Design a simple apnea detection system

Design a unreserved apnea staining brassCHAPTER 11.1 INTRODUCTIONAIMThe aim of the project is to design a simple apnea sight system with an fear and to classify the type of apnea identified victimization LabVIEW.1.1.1 Normal Respiratory EventRespiration is the phenomenon of supplying group O to the tissues and removing the snow dioxide from the tissues. External internal ventilation is the change of deepen of gases between the lungs and atmosphere. Internal respiration is the process of gas exchange in the tissues. The balance between the do using and excretion of these gases in personal credit line atomic number 18 maintained as existent activity. During inspiration the level of blood in oxygen increases and it decreases during exhalation. Chemoreceptors be the sensational receptors in the blood stream that senses the level of oxygen and carbon dioxide in blood ,and sends distinguishs to the brain. so the brain totally(prenominal)ows the opening of larynx and vo cal cords, fol firsted by the expansion of ribcage and diaphragm muscles. The chest cavity enlarges to allow the inflow of oxygen into the lungs thus terminusing in inhalation process. Similarly the chest cavity occludes during the process of exhalation and expels the carbon dioxide from lungs. More of oxygen inflow results in upper limit tidal mess and a characteristic respiratory flow. Fig 1.1 shows the convention respiratory presage with respiration rove of 12 jots per time of day.1.1.2 ApplicationsSleep depth psychologyPolygraphyPulmonary functionStress testSportsSudden Infant dying Syndrome (SIDS)1.1.3 Respiration Signal SpecificationsAmplitude 2-200mVFrequency wave draw-0 150HzRepetition frequence- 20 cycles per minute (adults) cytosine cycles per minute (neonates)1.1.4 Respiratory MeasurementsRespiration rateTidal tidy sumApneas preventative apnea rudimentary apneaHypopneaTachypneaBradypneaApnea indexAlso several correlations between EEG, paradoxical quiet s leep, apneas, quiet sleep, non-quiet sleep and de-saturations. 1.2 APNEA AND ITS TYPESApnea is the cessation of breathing during sleep which may top the arrest of the heart and circulation in several clinical turn onuations such as head injury, drug overdose, anesthetic agent complications and obstructive respiratory diseases. Apnea may to a fault get in premature babies during the starting line weeks of life because of their immature vile system. If apnea persists for a prolonged period, brain function rump be seriously damaged. in that locationfore, affected roles suffering from apnea require close and constant observation of their respiratory activity. Apnea admonishers are particularly useful for superintending the respiratory activity of premature infants. at that place are three types of sleep apnea. They areObstructive apnea substitution sleep apneaMixed or multiform sleep apnea1.2.1 Obstructive Sleep ApneaIndividuals with corpulency referable to low muscle t bingle and soft tissue about the agate lineway give rise to a narrowed airway ,so they are at high risk of obstructive sleep apnea. The elderly sight are more likely to suffer from OSA than young hoi polloi because of their fodder habits, smoking and alcoholic life style. Men are more typical sleep apnea sufferers when compared to women and children.The risk of OSA rises with increasing body bur whence, age, high cholesterol, sinus problems, and in addition, affected roles with diabetes have up to three times the risk of having OSA compared to an former(a)(a)(prenominal)s. Loudsnoring, rest slight sleep, and sleepiness during the daytime are several(prenominal) of the common symptoms of OSA. Diagnostic tests include homeoximetryorpolysomnographyin a sleep clinic. Treatment includes CPAP apparatus that gives invariable positive airway wedge in order to expand their narrowed nasal pathway1.2.2 Central Sleep ApneaWhen the brains respiratory control centers are imbalanced during sleep, it results in utter(a) interchange sleep apnea , in addition called as Cheyne-Stokes respiration. In this type of apnea the brain pauses to gun trigger the respiratory activity for about 30 seconds and triggers when it realizes that the patient suffocates for oxygen. The sleeper do not breathe for a certain period, during which there are no chest movements and no effort by the patient. Brain does not expecterbalance immediately with a neurological feedback to make the respiratory rate change surface. There is a swing between apnea and hyperpnea in order to compensate the compulsion for oxygen. After an apnea episode the hypoxia condition is reduced by breathing speedy and absorbing more oxygen. Central sleep apnea may