Biomedical Instrumentation Lab Manual Biomedical Engineering Department, School of bioengineering, SRM University Page 1 LABORATORY MANUAL PROGRAMME: B.Tech SEMESTER /YEAR: V / III SUBJECT CODE: BM0315 SUBJECT NAME: Biomedical Instrumentation Lab Prepared By: Name: S.P. Angeline Kirubha Designation: A.P (Sr. Gr) DEPARTMENT OF BIOMEDICAL ENGINEERING SCHOOL OF BIOENGINEERING, FACULTY OF ENGINEERING & TECHNOLOGY SRM UNIVERSITY (UNDER SECTION 3 of UGC ACT 1956) KATTANKULATHUR-603203 Tamil Nadu, India LIST OF EXPERIMENTS
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Biomedical Instrumentation Lab Manual Biomedical Engineering Department, School of bioengineering, SRM University Page 1
LABORATORY MANUAL
PROGRAMME: B.Tech
SEMESTER /YEAR: V / III
SUBJECT CODE: BM0315
SUBJECT NAME: Biomedical Instrumentation Lab
Prepared By:
Name: S.P. Angeline Kirubha
Designation: A.P (Sr. Gr)
DEPARTMENT OF BIOMEDICAL ENGINEERING SCHOOL OF BIOENGINEERING,
FACULTY OF ENGINEERING & TECHNOLOGY
SRM UNIVERSITY (UNDER SECTION 3 of UGC ACT 1956) KATTANKULATHUR-603203
Tamil Nadu, India
LIST OF EXPERIMENTS
Biomedical Instrumentation Lab Manual Biomedical Engineering Department, School of bioengineering, SRM University Page 2
Sl. No Experiment Page .No
1 Blood Pressure Measurement 1
2 Real time monitoring of Echocardiography 6
3 Working of different types of Diathermy equipments – study 20
3.a Shortwave Diathermy 22
3.b Ultrasound Diathermy 26
3.c Surgical Diathermy 28
4 ECG wave analysis using simulator 32
5 Real time patient monitoring system 35
6 Ultrasound blood flow measurement to identify arteries and
veins
39
7 Respiratory system analysis using Spirometer 41
8 Analysis of ECG abnormal wave pattern using Arrhythmia
Simulator
47
9 EEG wave analysis using simulator 52
10 Auditory system check up using Audiometer 56
11 Heart sound measurement using PCG 61
12 Biotelemetry 65
13 Pacemaker Module 68
14 ECG heart rate alarm system with HRV 73
15 EMG Biofeedback with NCV 78
Biomedical Instrumentation Lab Manual Biomedical Engineering Department, School of bioengineering, SRM University Page 3
Ex. No 1 Blood Pressure Measurement
Aim: To Measure blood pressure using Sphygmomanometer, semi-automatic blood pressure
measuring instrument and automatic blood pressure measuring instrument.
Apparatus Required:
1. Cuff
2. Inflator
3. Power supply
4. Stethoscope
5. Sphygmomanometer
6. Semi-automatic bp measuring unit
7. Automatic bp measuring unit
THEORY:
Blood Pressure
Blood pressure is a measurement of the force applied to the walls of the arteries as the
heart pumps blood through the body. The pressure is determined by the force and amount of
blood pumped, and the size and flexibility of the arteries. Blood pressure is continually changing
depending on activity, temperature, diet, emotional state, posture, physical state, and medication
use. The ventricles of heart have two states: systole (contraction) and diastole (relaxation).
During diastole blood fills the ventricles and during systole the blood is pushed out of the heart
into the arteries. The auricles contract anti-phase to the ventricles and chiefly serve to optimally
fill the ventricles with blood. The corresponding pressure related to these states are referred to as
systolic pressure and diastolic pressure .The range of systolic pressure can be from 90 mm of Hg
to 145mm of Hg with the average being 120 mm of Hg. The diastolic pressure typically varies
from 60mm of Hg to 90 mm of Hg and the average being 80 mmofHg.
PRINCIPLE
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The upper arm is wrapped with the cuff belt connected to a mercury pressure gauge and air is
pumped with a rubber ball to increase cuff pressure about 30 mmHg higher than the systolic
blood pressure to block the artery and stop blood flow downstream. Then, the cuff pressure is
slowly lowered. The artery opens at the instant when the cuff pressure decreases below the
systolic blood pressure and blood begins to flow on and off in synchrony with pulses causing the
opening and closing of the artery. The sound emitted by the pulses is named Korotkoff's and
continues until the cuff pressure decreases below the systolic blood pressure and the artery
ceases the opening and closing. The stethoscope placed closely to the artery downstream of the
cuff is used to hear Korotkoff's sound; the blood pressures are measured. Cuff pressure when
Korotkoff's sound begins to be heard is defined as the highest blood pressure and that when the
sound disappears is defined as the lowest pressure.
SPHYGMOMANOMETER
Mercury Sphygmomanometer
This includes a mercury manometer, an upper arm cuff, a hand inflation bulb with a pressure
control valve and requires the use of a stethoscope to listen to the Korotkoff sounds. Relies on
the ausculatory technique.
Advantages:
Regarded as the 'Gold Standard'. It is transportable and is understood by users. Can be used on
most patients.
Disadvantages:
It contains toxic mercury which can lead to maintenance problems, although it is safe in normal
useage. Can be prone to observer bias.
Semi-automated device
This includes an electronic monitor with a pressure sensor, a digital display, an upper arm cuff
and a hand bulb. The pressure is raised manually using the hand bulb. The device automatically
deflates the cuff and displays systolic and diastolic values. Pulse rate may also be displayed. Is
battery powered and uses the oscillometric technique.
