4 Dependent and independent waveforms
Healthcare data which is waveform independent does not n
transfer, and therefore data transfer should be initiated only
monitoring side, or in periods of finite durations. On the ot
dependent data requires long-term medical data transfer in co
application. Therefore, for waveform dependent data, data
would be well suited where a query or command from the
the data transfer. The waveform independent data can use ei
approach or the event-driven approach where data is transfe
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missed they can be replaced. For waveform dependent data, any pac
be a big problem as it will result in a loss of useful information or cafalse impression of abnormality about a patients health parameter.
2.5 Scalability
Another important issue is that the routing of message packets from o
nodes is more challenging, since stability becomes an important factor, in addition to energy and bandwidth etc. Since fast data delive
requirement in healthcare, proactive routing protocols will be efficien
this case, the path to be chosen is known in advance, before data t
Also, any change in topology is updated by timely updates. Am
proactive protocols, a DSDV [33] based protocol would b
implementation and supports a flat network. The key advantage of D
it guarantees loop freedom.
In a healthcare network, as data generated from different sensor
different rates, subject to different quality of service constraints and
multiple data delivery model, traditional methods of data aggregatio
applied. Scalability is also major issue because single gateway archit
scalable for a large set of sensors [34].
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3 Vital signs monitoring system
3.1 System architecture of a general u-Healthcare system
Ubiquitous healthcare is built around the concept of placing unobtru
on a persons body to form a wirelessly connected network. Persona
networks [3537] make it possible to continually monitor pati
anywhere and immediately notify clinicians, the nearest hospital or anservice of any critical change in status. Such networks can quic
biomedical data from sensors deployed on the body to a server c
processing.
Fig. 1 illustrates the system architecture of a general ubiquitou
system for monitoring patient status. The system consists of
components, namely, a body area sensor network (BASN) node, loca
unit and central server.
Fig. 1. System architecture of ubiquitous healthcare system for vital sign
[I, published by permission of Rare Metal Materials and Engineering].
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receiving data from the wireless sensor node using an RF
storing and transferring the data to a mobile unit using TCPAn example of ubiquitous healthcare is provided by the ub
environment for wearable and implantable sensors (UbiM
Imperial College, London, UK. This project aims to provid
unobtrusive monitoring system for patient care in order to c
life threatening events. To this end, a compact flash BSN card
for PDAs, allowing sensor signals to be gathered, displayed
PDA. Apart from acting as the local processor, the PDA c
router between the BSN node and a central server to which
data will be transmitted through a WiFi/GPRS network for lo
trend analysis. Monitoring terminals are utilized to allow c
patient data using such portable handheld devices as laptop
phones. In addition to real-time sensor information, histori
retrieved and played back to assist the diagnosis. [Paper I]
3.2 MICAz node and ECG interface circuit
Fig. 2 shows the system architecture of the wireless senso
discussed in this thesis, consisting of four major parts:
acquisition board, ECG interface circuit and base-station. Astudy used the commercially available MICAz (Crossbow
USA). The MICAz has a Chipcon CC2420 radio chip set op
802.15.4 standard (Zigbee compatible), an Atmega 128L mi
Corporation, USA) with a data throughput of 250 kbps. T
board has a maximum of 11 input channels, each with its ow
digital converter (ADC).
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Fig. 2. Hardware configuration of the wireless sensor network [I, p
permission of Rare Metal Materials and Engineering].
One of most commonly monitored vital signs in clinical and trauma c
signals. A two- or three-electrode ECG is used to evaluate cardiac ac
extended period. Physicians, clinicians or the patients themselve
continuously watch for signs of deterioration in the patients cond
cardiac problems such as arrhythmia that occur intermittently, maybe
twice a day. In this thesis, an ECG signal generator was used to accurate ECG signal for our preliminary experiment. In the
experiments, the ECG signal was obtained from sensors attached to a
body.