be payable to hypertension, excess stress,and neuronal damage.In most of the cases CSA is treated with medications while some aim surgery. Fig.1.3 shows Central Sleep Apnea.1.2.3 Mixed Sleep ApneaMixed sleep apnea is a combination of obstructiv e and central sleep apnea . It is similarly called as complex sleep apnea.When obstructive sleep apnea syndrome is terrible and longstanding, some episodes of central apnea civilise during the course of sleep. though the exact mechanism of the loss of central respiratory drive during sleep in OSA is unknown it is most commonly link up to acid-base and CO2feedback malfunctions originating fromheart failure. Complex sleep apnea has been described by researchers as a divers(prenominal) dimension of sleep apnea. Patients with complex sleep apnea when treated with positive airway gouge for OSA was observed to exhibit persistent central sleep apnea. In sleep-disordered breathing there is a collection of diseases and symptoms relating to body mass, cardiovascular, respiratory, and occasionally, neurological disfunction that have a synergistic effect. 1.2.4 HypopneaHypopnea refers to a transient reduction of airflow (often while asleep) that lasts for at least 10 seconds, shallow bre athing, or an abnormally low respiratory rate. Breathing that is shal cut down or slower than normal. Hypopnea is distinct from apnea in which there is no breathing. Hypopnea comes from the Greek roots hypo- (meaning low, chthonic, beneath, down, below normal) and pnoe (meaning breathing). Hypopnea is less severe than apnea (which is a more complete loss of airflow). It may likewise result in a decreased amount of air movement into the lungs and feces cause oxygen levels in the blood to drop. It more commonly is collectible to partial obstruction of the upper airway1.2.5 TachypneaTachypnea means elevated respiratory rate. In some situations, this might be usual, for example when climbing a flight of stairs. In disease it is indicative of problems with oxygenation. It occurs when the patient is breathing very(prenominal) hard to compensate for the higher than usual PCO2. When the patient is tachypneic it is important to sit him up in bed. In tachypnea the tidal volume is decreas ed, the minute volume may be the akin because the respiratory rate is increased. Decreased tidal volume leave have bad consequences for the patient because a corporation of energy is being spent on moving dead air space which does not help oxygenate the interior of lungs where gas exchange takes place. 1.2.6 BradypneaThis is a slow respiratory rate which is seen in the post anesthetic or sedated patient. Bradypnea is also seen in patients who have taken overdoses of barbitu rank and/or hypnotics. Bradypnea with a respiratory rate of more than ten breaths may correct itself as the patient recovers from the anaesthetic gases. Sometimes, in bradypnea, the patient compensates by increasing the tidal volume thereby the blood gases and oxygen saturation remain stable.Fig 1.6 shows bradypnea with respiratory rate 8b/min.1.3 IMPEDANCE PNEUMOGRAPHYImpedance pneumography is another practical method to monitor the breathing of the patient. The technique also enables the simultaneous monitor of the heart rate and respiration. This has certain inherent dis benefits. One is that the placement of the electrodes is very critical and other is cardiovascular artifact. This results from the manoeuver detection of movement between the electrodes because of the cardiovascular system, rather than due to respiration. Apnea monitors need to be designed to reject this artifact. The principle of resistor pneumography is to choke off a authorized through the chest between two electrodes, and from the ending voltage to cook the changes in chest impedance which occur during respiration. It has been proposed that the impedance change occurring in respiration is directly proportional to the change in volume of air contained in the thorax, and therefore reflects tidal volume. The technique kit and caboodle by applying a current of approximately 10 microamperes to 1milliamperes with a frequency of 30-100 kilohertz to the thorax. This frequency is high enough to avoid stimulation o f tissues, electrode polarisation and excessively high skin impedance. The electrodes are always maintained with trifling potential difference which makes it possible to gradation the impedance of a central core of thoracic tissue.Thus these impedance changes are obtained as thoracic changes that gives inside information about respiration.Fig 1.7 shows the occlude diagram Of impedance pneumography technique.1.4 LABVIEW AND ITS APPLICATIONSLabVIEWLaboratory Virtual instrumentation