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Advantages:
Is mercury-free, lightweight and compact. There is no observer bias and it is portable and easy to
use.
Disadvantages:
It was originally designed for home use and may not be suitable for all patients, particularly
those with arrhythmias. May be difficult to calibrate. Some cuffs cannot be washed or
decontaminated.
Automated device
This includes an electronic monitor with a pressure sensor, a digital display and an
upper arm cuff. An electrically driven pump raises the pressure in the cuff. Devices may have a
user-adjustable set inflation pressure or they will automatically inflate to the appropriate level,
about 30 mmHg above the predicted systolic reading. On operation of the start button the device
automatically inflates and deflates the cuff and displays the systolic and diastolic values. Pulse
rate may so be displayed. Devices may also have a memory facility that stores the last
measurement or up to 10 or more previous readings. It is battery powered and uses the
ocillometric technique.
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Block Diagram:
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Tabulation:
S.No Patient
Name
Sphygmomanometer Semi Automated Automated
Systolic
(mmHg)
Diastolic
(mmHg)
Systolic
(mmHg)
Diastolic
(mmHg)
Pulse (bpm)
Systolic
(mmHg)
Diastolic
(mmHg)
Pulse
(bpm)
1 X
2 Y
3 Z
4 A
Result:
Thus the blood pressure measurements are done using mercury sphygmomanometer, semi
automated and automated devices for human.
Ex. No 2 Real time monitoring of Echocardiography
Biomedical Instrumentation Lab Manual Biomedical Engineering Department, School of bioengineering, SRM University Page 8
Aim: To acquire real time ECG of 12 lead ECG system and analyse the signals.
ECG is a transthoracic interpretation of the electrical activity of the heart over time captured and
externally recorded by skin electrodes. It is a noninvasive recording produced by an
electrocardiographic device.
OBJECTIVES:
Understand and be able to identify the different deflections seen in an electrocardiogram, a trace
of the heart’s electrical activity.
COMPONENTS REQUIRED:
S.NO
DESCRIPTION
RANGE
QUANTITY
1 ECG sensor with leads
(electrode patches)
10 lead
1 No
2 Computer interface
1 No
3 PC 1 No
4 Gel some
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DIAGRAM:
Leads:
Graphic showing the relationship between positive electrodes, depolarization wavefronts (or
mean electrical vectors), and complexes displayed on the ECG.
In electrocardiography, the word lead (pronounced /lid/) refers to the signals transmitted and
received between two electrodes. The electrodes are attached to the patient's body, usually with
very sticky circles of thick tape-like material (the electrode is embedded in the center of this
circle).
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ECG leads record the electrical signals of the heart from a particular combination of recording
electrodes which are placed at specific points on the patient's body.
PLACEMENT OF ELECTRODE:
Ten electrodes are used for a 12-lead ECG. They are labeled and placed on the patient's body as
follows:
ELECTRODE
LABEL (in the
USA)
ELECTRODE PLACEMENT
RA On the right arm, avoiding bony prominences.
LA In the same location that RA was placed, but on the left arm this time.
RL On the right leg, avoiding bony prominences.
LL In the same location that RL was placed, but on the left leg this time.
V1 In the fourth intercostal space (between ribs 4 & 5) to the right of the sternum
(breastbone).
V2 In the fourth intercostal space (between ribs 4 & 5) to the left of the sternum.
V3 Between leads V2 and V4.
V4 In the fifth intercostal space (between ribs 5 & 6) in the midclavicular line (the
imaginary line that extends down from the midpoint of the clavicle (collarbone).
V5
Horizontally even with V4, but in the anterior axillary line. (The anterior
axillary line is the imaginary line that runs down from the point midway
between the middle of the clavicle and the lateral end of the clavicle; the lateral
end of the collarbone is the end closer to the arm.)
V6 Horizontally even with V4 and V5 in the midaxillary line. (The midaxillary line
is the imaginary line that extends down from the middle of the patient's armpit.)
Unipolar vs. bipolar leads
There are two types of leads—unipolar and bipolar. Bipolar leads have one positive and one
negative pole. In a 12-lead ECG, the limb leads (I, II and III) are bipolar leads. Unipolar leads
have only one true pole (the positive pole). The negative pole is a "composite" pole made up of
Biomedical Instrumentation Lab Manual Biomedical Engineering Department, School of bioengineering, SRM University Page 1
signals from lots of other electrodes. In a 12-lead ECG, all leads besides the limb leads are
Power supply is connected to the simulator. A simulator is a device which is an imitation
of the real time record of ECG. All the abnormality and normal ECG waveforms are stored in it.
DIFFERENT ECG WAVEFORMS
NORMAL ECG WAVEFORM
BRACHYCARDIA
TACHYCARDIA
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ATRIAL FIBRILLATION
VENTRICULAR FIBRILLATION
Each heart beat originates as an electrical impulse from a small area of tissue in the right
atrium of the heart called the sinus node. The impulse initially causes both of the atria to
contract, then activates the atrioventricular (or AV) node which is normally the only electrical
connection between the atria and the ventricles , which can be called as main pumping chambers.
The impulse then spreads through both ventricles via the Bundle of His and the Purkinje fibres
causing a synchronised contraction of the heart muscle, and thus, the pulse. In adults the normal
resting heart rate ranges from 60 to 80 beats per minute. The resting heart rate in children is
much faster
Bradycardia (Brad)
A slow rhythm, beats less than 60 beats/min, is called bradycardia. This may be caused
due to a pause in the normal activity of the sinus node or by blocking of the electrical impulse on
its way from the atria to the ventricles. There is a long RR interval in bradycardia
Tachycardia (Tach)
Any resting heart rate faster than 100 beats/minute is called as tachycardia. Increased
heart rate is a normal response to physical exercise or emotional stress. Inverted QRS waveform
is obtained with short RR intervals in tachycardia.