After processing in an interface circuit, signals produced by the
generator were recorded by the MICAz wireless sensor node. MICAz
custom operating system called TinyOS [38], which supports mult
allowing the performance of a variety of tasks tailored specifically
sensor network applications. Each node is capable of sending an
specific wireless network packets called active messages. A similar M
was used as the base-station with an MIB510 serial PC interface
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Fig. 3. Block diagram of a MICAz sensor node [I, published by
Metal Materials and Engineering].
3.3 USN platform for wireless sensor networking
Fig. 4 shows a block diagram of the USN platform develope
The specifications of the USN platform are summarized in Ta
The USN platform features an ultra low power Texas I
micro-controller [39] with 10KB RAM, 48KB flash mem
converter. It supports several low power operating modes and
5.1uA in sleep mode and 1.8mA in active mode. The CC2420
[40] is IEEE 802.15.4 Zigbee compliant and has programma
maximum data rate of 250 kbps and hardware that provides P
layer functions. The CC2420 is controlled by the MSP430F
port and a series of digital I/O lines. The M25P80 is an 8 MB
with a write protection mechanism, accessible from a SPI b
size of the USN platform, the USB programming board was
module which is needed only when nodes are connected t
li i d l d h h d b i
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Fig. 4. Block diagram of the USN platform.
Recent research has focused on the development of wireless sensor n
pervasive monitoring systems that can monitor the status of a patient
temperature, blood pressure, SpO2, accelerometer, etc.) for ubiquitouapplications. Therefore, a low power operating ECG sensor board wa
for patient health monitoring, and the output of the ECG sensor
connected to a USN platform.
Table 1. Specifications of USN platform.
Item Specification Remark
Platform
Processor MSP430F1611
Memory 48 KB/10 KB Program flash/data RAM
Current draw 1.8 mA/5.1 uA Active/sleep mode
ADC 12 bit resolution 8 channels
Power 3V Battery
Connector Expansion/USB type
RF transceiver
Frequency band 2.42.485 GHz
Sensitivity 95 dBm
Transfer rate 250 Kbps
RF power 25 dBm 0 dBm
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3.4 Sensor boards for vital signs monitoring
3.4.1 Single ECG interface circuit for MICAz node
An ECG signal generator with an interface circuit was atta
node for the purpose of continuously supplying ECG signa
produced by an ECG sensor on a patients body.
Fig. 5 shows a block diagram of the ECG interface circui
circuit is required for the amplification of the output signal p
signal generator, signal conditioning and analog to digital con
Fig. 5. Block diagram of an ECG interface circuit [I, published b
Metal Materials and Engineering].
3.4.2 ECG & accelerometer sensor board
Fig. 6 illustrates the block diagram of the sensor board which
interface and a three-axis accelerometer sensor [Paper II] c
bioelectric signal which records the hearts electrical ac
therefore it is a very important and basic diagnostic tool
functions. An electrocardiogram is obtained by measuring
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from at least two leads are generally used in order to g
electrocardiogram representation of the cardiac electrical activiimportant part of home healthcare is to monitor behaviour and physic
daily life. There are many exisitng research studies [4143] to
detection systems using a 3-axis accelerometer. The system can
accelerometer signals to determine whether the person with the dev
has fallen or not.
ECG signals from the electrodes are amplified with a gain of 30
and filtered with the cut-off frequencies of 0.05 Hz and 123 Hz in
board. An ECG electrode has two conductive fabric electrodes (Polar
Finland) which are woven into the fabric. In addition, the sensor boa
three-axis accelerometer sensor (MMA7260Q, Freescale) [Paper II]
acceleration signals for the activity monitoring of a patient. The shap
board with a wireless sensor node is designed with a contoure
comfortable wear and convenience. [Paper III]
Fig. 6. Block diagram of a sensor board [III, published by permission of E
Table 2. Sensor board specification.