Engineering Workbench.LabVIEW is a graphical programming environment use by millions of engineers and scientists to develop sophisticated measurement, test, and control systems using intuitive graphical icons and wires that check a flowchart.Biomedical ApplicationMultisim Simulation with ancardiogramAmplifierNoninvasive Blood blackjack (NIBP) AnalyzerAnalog ECGGeneratorHeart Rate Variability (HRV) AnalyzerECG Feature ExtractorOnline Bio augur Noise Reduction information ladBio subscribe LoggerOBJECTIV ESTo collect the respiratory entropybaseTo study the apnea characteristicsTo detect and classify apneaTo achieve upper limit accuracyTo design a respiratory channelize simulation systemCHAPTER 2LITERATURE SURVEY2.1 RESPIRATION DATA ACQUISITION, CONVERSION AND vaunt SYSTEM2.1.1 MethodologyRespiration info is acquired and converted into a serial publication of pulses, the frequency of which is related to the respiration rate of the data measured . The issue pulses switch a timing device on and off , and the mean(a) time of a respiration cycle is then converted and displayed as respiration rate. The timing device includes a means for delaying a first fruit pulses before beginning the sampling period and registering a count of clock pulses for a condition number which represents the time period of a second specified number of the make pulses occurring subsequently to the first specified number of output pulses.2.1.2 destination This instauration relates to an acquisition un it for acquiring data relating to one or more physiological variables from a patient. Displaying the data digitally and, upon operator approval, recording the data in an internal memory. Further, the blind relates to a data storage system responsive to data stored in an acquisition unit for a display presentation. 2.2 regularity AND APPARATUS FOR ascertain A RESPIRATIONPARAMETER IN A MEDICAL DEVICEShrivastav, Maneesh, Cho, Yong K., Bennett, Tommy D., Erickson, Mark K., Greenhut, capital of Minnesota E., Kleckner, Karen J., Sperling, Charles P., Corey, Robert A.2.2.1 MethodologyA pressure sensing element senses pressure signalises, and a signal processor, coupled to the pressure sensor, receives the sensed pressure signaland generates interchangeable sample points. A microprocessor continuously adjusts a breath detection threshold in solution to the generated sample points to generate a current familiarized breath detection threshold.Then it compares a current generated sampl e point to the current adjusted breath detection threshold, suspends the continuous adjusting of the breath detection threshold.Then the microcontroller sets the breath detection threshold equal to the most current adjusted breath detection threshold generated prior to the suspending, and determines the respirationparameter in response to a study of a next generated sample point to the set breath detection threshold.2.2.2 ConclusionThis invention relates to a method of acquisition of respiratory signal using pressure sensor and displays that respiration parameter using a microcontroller.2.3 METHOD AND APPARATUS FOR monitorING RESPIRATIONRymut, Russell, Slotty, Eric, Kini, Narendra2.3.1 MethodologyThe apparatus includes a piezoelectric claim which converts acoustical waves generated by the patients respiration activity into electrical signal output. The piezoelectric film sensor placed in the capable can be use to monitor the respiration of a patient by correlating the sound gen erated in the patients airway with respiratory activity. Further, the data generated by the sensor may be provided analyzed by a patient monitor to diagnose respiratory conditions and display it.2.3.2 ConclusionThis invention relates to a method and apparatus for monitoring and quantitatively measuring the respiration of a patient , particularly, using a flexible piezoelectric film sensor.2.4 APNEA MONITORGuixian Lu2.4.1 Methodology1. A conductive gumshoe range of mountains is used to measure the chest volume changes. It is not suitable for OSA. In that case a differential gas flow sensor is used.The output of the sensors is amplified and then federal official to a re-shaper.3.The re-shaper re-shapes the signal and generates pulses to trigger the counter.4.The counter triggers the horrify circuit if the count exceeds a predetermined threshold.2.4.2 ConclusionFor adults one rubber string is enough. But for infants, the frequency of the body movement is measured. So an superfluou s rubber string with motion detector is needed. The gas flow sensor is reliable and sensitive. A buzzer is used to give misgiving.2.5 DESIGN AND carrying into action OF A PROGRAMMABLE APNEA MONITORING SYSTEMMustafa avuolu, Osman Eroul , Ziya