Atrial Fibrillation (A-fib)
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Atrial fibrillation affects the upper chambers of the heart, known as the atria. Atrial
fibrillation may be due to serious underlying medical conditions. It is not typically a medical
emergency. P wave and T wave is fibrillated or lost in fibrillation.
Ventricular Fibrillation (V-fib)
Ventricular fibrillation occurs in the ventricles (lower chambers) of the heart; it is always
a medical emergency. If left untreated, ventricular fibrillation can lead to death within minutes.
When a heart goes into V-fib, effective pumping of the blood stops. Vfib is considered a form of
cardiac arrest. No amplitude and frequency could be seen in Vfib as it is an irregular waveform.
There is no FFT obtained.
Thus the different abnormal ECG waveforms are monitored using ECG-A-S in remote areas
using the mobile unit (ECG-A-S). It is also possible to connect an alarm to the ECG-A-S or
setting up threshold limits over the parameters. Thus when the patient’s ECG parameters exceed
or cross over the preset limits, then the sensors alarms and alert the attention towards the patient,
and this entire set up is possible to be connected to a solar panel so that it can work even in the
absence of electricity or even during night.
Result:-
The abnormal changes in amplitude for a subject having arrhythmia is verified and recorded.
Ex. No 9 EEG wave analysis using simulator
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AIM:
To measure and record the amplitude and time taken for the different alpha , theta, beta and
gamma EEG waves.
APPARATUS REQUIRED:
1. EEG stimulator
2. Connecting probes
3. Biokit physiograph
4. PC
THEORY:
Electroencephalography (EEG) is the recording of electrical activity along the scalp produced by
the firing of neurons within the brain. In conventional scalp EEG, the recording is obtained by
placing electrodes on the scalp with a conductive gel or paste. Electrode locations and names are
specified by the International 10–20 system for most clinical and research applications. Each
electrode is connected to one input of a differential amplifier (one amplifier per pair of
electrodes); a common system reference electrode is connected to the other input of each
differential amplifier. These amplifiers amplify the voltage between the active electrode and the
reference.
A typical adult human EEG signal is about 10µV to 100 µV in amplitude when
measured from the scalp and is about 10–20 mV when measured from subdural electrodes.
EEG WAVE PATTERNS:
DELTA WAVE:
Delta is the frequency range up to 4 Hz. It tends to be the highest in amplitude and the slowest
waves. It is seen normally in adults in slow wave sleep. It is also seen normally in babies.
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THETA WAVE:
Theta is the frequency range from 4 Hz to 7 Hz. Theta is seen normally in young children. It may
be seen in drowsiness or arousal in older children and adults; it can also be seen in meditation.
ALPHA WAVES:
Alpha is the frequency range from 8 Hz to 12 Hz. Hans Berger named the first rhythmic EEG
activity he saw, the "alpha wave. It emerges with closing of the eyes and with relaxation, and
attenuates with eye opening or mental exertion. The posterior basic rhythm is actually slower
than 8 Hz in young children.
BETA WAVES:
Beta is the frequency range from 12 Hz to about 30 Hz Beta activity is closely linked to motor
behaviour and is generally attenuated during active movements. It is the dominant rhythm in
patients who are alert or anxious or who have their eyes
open.
Since an EEG voltage signal represents a difference between the voltages at two electrodes, the
display of the EEG for the reading encephalographer may be set up in one of several ways. The
representation of the EEG channels is referred to as a montage.
BIPOLAR MONTAGE:
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Each channel (i.e., waveform) represents the difference between two adjacent electrodes. The
entire montage consists of a series of these channels. For example, the channel "Fp1-F3"
represents the difference in voltage between the Fp1 electrode and the F3 electrode. The next
channel in the montage, "F3-C3," represents the voltage difference between F3 and C3, and so
on through the entire array of electrodes.
REFERENTIAL MONTAGE:
Each channel represents the difference between a certain electrode and a designated reference
electrode. There is no standard position for this reference; it is, however, at a different position
than the "recording" electrodes. Midline positions are often used because they do not amplify the
signal in one hemisphere vs. the other. Another popular reference is "linked ears," which is a
physical or mathematical average of electrodes attached to both earlobes or mastoids.
AVERAGE REFERNTIAL MONTAGE:
The outputs of all of the amplifiers are summed and averaged, and this averaged signal is used as
the common reference for each channel.
LAPLACIAN MONTAGE:
Each channel represents the difference between an electrode and a weighted average of the
surrounding electrode.
When analog (paper) EEGs are used, the technologist switches between montages during the
recording in order to highlight or better characterize certain features of the EEG. With digital
EEG, all signals are typically digitized and stored in a particular (usually referential) montage;
since any montage can be constructed mathematically from any other, the EEG can be viewed by
the electroencephalographer in any display montage that is desired.
TABULAR COLUMN:
Biomedical Instrumentation Lab Manual Biomedical Engineering Department, School of bioengineering, SRM University Page 5
WAVES
AMPLITUDE(V)
TIME(S)
FREQUENCY(Hz) POWER
ALPHA
BETA
THETA
DELTA
PROCEDURE:
1. From the EEG stimulator input is given to the biokit physiograph.
2. The physiograph kit is connected to the PC using RS232.
3. For the respective alpha, beta , theta and delta waves the amplitude and time are noted.
4. The FFT is performed for the respective waves and the values are noted.
Result:
Thus the EEG waves are studied and the amplitude and time for each waveforms are noted for a
subject.