Specifications
ECG sensor specification
ECG type Chest-belt type
Gain 300 (24.8)dB
Bandwidth 0 05 123 Hz
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3.4.3 Wearable sensor node with sensor board
Fig. 7 shows the overall system architecture of the wear
ubiquitous health and activity monitoring, which consis
integrated wireless sensor nodes, a base-station and ser
monitoring. The wireless sensor network consists of a larg
nodes, which have built-in computing, power, sensors to a
and activity data from the human body and wireless transm
capability. The smart shirt is compatible with the wireless s
the individual physiological data from each smart shirt is tr
wireless communication for further processing using a wireles
The wearable sensor nodes are responsible for acquirin
data and transmitting it to the base-station. The sensor node
tiny in size and consume low operating power to reduce bat
also last for longer durations. The sensor node has a limited bas computing and communication capability, due to its physic
Fig. 7. System architecture of the u-Healthcare system with we
published by permission of Elsevier].
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shows the architecture of the designed wireless sensor node. The wi
node is round in shape and 40 mm in diameter.
(a)
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The smart shirt consists of a wireless sensor node, an EC
sensor board and conductive fabric electrodes for ECG measshirt design. To reduce the size of the integrated wearab
structure is made up of two round shaped PCB boards whic
wireless sensor node plate for communication in a wireless s
sensor board plate with an ECG interface & accelerometer.
node and sensor board are combined together as shown in
sensor node is placed in the top position and the sensor board
and accelerometer circuits is placed in the bottom position of
node structure. To obtain physiological ECG data, two
electrodes are extended from the ECG interface circuit of the
knitted into the shirt. The smart shirt is a wearable T-shirt
ECG and acceleration signals from the human body contin
The shirt contains ECG and accelerometer sensors that can
vital signs such as heart rate, ECG and acceleration. The doub
the wearable sensor node reduces the width of the normal s
sensor node structure with sensors and gives convenience in
size batteries. [Paper III]
Fig. 9. An integrated wearable sensor node combined with a wire
a sensor board in double layer structure.
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platform is implemented based on TinyOS [38]. TinyOS is a small,
embedded operating system developed by UC Berkeley. A stand-alconstrained operating system, TinyOS is application specific an
selected system components and custom components needed f
application. In the TinyOS operating system, libraries and application
in nesC [40], which is a structured component-based language. NesC
syntax, but supports the TinyOS concurrency model, as well as mec
structuring, naming and linking together software components
network embedded systems. TinyOS defines a number of important c
are expressed in nesC: (1) nesC applications are built out of comp
well-defined, bidirectional interfaces, (2) nesC defines a concurr
based on tasks and hardware event handlers and detects data-race
time. Races are avoided either by accessing a shared state only in ta
within atomic statements.
The component based architecture and event driven executio
TinyOS enables fine-grained power management while minimizin
keeping in view the memory constraints in wireless sensor net
architecture for software is based on the Active Message communic
The Healthcare application consists of several components like uHea
GenericComm and Routing. These components have specific fu
services that they provide/use to/from other connected componentstechniques of these have been developed, and some of the compone
shown in Fig. 10. [Paper IV, Paper V]
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The main application level component is uHealth which contro
handling of various hardware and software events. The composamples the ECG signal from the ECG sensor board. GenericCom
generic packet handling and a basic SendMsg and ReceiveMsg in
TinyOS messages. GenericComm will also interface to low lev
specific TinyOS hardware drivers. The Routing component p
function of routing data and topology updates to the application. [Pap
VII]
3.5.1 Sampling time for the ECG signal
The default value of the TIME_SCALE (local clocks of nodes) i
resolution of 100, indicating a 0.1 second sampling time in TinyOS. I
TIME_SCALE could be modified to 10, corresponding to a sampling
s. Thus, the ECG signal produced by the ECG signal generator passed
signal interface circuit and entered the MICAz. The analog ECG
collected at a sampling rate of 125Hz and converted into a digital sig
data. [Paper I]
3.5.2 Packet format
Digitized ECG data can be transmitted to other sensor nodes or the
connected to the server PC by an RS-232 serial interface in the IEE
(Zigbee compatible) standard format. The overall packet struct
developed system is composed of 36 bytes, as shown in Table 3. S
structure of tinyos message structure (TOS_MSG), the header part of
is comprised of a destination address, an active message handler, a gmessage length. This is followed by a data part of 29 bytes, which is c
7 bytes of multi-hop message attributes and data of 22 bytes. A 1 b
was included for indication of types of sensors. The sensor reading
and the rest are for internal management. The header and data part is
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Table 3. Packet structure for communication between sensor n
permission of Rare Metal Materials and Engineering].