Telatar2.5.1 MethodologyRespiratory signal is perceived by a thermal sensor.The signal is amplified and then fed to the microcontroller.The output of microcontroller is pitchred to the computer and the relation between ECG and the signal is evaluated.An alarm system is also provided to indicate apnea2.5.2 ConclusionThe system is capable of detecting apnea, warns during the apnea and transfers the respiration signals to the computer. Finally,categorization of the apnea intervals is done to generate a real-time histogram of their frequency and while which makes possible to investigate the relations between the EEG, ECG or other physiological signals and the respiratory patterns.2.6 APNEA ALARM SYSTEMS2.6.1 MethodologyA crib or bed with piezo e lectric or strain gauge transducer attached to each leg is used to acquire the movement of infants.Whenever the infant is breathing there is a sport in the force distibution in the foam mat, so the vertical force apply on the frame of the crib also varies,which is captured by the sensors attached to the leg of the crib.These sensors convert the force into an electrical output signal and gives it to a summing amplifier to provide a summed output signal from all four legs.The summed output is given to a microcontroller where it is compared with the patients physical parameters to give an alarm if there is apnea detected using a buzzer or jiffy light.2.6.2 ConclusionThis apparatus helps to detect apnea in infants who can be monitored even at home instead of hospitals.This alarm system is more favourable to babies as it does not attach any sensor to infant s body.Mainly used to detect expiration due to apnea (crib expiry or cot death ) very common in premature infants.2.7 APNEA MO NITOR DATA SYSTEM2.7.1 MethodologyAn apnea monitoring system along with a portable data storage cartridge is presented.Respiration is monitored through the electrodes dictated on the thoracic cavity of the patient.Detected events are compared with respiration rates and when it is exceeded the signal is transmitted to audio and visual alarms indicating apnea.In addition to that a poratable data storage cartridge is provided which has enough memory to store all monitored events and waveforms that can be transferred to computer.2.7.2 ConclusionThis invention not only helps to monitor also contains a portable cartridge,that can be easily carried or mailed,which makes it time efficient and cost efficient method to store data.Another advantage is that the cartridge is replaceable,which provides an unlimited amount of memory space that helps in transfer of data.2.8 A MODEL abstract OF ARTERIAL OXYGEN DESATURATION DURING APNEA IN PRETERM INFANTSScott A. Sands, Bradley A. Edwards, genus Va nessa J. Kelly, Malcolm R. Davidson, Malcolm H. Wilkinson, Philip J. Berge2.8.1 MethodologyIndependent influence of clinically relevant cardiorespiratory fators on the desaturation of arterial oxygen during apnea is determined using a two-compartmental lung-body mathematical regulate which incorporated realistic oxygen stores and gas exchange dynamic uninflected solutions were derived for arterial oxygen desaturation to quantify the importance of cardiorespiratory factors on arterial oxygen desaturation such as cardiac output, lung volume, metabolic oxygen employment, pre-apneic ventilation, blood oxygen affinity, hemoglobin content and blood volumeThe model summary reveals that lung volume, hemoglobin content, cardiac output, pre-apneic ventilation exerts a unique effect on arterial oxygen desaturation throughout the time-course of desaturation and metabolic oxygen consumption is uniformly influential throughout the process.Infants with elvated metabolic needs and low lung volu me and those with anemia, cardiac dysfunction or hypovolemia which are common in prematurity are at heightened risk of rapid and profound arterial desaturation during apnea. 2.8.2 ConclusionA mathematical framework for quantifying the relative importance of key cardiorespiratory factors on the rate of arterial oxygen desaturation during apnea with particular relevance to preterm infants is provided. for each one of the factors examined has a signature influence on the trajectory of desaturation, providing quantitativeinsight into the causes of rapidlydeveloping hypoxemia during apnea have been demonstrated.2.9 preventive quietude APNEA AS A RISK FACTOR FOR STROKE AND expiration H. Klar Yaggi, M.D., M.P.H., John Concato, M.D., M.P.H., W falsify N. Kernan, M.D., Judith H. Lichtman, Ph.D., M.P.H., Lawrence M. Brass, M.D., and Vahid Mohsenin, M.D. 2.9.1 Methodology1.In this study patients underwent polysomnography and subsequent events like rap and death