Ex. No 10 Auditory system check up using Audiometer
AIM:
To plot audiogram of the subject using air conduction pure tone audiometer
EQUIPMENTS REQUIRED:
Biomedical Instrumentation Lab Manual Biomedical Engineering Department, School of bioengineering, SRM University Page 5
a) Sine wave generator 0 to 10KHz b) White noise generator c) L‐R selector d) Audio Amplifier – 2 Nos. e) Level Indicator Log f) Battery g) Charger
THEORY:
The human ear has three main sections, which consist of the outer ear, the middle ear, and the inner ear. Sound waves enter the outer ear and travel through the ear canal to the middle ear. The ear canal channels the waves to the eardrum, a thin, sensitive membrane stretched tightly over the entrance to the middle ear. The waves cause the eardrum to vibrate. It passes these vibrations on to the hammer, one of three tiny bones in the ear.
The hammer vibrating causes the anvil, the small bone touching the hammer, to vibrate. The anvil passes these vibrations to the stirrup, another small bone which touches the anvil. From the stirrup, the vibrations pass into the inner ear. The stirrup touches a liquid filled sack and the vibrations travel into the cochlea, which is shaped like a shell. Inside the cochlea, there are hundreds of special cells attached to nerve fibers, which can transmit information to the brain. The brain processes the information from the ear and this distinguishes between different types of sounds.
Air and bone conduction:
Air conduction, by definition, is the transmission of sound through the external and middle ear to the internal ear. Bone conduction, on the other hand, refers to the transmission of sound to the internal ear mediated by mechanical vibration of the cranial bones and soft tissues. The most important diagnostic differential from the standpoint of the functional hearing tests is the relationship between air and bone
Biomedical Instrumentation Lab Manual Biomedical Engineering Department, School of bioengineering, SRM University Page 5
conduction acuity. Clinical observation has shown that hard‐of‐hearing patients with middle ear disease have normal hearing by bone conduction, whereas patients with inner ear involvement have decreased or diminished bone–conduction.It has been concluded from clinical observations that approximately 60dB loss is the maximal air conduction impairment to be anticipated with middle ear defect. Therefore, if the air conduction loss in a patient with apparently typical middle ear pathology exceeds 60 dB, it is likely that inner ear impairment is superimposed on the middle ear lesion.
BLOCK DIAGRAM:
BLOCK DIAGRAM DESCRIPTION:
Sine wave generator
Sine wave generator is used to generate a signal representing the periodic value of a given mathematical function, especially sine waveform, the range here is 0‐ 10 KHz and the output ranges from 2V Pk to Pk.
White noise generator
A white noise generator produces a sound that is random in character which sounds like a rushing waterfall or wind blowing through trees. White noise is a random signal with a flat power spectral
Biomedical Instrumentation Lab Manual Biomedical Engineering Department, School of bioengineering, SRM University Page 6
density. In other words, the signal contains equal power within a fixed bandwidth at any center frequency.
Audio amplifier
Audio amplifier is an electronic amplifier that amplifies low power audio signals to a required level. The audio amplifier used in this application has a frequency range of 0‐10KHz.
Level Indicator
The level indicator displays the level of sound in decibels it has LEDs which indicates the sound level given to the subject.
L‐R selector
The L‐R selector is used to select the ear in which the subject wishes to determine the threshold of hearing.
PROCEDURE:
1) To plot audiogram of the subject using air conduction pure tone audiometer
a) Connect the modules as per the block diagram. b) Switch ON the battery. c) Adjust masking level to a suitable level so that it does not cause discomfort to the subject d) Put L, R switch in L position. e) Keeping x1, x10 switch and set frequency in steps of 100Hz. f) Adjust output dB level till the subject hears the sound. g) Note the frequency and output dB level from DSO and level indicator respectively. h) Repeat the above mentioned procedure for different set of frequencies. i) Put L, R switch in R position j) Repeat the above mentioned procedure for the right ear. k) Plot the graph of frequency versus output dB level for L, R.
TYPICAL AUDIOGRAM
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TABULAR COLUMN Frequency Decible(dB) Left
Right
Left & Right
GRAPH
Sound Level in dB
-10
0
+10
+20
+30
+40
+50
+60
+70
+80
Frequency in Hz
200 500 1K 2K 3K 4K 5K 6K 7K 8K 9K 10K 11K
Left Ear Response
Right Ear Response
L + R Ear Response
Biomedical Instrumentation Lab Manual Biomedical Engineering Department, School of bioengineering, SRM University Page 6
200 400 600 800 1000 -------------- Frequency
RESULT:
The graph of frequency verses output dB level gives audiogram of the subject.
Ex. No 11 Heart sound measurement using PCG
-20 -15 (dB) -10 -5
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AIM
The basic aim of phonocardiograph is to pick up the different heart sounds, filter out the heart sounds and to display or record them.
APPARATUS REQUIRED
• Power supply
• Digital storage oscilloscope
• Head phone
• Phonocardiograph
THEORY
A Phonocardiogram or PCG is a plot of high fidelity recording of the sounds and murmurs made by the heart with the help of the machine called phonocardiograph, or "Recording of the sounds made by the heart during a cardiac cycle". The sounds are thought to result from vibrations created by closure of the heart valves. There are at least two: the first when the atrioventricular valves close at the beginning of systole and the second when the aortic valve closes at the end of systole. It allows the detection of sub audible sounds and murmurs, and makes a permanent record of these events. In contrast, the ordinary stethoscope cannot detect such sounds or murmurs, and provides no record of their occurrence. The ability to quantitate the sounds made by the heart provides information not readily available from more sophisticated tests, and provides vital information about the effects of certain cardiac drugs upon the heart. It is also an effective method for tracking the progress of the patient's disease.