Header Data Part Payload Data
Destination
address
Active
Message
handler
Group ID Message
Length
Mote ID Counter
2Bytes 1Byte 1Byte 1Byte 2Bytes 2Bytes
3.5.3 Routing protocol
For constructing our ad-hoc network, a variant of the De
Distance Vector (DSDV) algorithm [33] has been used
destination of data from all nodes is a single base statio
periodically broadcasts its identity, which is used by receivin
its routing information table. They then rebroadcast the new rnodes in their range. Thus, a hierarchy of nodes is formed wi
the top level, and all nodes target their data to the nodes w
them. Any change in topology is conveyed to the parent node
their tables.
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4 Reliable medical data transmission
4.1 Need for reliable medical data transmission
Quality of service is an important part of healthcare application. A c
is reliable medical data transmission, by which medical informa
monitored correctly by healthcare professionals. In a reliable m
transmission system, the receiver side BER may be affected by
channel noise, interference, distortion, attenuation, wireless multipath
A healthcare application has a dynamic duty cycle compared to
environmental monitoring applications. For example, environmenta
applications need a low duty cycle to collect environmental par
temperature, humidity etc. These applications have lower
requirements than the high duty cycle applications (healthcare appli
many applications, a fundamental problem is providing efficient and
transmission. In wireless sensor networks, the data transmission is un
to several factors such as [45]:
The wireless links can be unreliable, which leads to packet losses
The network congestions lead to packet losses as packets are
intermediate/routing nodes in the routing paths.
Interference, attenuation and fading are the main factors in un
transmission
Channel bit errors during wireless data transmissions.
In particular, ubiquitous health monitoring applications are related to
So, health management, precise measurement and reliable data
methods should be analysed before the designing of healthcare
applications. So far, a few research studies have been proposed
reliable data transmission using positive acknowledgement (ACK) a
acknowledgement (NACK) methods. The data retransmission app
most commonly used method for recovering packet error and losses. A
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4.2 Low-rate wireless personal area networks
Wireless technology for medical applications like IEEE 80
was used in this study The IEEE 802.15.4 standard was dev
demand for low power and low-cost in low-rate wireless per
(LR-WPAN). IEEE 802.15.4 deals with a low data rate, b
battery life (months or even years) and a very low complexity
802.15.4, defines the physical layer (PHY) and medium ac
sub-layer specifications for low-rate wireless personal ar802.15.4 defines two PHY layers; in the 2.4 GHz and 868/9
license free industrial scientific medical (ISM) 2.4 GHz
worldwide, while the ISM 868 MHz and 915 MHz bands are
and North America respectively. A total of 27 channels with
the-air data rates are allocated in 802.15.4: 16 channels wit
kbps in the 2.4 GHz band, 10 channels with a data rate of 40 band, and 1 channel with a data rate of 20 kb/s in the 868 MH
4.3 Error rate analysis for reliability
The bit error rate (BER) is the number of received binary
altered due to noise and interference, divided by the total nu
bits during a studied time interval. The BER can be considere
estimate of the bit error probability (bP ).
The packet error rate (PER) is the number of incorrectly tran
divided by the number of transferred packets. A packet is assu
if at least one bit is incorrect. Denote that the packet error p
expectation value of PER, which can be expressed for a data
bits as
1 (1 )Np bP P= .
The BER is often expressed as a function of the normalized
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0
2 be
EP Q
N
=
,
where ( )Q is the error function, bE is energy per bit, and 0N is the
spectral density ratio. The SNR as a function of transmission
expressed as
0
bE R
SNR
N B
= ,
where R is the channel data rate, and B is the channel bandwidth.
Fig. 11 shows the theoretical bit error rates of O-QPSK, 8-PSK a
The curves present that O-QPSK is better than 8-PSK and 16-PSK. I
higher-order modulations exhibit higher error-rates in exchange an
they deliver a higher raw data-rate.
10-7
10-6
10-5
10-4
10-3
10-2
10-1
100
BER
O-QPSK
8-PSK
16-PSK
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5 Results
5.1 Experimental setup and ECG signal measurement
In our tests, ECG data was obtained from the ECG signal generator
interface circuit, instead of an ECG sensor on the patients body. The
generator generates a synthesized ECG signal with a user-settable
signal duration, sampling frequency, QRS waves, etc. Fig. 12
oscilloscope output of the interface. This analog ECG signal, sup
MICAz wireless sensor node, is nearly identical to a theoretically cal
signal. The deflections in the tracing of the ECG comprise the Q, R, a
that represent the ventricular activity of the heart. The interval betw
peaks indicates the time between heartbeats. [Paper I]
Fig. 12. (a) ECG data from the ECG signal generator, (b) ECG signinterface circuit board, MICAz sensor node and base station with an RS-
[I, published by permission of Rare Metal Materials and Engineering].
5 2 Wearable u Healthcare monitoring
(a) (b)
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versatile framework for the incorporation of sensing, monitor
processing devices. Moreover, the smart shirt can be us
applications such as battlefield, public safety, health monito
fitness, among others [48, 49]. [Paper III]
Fig. 13. Smart shirt with an integrated wearable sensor nod
permission of Elsevier].
The monitoring of vital signs during the wearing of the desig
tested by real time monitoring of the ECG and acceleration
For the simultaneous monitoring of physiological ECG data a
smart shirt wearer, a treadmill was used. The speed of
controlled at a speed of 5km/h for walking and 8km/h for r
test on the treadmill was performed with the wearer standing
walking and running on the treadmill as shown in Fig. 14. F
results for walking, running and resting after the exercise.
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Fig. 14. ECG signal variations during walking, running and resting on the
published by permission of Elsevier].
The raw acceleration signals from a 3-axes accelerometer in the wea
node of a smart shirt during the exercise of a person on a treadmill we
in a wireless sensor network, as shown in Fig. 15. Acceleration sig
valuable information for the wearers activity classification, such
running and resting (standing). [Paper III]
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Fig. 15. Acceleration signals form a three-axes accelerometer du
and resting of a person on a treadmill [III, published by permissio
5.3 ECG data on the client display
Attached to the ECG signal generator and interface circuit
node collected the ECG signal at a sampling rate of 125 Hz.
also collected data at a 125 Hz sampling rate. Fig. 16 sho
sampled at a 12 bit resolution, in the terminal PCs GUI. A
ECG data obtained from the ECG signal generator via the int
12 (b) and the ECG data in the terminal PCs GUI in Fig. 1
sensor data were accurately transferred to the terminal PC
802.15.4 communication between the sensor node and the ba
is true concerning the transmission of data via TCP/IP betwee
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Fig. 16. ECG data in the terminal PCs GUI [IV, published by permission of
5.4 PDA display
A PDA (Personal Digital Assistant) was also used as a client termina
shows a PDA GUI snapshot of the PDA emulator, which displays rea
data sent from the server. The graphic user interface was developed t
PDA terminal to display the recorded ECG data in real time on the PD
and PDA screen, as shown in Fig.17 (a) and (b). [Paper I]
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5.5 Reliability analysis
The parameters used in the experiments are summarized i
measurement, a total of 500 packets were sent to the base-
packet size of 46 bytes in each packet. The measurements fo
made from a 1 to 100 meter distance between sensor nodes a
system operates at a 2.4 GHz band and offers a bit rate of 250
Table 4. Table 1 Reliability analysis parameters.