Heart sounds are classified into four groups on the basis of their mechanism of origin, they are
1. Valve closure sound
2. Ventricular filling sound
3. Valve opening sounds and
4. Extra cardiac sounds
Biomedical Instrumentation Lab Manual Biomedical Engineering Department, School of bioengineering, SRM University Page 6
HEART SOUNDS
First heart sound
Second heart sound
BLOCK DIAGRAM
Valve closure sound
AMPLIFIER
OUT LEVEL
AMPLIFIER AMPLIFIER
AMPLIFIER
5 FILTERS
BUFFER
AUDIO (DSO)
PCG DISPLAY
TRANSDUCER
MICROPHONE
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These sounds occur at the beginning of systole (first heart sound) and the beginning of diastole (second heart sound). The first heart sound is due to the closure of mitral and tricuspid valves associated with myocardial contraction. And the second heart sounds is due to the closure of the aortic and pulmonary valves. The first heart sounds are low frequency vibrations occur approximately 0.05s after the onset of the QRS complex of the ECG, the first heart sounds last for (0.1 to 0.12s) and the frequency ranges 30-50Hz.The second heart sound is due to the vibrations set up by the closure of semilunar valves. These sounds start approximately ( 0.03 to 0.05)s after the end of T wave of the ECG, this lasts for (0.08 to 0.14)s and have a frequency up to 250Hz.
Ventricular filling sounds
These sounds occur either at the period of rapid filling of the ventricles (third heart sound) or during the terminal phase of ventricular filling. These sounds are inaudible. Third heart sound starts at (0.12 to 0.18) s after the onset of the second heart sound.it last approximately (0.04 to 0.08) s. The frequency is about 10 to 100 Hz.
Valve opening sounds
These sounds occur at the time of opening of the atria ventricular valves and semi lunar valves. The fourth heart sound starts approximately (0.12 to 0.18) s after the onset of the P wave. The sound last for (0.03 to 0.06)s. And the frequency is 10 to 50 Hz.
Extra cardiac sounds
These sounds occur in late systole or early diastole and are believed to be caused by thickened pericardium which limits ventricular distensibility. Murmurs are sounds related to non-laminar flow of blood in the heart and the great vessels. They are distinguished from the basic heart sounds such that they have noisy character having long duration and with high frequency components up to 1000 Hz.
OBSERVATION TABLE:
Biomedical Instrumentation Lab Manual Biomedical Engineering Department, School of bioengineering, SRM University Page 6
Period:
Peak-peak value:
PROCEDURE
1. Switch on the main power supply.
2. Connect the transducer and microphone.
3. The heart beat is sensed by keeping the sensor on the chest position.
4. Press the acquire button in DSO, when a proper signal is formed.
5. Press the stop button to freeze the signal.
6. Finally measure the peak to peak voltage and time period by using the measure button.
RESULT:
Thus by using a Phonocardiograph, different heart sounds have been identified, displayed and recorded.
Ex. No 12 Biotelemetry
SL.NO:
HEART SOUNDS
AMPLITUDE
1.First heart sound
. 2.Second heart sound
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AIM:
To understand the transmission and reception of biological signal using a telemetry system
EQUIPMENTS REQUIRED:
ECG Amplifier
Low Pass Filter – 2 Nos.
FM Modulator
FM Transmitter
FM Receiver
FM Demodulator
Charger
Battery – 2 Nos.
Electrodes
THEORY:
Telemetry is a system of sending data, usually measurements, over a distance. Telemetric data may be physical, environmental or biological. Telemetry is typically used to gather data from distant, inaccessible locations, or when data collection would be difficult or dangerous for a variety of reasons. In telemetry, specialized instruments carry out measurements of physical quantities, and store or transmit the resulting signal, often after some initial signal processing or conversion. Biotelemetry is the electrical measuring, transmitting, and recording of qualities, properties, and actions of organisms and substances, usually by means of radio transmissions from a remote site. There are single channel and multi channel telemetry systems. For a single channel system, a miniature battery operated radio transmitter is connected to the electrodes of the subject. This transmitter broadcasts the biopotential over a limited range to a remotely located receiver, which detects the radio signals and recovers the signal for further processing. In this situation there is a negligible connection or stray capacitance between the electrode circuit and rest of the system. The receiving system can even be located in a room separate from the subject.
BLOCK DIAGRAM:
Biomedical Instrumentation Lab Manual Biomedical Engineering Department, School of bioengineering, SRM University Page 6
BLOCK DIAGRAM DESCRIPTION:
ECG Amplifier
ECG has amplitude of only about 1 mV, so to detect it an amplifier is required. The ECG amplifier used here has a Gain of 1000 and CMRR of more than 80dB.
Low Pass Filter
A low-pass filter allows low-frequency signals but attenuates (reduces the amplitude of) signals with frequencies higher than the cutoff frequency. When the ECG is amplified, the noise is amplified too, and often swamps the ECG signal. The noise is usually of a higher frequency than the ECG. So the noise can be reduced by low-pass filtering.
FM Modulator
Modulation is used to embed a message (voice, image, data, etc.) on to a carrier wave for transmission. A bandlimited range of frequencies that comprise the message (baseband) is
Biomedical Instrumentation Lab Manual Biomedical Engineering Department, School of bioengineering, SRM University Page 6
translated to a higher range of frequencies. The bandlimited message is preserved, i.e. every frequency in that message is scaled by a constant value. Here the incoming ECG signal is modulated at around 110MHz. The modulated ECG signal is given to the FM Transmitter.