Parameters Value
Number of sent packets 500 (ECG data)
Number of packet size 46 bytes
Number of nodes 1~5
Topology configuration Randomized
Channel data rate 250 kbps
Ground distance 1~100 m
RF frequency 2.45 GHz
RF power 25~0 dBm
5.5.1 Reliability test in function of distance between
For empirical measurements, three scenarios were consider
distance between sensor nodes and the base-station, (2)
deployed sensor nodes in a network, (3) data transmissio
intervals. They were measured to analyse the reliability of th
rate wireless health monitoring applications. The PER is
received data that is analyzed to evaluate performance accord
All of the experiments were conducted using ECG sens
environment. The first experiment is about the measureme
function of distance, in a short communication range. The exp
built according to Table 4. The experiment scenario of differe
sensor node and base-station is shown in Fig. 18. For this ex
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Fig. 18. Measurement setup of network reliability of the distance bet
nodes and base-station.
In Fig. 19, the measured PER is shown as a function of the distan
sensor node and base-station. The average packet loss rate was obtain
RF signal strength to 0 dBm and 500 packets were sent to the base-
PER was calculated using the received packet loss rate. The x-axi
distance between sensor node and base-station. The PER increase
distance between sensor node and base-station was increased. The r
that the minimum and maximum packet losses are not much different
was found that the PER in the function of the distance jumped up su50 meters and was almost zero when node 1 and node 2 were dep
same time in a network.
The results of the measured PER versus SNR of different dis
such as D=10, 60 and 90 meter are shown in Fig. 20. The PER is 0
SNR is 8 dB.
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Fig. 19. Measured PER in the function of the distance between s
station.
10 20 30 40 50 60 700
0.1
0.2
0.3
0.4
0.5
0.6
0.7
0.8
0.9
1
Distance [m]
PER
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Fig. 20. Measured PER versus SNR for different distance values, D=1
meter.
5.5.2 Reliability test in the function of the number of the se
nodes
The second set of experiments was to measure the PER as a fun
number of the sensor nodes, as shown in Fig. 21. In this ex
randomized topology was used and four sensor nodes and one base-
deployed in a network. It was assumed that each sensor node is abo
away from a base-station and RF signal strength was set to 5 dBm.
The PER, by deployment of the number of sensor nodes, is show
-15 -10 -5 0 510
-3
10-2
10-1
100
Eb/N
0(dB)
BER
DD
D
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PER increases with an increase in the number of nodes, du
packets.
Fig. 21. Measurement setup for deployment of the number of sen
0.2
0.3
0.4
0.5
0.6
0.7
0.8
0.9
1
PER
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Table 5. End-to-end success rate of number of transmission nodes.
Node ID Number of nodes Success rate (%)
1 1 99.56
2 1 99.32
2 99.44
3 1 72.4
2 71.64
3 72.52
4 1 59.32
2 50.52
3 59.96
4 43.8
5 1 39.72
2 47.76
3 41.56
4 35.56
5 37.96
5.5.3 Reliability test for different time intervals
For the last experiment, a scenario was considered for different time
different sensors using ECG and temperature sensors. Fig. 23 shows t
the PER for different sampling time intervals, when ECG data packeto the base-station at a rate of every 0.01 sec. On the other hand, the t
of the temperature sensor was set to 1 sec when sending the data
station. The PER of the temperature sensor is almost 0, when seven s
are deployed in a network. On the other hand, in the ECG experime
increased sharply for three or more sensor nodes in the network. As th
ECG sensor nodes increases, the PER also increases because of conte
multiple sensor nodes and data packet overflow.
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Fig. 23. Measured PER for different sampling time intervals,
temperature sensors (1 sec).
1 2 3 4 5 6 7 80
0.1
0.2
0.3
0.4
0.5
0.6
0.7
0.8
0.9
1
Number of nodes
PE
R
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6 Discussion
The main objective of this thesis project was to study the use of wir
networks in a healthcare system as a low power consumption, low
hoc network. This thesis project focused on two specific research to
development of a distributed healthcare system for vital signs moni
wireless sensor network devices and 2) the empirical analysis of the
such low-rate wireless technology ubiquitous health monitoring applic
6.1 Multi-hop network for wireless body area network
This study proposes a ubiquitous healthcare system for vital signs m
Chapter 3. Since remote sensing techniques are to use wireless health
this thesis project sought to provide a reliable ECG signal for
healthcare monitoring. While technological advancements have changes in many aspects of daily life, there is still a significant gap
existing solutions and the needs in the medical field.