FM Transmitter
FM Transmitter sends a signal (typically 4-20mA) from a process location to a central location for control and monitoring. Here FM transmitter transmits the modulated ECG signal.
FM Receiver
A receiver receives its input through an antenna. It receives the modulated signal from the transmitter. The receiver then passes on the information to the FM Demodulator where the ECG signal is demodulated to obtain the original ECG signal.
FM Demodulator
Demodulation, in radio is the technique of separating a transmitted audio frequency signal from its modulated radio carrier wave. Here the modulated ECG signal is demodulated at a frequency of around 100Hz and the original ECG signal is recovered.
PROCEDURE:
Connect the modules as per the block diagram.
Switch ON the battery.
Connect the ring electrodes to the subject.
View the transmitted signal on the DSO.
The various outputs from each of the modules can be viewed on the DSO by connecting the output banana pin to the desired module.
RESULT:
Thus we understand the transmission and reception of biological signal using a telemetry system.
Ex. No 13 Pacemaker Module
AIM:
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To understand the working of an external pacemaker and the various modules included in it.
EQUIPMENTS REQUIRED:
a) Oscillator
b) Refra Generator –2 Nos.
c) Pulse width control
d) Amplitude Control
e) Paced output
f) Synch Generator
g) QRS Detector
h) QRS Filter
i) ECG Amp Pacemaker
j) Patient Simulator
k) Electrodes
l) Charger
m) Battery
THEORY:
A pacemaker is an electronic device equipped with a battery, electronic circuits and memory that generates electronic signals (pacing pulses), which are carried along insulated wires (leads) to the heart to make the muscle beat at a normal rhythm. Bradycardia, a heartbeat that slows to an unhealthy rate, is the most frequent reason for a pacemaker. There are three basic types of temporary or permanent pacemakers, and each may work on demand, constantly or according to the heart's activity. Pacemakers are also of internal and external type. Internal pacemakers are mostly used for permanent heart damages are surgically implanted beneath the skin near the chest or abdomen with its output leads connected directly to the heart muscle. The external pacemakers are mostly used for temporary heart irregularities and are placed outside the body in the form of a wrist watch or in the pocket, from which one wire will go into the heart through the vein. Pacemakers may also be of single-, dual-, or triple chambered.
Demand Pacemakers
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When the heart's rate is too slow or it misses a beat, demand pacemakers, which monitor the heart's activity, will send an electrical pulse to set the heart back to a more normal rhythm.
Fixed-rate Pacemakers
Fixed-rate pacemakers discharge steadily, regardless of the heart's natural electrical activity.
Rate-responsive Pacemakers
Rate-responsive pacemakers have sensors that adjust automatically to changes in your physical activity. They are designed to raise or lower the heart rate to meet the body's needs.
Here we consider demand pacers having circuitry that analyze the ECG (as detected by the pacer's electrodes). If a QRS is detected, the internal clock is reset thereby delaying the time until when the next pulse is due (i.e. the escape cycle length). The escape interval (the time between the last intrinsic beat and the paced beat) is equivalent to the rate at which the pacemaker is set to activate. Once the pacemaker begins pacing, it will not stop until the intrinsic heart rate climbs above the paced rate.
BLOCK DIAGRAM:
BLOCK DESCRIPTION:
Oscillator
An oscillator produces a repetitive electronic signal, often a sine wave or a square wave. The oscillator synchronises with the synch generator. If an R wave is detected the oscillator circuit is reset. In the absence of R wave, the oscillator circuit starts and delivers pulses at a paced rate till
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the heart rate climbs above the paced rate. The output voltage is 5V and a 10msec pulse. the oscillator has rate control knob on the top panel.
Refractory Generator
The refractory generator is a non-retrigerrable monostable multivibrator which generates a 250ms delay following an output pulse or a sensed R-wave during which the amplifier in the sensing circuit will not respond to outside signals. The input is a pulse of 0-5V (Min 1msec) and output is pulse of 0-5V (250msec).
Pulse Width Control
The pulse width circuit is a basic RC network which determines the duration of the pulse delivered to the heart. The pulse width control has a range of 0.1- 2.1 msec and output of 5V.
Amplitude Control
The output of the pulse width control is given to the amplitude control which controls the amplitude of the delivered pulses.
Paced output
The paced output delivers the pulse to the heart, the duration and amplitude being controlled by the pulse width control and amplitude control. The output also goes to the ECG amplifier as a feedback signal.
ECG Amp. Pacemaker
The input to the ECG amplifier is from the Paced output which gives ECG signal as the feedback and it is amplified here.
QRS Filter
The Demand type pacemaker works on the presence or absence of R wave hence a QRS filter is used to selectively filter the QRS wave. The QRS Filter used here is a Bandpass Filter having limits from 22Hz to 45Hz with a gain of 10.
QRS Detector
With the presence of an R wave, the QRS detector will generate a pulse. The input voltage is 1V Pk –Pk and output voltage is 5V. It has a frequency range of 15-30Hz.
Synch Generator
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The Synch Generator synchronises with the QRS Detector and in presence of an R wave it resets the oscillator circuit. In the absence of R wave it allows the oscillator to deliver pulses at its preset rate.
Patient Simulator
The Patient Simulator simulates the abnormal heart condition- Bradycardia, Tachycardia and AV Block.
Front Panel
a) It has 3 buttons to simulate any of the three conditions mentioned above.
b) A control knob to limit the rate of simulating heart conditions.
c) Control the threshold of the simulating conditions.
Top Panel
The top panel of the Simulator has the sketch of the heart. Red and Yellow LEDs arranged in various regions of the heart. The flashing of the Red LEDs indicates the simulated abnormal heart condition. Once the Green LED flashes it signifies the pacemaker has taken over. Output pin connectivity to the DSO to view the paced output.