This thesis project is an endeavour to suggest a solution for utiliz
technologies and to provide a remote health monitoring system desi
medical environment. This system provides continuous and
monitoring for patient care in order to capture transient behaviour.
consists of three major components; a body sensor network node, loca
unit and a central server. Body sensor network nodes are attached on t
patient based on wireless sensor networks. The gathered data is
wirelessly over radio to the receiving base-station. Recent resear
focused on the development of wireless sensor networks and health
systems. For example, a number of wearable systems have been pr
integrated wireless transmission and local processing. The vital sign
systems worked fine in single-hop (ad-hoc network) data commun
revealed some scheduling problems in a multi-hop network. One
difficult constraints was that several wireless biological data sensor
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6.2 Electrocardiogram and accelerometer sensor
The electrocardiogram (ECG) is currently one of the mosmedical diagnostic procedures. ECG is usually used in a dia
monitoring mode. In the monitoring mode, the frequency
0.5Hz to 40Hz. In the diagnostic mode, the high-pass filter
the low-pass filter at 150Hz. The ECG sampling rate was
project, which allowed the bandwidth of the ECG (0.05 to 12
The ECG signal was amplified with a gain of 200 (24.8ddefault value of the sampling rate is fixed at a resolution of
seconds (10Hz). In this thesis project, we tried to apply
indicating 250Hz, with which an ECG signal cannot b
Therefore, we were interested in obtaining better performan
sampling rate, because according to well-known sampling th
rate must be more than two times the highest frequency
However, a bandpass-filter from 0.05 to 123Hz was used to li
converter (ADC) saturation and for anti-aliasing when the a
playback unit were digitized. Perhaps there are not very man
above 62Hz. The ADC was unipolar, with a 12-bit resolution
Sample values thus range from 0 to 2047 inclusive, wit
corresponding to zero volts. So, to convert a sample back
(millivolts), the ADC Zero 1024) is subtracted from the sam
divided by the gain.
Accelerometer sensors have been widely used to monito
movement parameters. We attached on the chest a three-ax
measure body acceleration as the reference signal. The subj
running on the treadmill. Acceleration signals provide valuab
as walking, running and resting (standing) in our experimacceleration signal, together with an ECG signal which includ
are measured as shown in Fig. 24. As seen in Fig. 24, Y-axis
the most sensitive to the motion artefact contained in the ECG
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Fig. 24. ECG signal with motion artefact and three-axes accelerometer sig
6.3 Wearable system for ubiquitous healthcare
A wearable system for ubiquitous healthcare should provide stable si
the patients daily activities. Resistance to motion artefact remains
challenge for wearable systems. Efforts are ongoing to eliminate
improving hardware design and applying signal processing algorith
studies have been devoted to the development of ring, watch, band
based wearable monitors, to improve the patients tolerance. In our sm
is still not very clear how to reduce the motion artefacts. Further impr
artefact reduction will remain critical for improvements in the wearab
acceptance and medical value of existing wearable systems. These c
are limited by factors including hardware design constraints associa
sensing of human status, power consumption, data storage and signal
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7 Conclusion
The main objective of this thesis project is to implement a wireles
monitoring system for measuring ECG from a patient in the home e
The research focuses on two specific research objectives: 1) the deve
distributed healthcare system for vital signs monitoring using wir
network devices and 2) a practical test and performance evalua
reliability for such low-rate wireless technology in ubiquitous health
applications.The first section of the thesis describes the design and impleme
ubiquitous healthcare system with tiny devices for the home car
persons. The system has been designed using a commercially availa
sensor network platform (MICAz, Crossbow Technology Inc., USA)
is capable of obtaining physiological data from a sensor attached to
body and transfers the data wirelessly to a remote base-station inetwork following the IEEE 802.15.4 standard for wireless pe
networks. The system concept can be used for ad-hoc routing o
monitoring signals to base-stations within the hospital premises, a
applications that require monitoring from the patients home. A wi
monitoring system has potential to provide an improved service
doctors and caregivers through continuous health monitoring. In addi
shirt with wireless sensor network compatibility is designed and fabri
continuous monitoring of physiological ECG signals and physical act
from an accelerometer simultaneously. To collect physiological EC
activity of the smart shirt wearer simultaneously, the performance tes
a treadmill by a wearer who is resting, walking and running on the
various speeds. Thus, the developed smart shirt system can be
improving the accuracy of a patient's diagnosis by continuous monit
non-invasive, comfortable and convenient shirt to wear in a wir
network environment.