Back Panel
Feedback to the paced output through banana pins.
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PROCEDURE:
1. Connect the modules as per the block diagram.
2. Select one of the abnormal conditions in the Pacemaker Simulator and keep holding the button for simulating the condition.
3. The Paced output leads detect this abnormality and the output is given as a feedback to the ECG Amplifier.
4. As a normal QRS wave is not detected, the Oscillator is now triggered and the Pacemaker takes over and Green LEDs flash.
5. Once the abnormal condition is removed the Paced output leads detect this change, the oscillator is reset and the Pacemaker stops functioning.
RESULT:
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Hence the working of a Pacemaker along with its various modules is studied.
Ex.No 14 ECG Heart rate alarm system with HRV
AIM:
To understand the various modules of an ECG heart rate alarm system with heart rate variability.
EQUIPMENTS REQUIRED:
a) ECG Amplifier
b) QRS Filter
c) QRS Detector
d) Refra Generator
e) Synch Generator
f) F to V Converter
g) High Alarm
h) Low Alarm
i) DVM
j) HRV
k) Audio Buzzer
l) Battery
m) Charger
n) Electrodes
THEORY:
Heart rate is the number of heartbeats per unit time - typically expressed as beats per minute (bpm) .The measurement of heart rate is used to assist in the diagnosis and tracking of medical conditions. The R wave to R wave interval (RR interval) is the inverse of the heart rate. Normally, heart rate varies depending on the person's age and activity. The term "arrhythmia” refers to abnormally fast or slow heart rates and to irregular heart rhythms. Arrhythmias are
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usually diagnosed with an electrocardiogram (ECG). A heart rate that's faster than normal is called tachycardia. Tachycardia may reduce the heart's pumping ability and may require treatment. Sometimes tachycardia is due to an abnormality of the heart's electrical circuits, while other times it may be due to abnormally high adrenaline levels as seen, for example, after surgery. A heart rate that's slower than normal is called bradycardia. Bradycardia may be associated with certain congenital heart defects or may develop by itself before birth or after heart surgery. In some more serious cases if the heart rate is very slow, an artificial pacemaker may be needed. Heart rate variability (HRV) is a physiological phenomenon where the time interval between heart beat varies. HRV analysis is based on measuring variability in heart rate; specifically, variability in intervals between R waves - “RR intervals”. These RR intervals are then analyzed by spectral or some other form of mathematical analysis (e.g., chaos, wavelet theories).
BLOCK DIAGRAM:
BLOCK DIAGRAM DESCRIPTION:
ECG Amplifier
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ECG has amplitude of only about 1 mV, so to detect it an amplifier is needed. The ECG amplifier used here has a Gain of 1000 and CMRR of more than 80dB.
QRS Filter
Heart rate is the number of heartbeats per unit time - typically expressed as beats per minute (bpm). The R wave to R wave interval (RR interval) is the inverse of the heart rate. Hence a QRS filter is used to selectively filter the QRS wave. The QRS filter used here is a Bandpass Filter having
limits from 22Hz to 45Hz with a gain of 10.
QRS Detector
With the presence of an R wave, the QRS detector will generate a pulse. The input voltage is 1V Pk –Pk and output voltage is 5V. It has a frequency range of 15-30Hz.
Refractory Generator
The refractory generator is a non-retrigerrable monostable mutivibrator which generates a 250msec delay following an output pulse or a sensed R-wave during which the amplifier in the sensing circuit will not respond to outside signals. The input is a pulse of 0-5V (min 1msec) and output is pulse of 0-5V (250msec).
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Synch Generator
The synch generator generates a synchronous pulse with the incoming wave. The input is a pulse of 0-5V (< 200msec) and output is pulse of 0-5V (100msec).
HRV Module
It is the analysis of variations in the instantaneous heart rate time series using the beat to beat RR intervals is known as heart rate variability analysis. These RR intervals are then analyzed by spectral or some other form of mathematical analysis (e.g., chaos, wavelet theories). Such mathematical analysis generates multiple parameters; typically 20-30. HRV analysis has been shown to provide an assessment of cardio vascular diseases.
F-V Converter
The output of synch generator is frequency hence it is converted into voltage for detection of an increase or decrease of the heart rate. The input pulse width is of 100msec and output voltage is 1V/100 pulse per minute.
High Alarm & Low Alarm
The modules high alarm and low alarm are calibrated at a certain rate. These are analog comparators which compare the incoming signal to the fixed rate. The high alarm and low alarm modules are calibrated using DVM at a fixed rate of 90 pulses/min and 60 pulses/min respectively. In case of the value being more than/less than the fixed rate the high alarm/low alarm triggers the audio buzzer. The input and output for High Alarm is 0-2.5V DC and 0-5V Pulse (100msec) respectively. The input and output for Low Alarm is 0-2.5V DC and 0-5V Pulse (100msec) respectively
DVM
The output of the High Alarm and Low Alarm is given to the DVM which gives the numerical display of the voltage.
Audio Buzzer
The audio buzzer generates an audio beep when the heart rate increases or decreases beyond the specified limits. The frequency of buzzer is 1 kHz and minimum input voltage is 5V.
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PROCEDURE:
1. Connect the modules as per the block diagram.
2. Connect the electrodes to the subject.
3. Switch ON the battery.
4. Observe the heart rate on the DVM.
5. If the heart rate deviates from the normal range the audio buzzer generates an audio beep.
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RESULT:
Thus we understand the various modules of an ECG heart rate alarm system with heart rate variability.