In the experimental tests, ECG data was displayed on a Gra
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Three scenarios of performance studies were conside
measurement: 1) the effects of the distance between sensor no
2) the number of the deployed sensor nodes in a network and
by different time intervals. They were measured to analyse
technology in low-rate wireless u-Healthcare monitoring appl
In this thesis project, three scenarios were considere
reliability of low-rate wireless u-Healthcare monitoring. In
using ECG data, the PER is higher (about 104) than the env
coming from a temperature sensor. Moreover, reliability basenetworks, in particular, low-rate wireless medical monitori
distance between sensor node and base-station, the number o
network and different time intervals affect reliability perfor
experimental results. It was found that the PER of distance j
after 50 meters and was almost zero when node 1 and nod
same time in a network. To apply low-rate wireless techubiquitous health monitoring applications, the sampling rat
and data packet sizes, as well as reliable medical devices, a
the overall reliability of the system.
R f
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monitoring of elderly person. Sensor Letters 6(6): 10541058.
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for ubiquitous health and activity monitoring. Sensors and Actuators
140(2): 390395.IV Walia G, Lee Y-D, Chung W-Y & Myllyl R (2006) Distribut
monitoring in an ad-hoc network using a wireless sensor network. P
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V Lee Y-D, Lee D-S, Walia G, Myllyl R & Chung W-Y (2006) Query
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S E R I E S C T E C H N I C A
355 Ronkainen Sami (2010) Designing for ultra-mobile interaction : experiences and a
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355. Ronkainen, Sami (2010) Designing for ultra-mobile interaction : experiences and a
method
356. Loikkanen, Mikko (2010) Design and compensation of high performance class ABamplifiers
357. Puikko, Janne (2010) An exact management method for demand driven, industrial
operations
358. Ylioinas, Jari (2010) Iterative detection, decoding, and channel estimation in
MIMO-OFDM
359. Tervonen, Pekka (2010) Integrated ESSQ management : as a part of excellent
operational and business managementa framework, integration and maturity
360. Putkonen, Ari (2010) Macroergonomic approach applied to work system
modelling in product development contexts
361. Ou, Zhonghong (2010) Structured peer-to-peer networks: Hierarchical
architecture and performance evaluation
362. Sahlman, Kari (2010) Elements of strategic technology management
363. Isokangas, Ari (2010) Analysis and management of wood room
364. Vnnen, Mirja (2010) Communication in high technology product development
projects : project personnels viewpoint for improvement
365. Korhonen, Esa (2010) On-chip testing of A/D and D/A converters : static linearitytesting without statistically known stimulus
366. Palukuru, Vamsi Krishna (2010) Electrically tunable microwave devices using BST-
LTCC thick films
367. Saarenp, Ensio (2010) Good construction quality : the realisation of good
construction quality in Finnish construction regulations
368. Vartiainen, Johanna (2010) Concentrated signal extraction using consecutive
mean excision algorithms
369. Nousiainen, Olli (2010) Characterization of second-level lead-free BGA
interconnections in thermomechanically loaded LTCC/PWB assemblies
370. Taskila, Sanna (2010) Improved enrichment cultivation of selected food-
contaminating bacteria
371. Haapala, Antti (2010) Paper machine white water treatment in channel flow :
integration of passive deaeration and selective flotation
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