Ex. No 15 EMG Biofeedback with NCV
AIM:
To understand the EMG system and also calculate the Nerve Conduction Velocity
I) a) EMG BIOFEEDBACK:
EQUIPMENTS REQUIRED:
a) EMG Amplifier
b) High Pass Filter
c) General Amplifier
d) Audio Amplifier
e) Level Indicator Linear
f) Electrodes
g) Battery
h) Charger
THEORY Electromyography (EMG) is a test of a muscle’s electrical activity. It is used to test how a muscle responds to signals from the nerves responsible for muscle movement, called motor nerves. An EMG may also include a test of how fast the motor nerve conducts impulses. This is
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called a nerve conduction study (NCS) or nerve conduction velocity (NCV) test. Nerve Conduction Velocity (NCV) measures the speed of conduction of impulses through a nerve. The impulses being measured are artificially supplied by a stimulating electrode placed on the skin over the nerve. Electrical activity in the nerve being stimulated is measured by recording electrodes placed on the skin at various distances from the stimulating electrode. The distance between the stimulating and recording electrodes and the time taken for an electrical impulse to travel between the electrodes are used to calculate the nerve conduction velocity. Nerve conduction tests have two parts – testing motor and sensory nerve testing. Nerve conduction velocity studies are performed to evaluate and document a variety of sensory and motor neuropathological conditions in patients with a suspected diagnosis of nerve dysfunction. Nerve dysfunction can be manifested in decreased signal amplitude, slowed conduction velocity or increased latency. Proximal and distal nerve segments may be tested separately to help identify and localize the cause of the patient’s condition. Additional tests are sometimes used to evaluate the results of treatment. Although the stimulation of nerves is similar with all NCV studies, the characteristics of motor, sensory, and mixed NCS are different.
• Motor NCV studies are performed by applying electrical stimulation at various points along the course of a motor nerve while recording the electrical response from appropriate muscle. Response parameters include amplitude, latency, configuration, and motor conduction velocity.
• Sensory NCV studies are performed by applying electrical stimulation near a nerve and recording the response from a distant site along the nerve. Response parameters include amplitude, latency, configuration, and sensory conduction velocity.
BLOCK DIAGRAM:
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BLOCK DIAGRAM DESCRIPTION:
EMG Amplifier
The amplitude of the EMG signal depends upon the type and placement of electrodes used and the degree of muscular exertion. Generally EMG signals range from 0.1 to 0.5mV which is a weak signal hence it has to be amplified. This amplification is done by the EMG amplifier. Here the gain of the EMG amplifier is 1000 and the output is1 V pk to pk per mV of input. High Pass Filter
A high-pass filter, allows high frequencies well but attenuates frequencies lower than the filter's cutoff frequency. The actual amount of attenuation for each frequency is a design parameter of the filter. It is sometimes called a low-cut filter. Here the HPF has a cut off frequency of 70Hz and a Minimum input voltage 1V Pk to Pk Audio Amplifier
Audio amplifier amplifies low power audio signals to a required level. Audio amplifier used in this application has a frequency range of 0-10KHz.
Level Indicator Linear
The level indicator displays the level of contraction of the muscle.
PROCEDURE:
1. Connect the modules as per the block diagram.
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2. Switch ‘ON’ the battery 3. Connect the subject to EMG amplifier through Ring electrodes. 4. Observe the output in the level indicator.
I) b) EMG NERVE CONDUCTION VELOCITY
EQUIPMENTS REQUIRED:
a) Monostable multivibrator. b) Amplitude control c) High voltage generator d) EMG amplifier e) High pass filter f) Charger g) Battery
BLOCK DIAGRAM:
BLOCK DIAGRAM DESCRIPTION:
Monostable multivibrator
A monostable multivibrator is an electronic circuit used to implement a variety of simple two-state systems such as oscillators, timers and flip-flops. In the monostable multivibrator one of the states is stable, but if the other is not then the circuit will flip into the unstable state for a determined period, but will eventually return to the stable state. Such a circuit is useful for creating a timing period of fixed duration in response to some external event. This circuit is also known as a one shot multivibrator.
Amplitude control
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The amplitude control controls the amplitude of the triggering pulse from the monostable mutivibrator.
High voltage generator
For the calculation of nerve conduction velocity an external high volt stimulus is required which is provided by the high voltage generator that produces an output voltage of 100V.
EMG Amplifier
The amplitude of the EMG signal depends upon the type and placement of electrodes used and the degree of muscular exertion. Generally EMG signals range from 0.1 to 0.5mV which is a week signal hence it has to be amplified. This amplification is done by the EMG amplifier. Here the gain of the EMG amplifier is 1000 and the output is1 V peak to peak per mV of input.
High Pass Filter
A high-pass filter, or HPF, allows high frequencies well but attenuates frequencies lower than the filter's cutoff frequency. The actual amount of attenuation for each frequency is a design parameter of the filter. It is sometimes called a low-cut filter or bass-cut filter. Here the HPF has a cut off Frequency 70Hz and a Minimum input voltage 1V Pk to Pk. PROCEDURE:
1. Connect the modules as per the block diagram. 2. Connect the ring electrodes to the subject. 3. Give the stimulus using the electrode of the high voltage generator to the subject’s elbow 4. The settings for the DSO are
Trigger: External Edge: Rising Edge Mode: Normal Mode
5. Press trigger switch and observe the waveform on the DSO. 6. Calculate nerve conduction velocity by measuring distance between stimulator electrodes
and amplifier electrode and measuring time from oscilloscope reading. Nerve conduction velocity = distance /time.
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RESULT:
Hence the working of EMG Biofeedback System and calculation of Nerve Conduction Velocity is understood and performed.