are verified.2.The diagnosi s was establish on apnea-hypopnea index of the patients.Patients with apnea-hypopnea index of less than 5 served as a comparison group.3.Proportional hazards analysis was used to determine the independent effect of OSA syndrome on the outcome of stroke or death from any cause.4.The mean apnea-hypopnea index for the patient with syndrome is 35 while the same for patients in the comparison group is 2.5.After adjustment for age,sex, diabetes mellitus, smoking status, alcohol consumption status, body-mass index, hypertension, the OSA syndrome retained a statistically significant association with stroke or death.2.9.2 ConclusionThe obstructive sleep apnea syndrome significantly and severely increases the chance for stroke or death from any cause. The increase for the risk of stroke or death due to OSA syndrome is independent of the other risk factors,including hypertension.2.10 AN ECONOMIC ANALYSIS OF CONTINUOUS POSITIVE AIRWAY PRESSURE FOR THE TREATMENT OF OBSTRUCTIVE calmness APNEA-HY POPNEA SYNDROMEHelen L. A. Weatherly, Susan C. Griffin, Catriona Mc Daid, Kate H. Dure, Robert J. O. Davies, John R. Stradling, Marie E. Westwood and Mark J. Sculpher.2.10.1 MethodologyThis study reports on the cost-effectiveness of the continuous airway-pressure(CPAP) compared with the dental devices and lifestyle advice to the patient. The Markov model compared the interventions over the patients life expectancy.The primary measure for cost-effectiveness was the incremental cost per quality adjusted life-year(QALY) gained for every patient.On further analysis, CPAP was associated with higher costs and QALYs compared with dental devices and lifestyle advice.The result of analysis was that the fortune that CPAP is more cost-effective than dental devices or lifestyle advice at a threshold value of 20,000 per QALY was 0.78 for men and 0.80 for women.2.10.2 ConclusionThis model suggests that CPAP is cost-effective compared with dental devices and also the lifestyle advice for adults with moderate or severe symptomatic Obstructive Sleep Apnea -Hypopnea Syndrome are at the cost-effectiveness thresholds used by NICE. This start outing is reflected in the NICE guidance.CHAPTER 3METHODOLOGY3.1 EXISTING METHODSSeveral contactless methods are accessible for monitoring the respiration of infants. The most successful apnea monitors to-date been mattress monitors. These instruments rely for their operation on the fact that the process of breathing redistributes an infants weight and this is detected by some form of a pressure sensitive pad or mattress on which infant is nursed. The mattress, in its simplest form, is a multi-compartment air bed, and in this case the weight redistribution forces air to flow from one compartment to another. The air flow is detected by the chill effect it produces on a heated thermistor bead. Though the technique is simple, the main disadvantage with the air mattress is the short-term sensitivity variation and the double throwawaying eff ect when inspiration or expiration produces separate cooling of the thermistor. Alternatively, a capacitance type pressure sensor in the form of a thin square pad is usually placed under or slightly above the infants head. Respiratory movements produce regular pressure changes on the pad and these alter the capacitance between the electrode plates incorporated in the pad. The capacitance change is measured by applying a 200 kHz signal across the electrodes and by detecting the current flow with a phase-sensitive amplifier. The disadvantage of this method is that the system is much too sensitive to people moving nearby and thus an electrically screened incubator is essential for the infant.3.1.1 METHOD ADOPTEDThis project is based on impedance pneumography method. Impedance pneumography is one of the practical methods to monitor the breathing of the patient. The technique also enables the simultaneous monitoring of the heart rate and respiration. This has certain inherent disadvantag es. One is that the placement of the electrodes is very critical and other is cardiovascular artifact. This results from the detection of movement between the electrodes because of the cardiovascular system, rather than due to respiration. Apnea monitors need to be designed to reject this artifact. So in this project the respiratory signal is considered to be acquired by using respiratory sensor. As there is no availability of sensor, respiratory signal is seized using our own designed impedance pneumography technique based circuit. Then this signal is given to microcontroller where apnea is detected and it then triggers an alarm. The mixed bag of apnea is also done using LabVIEW. In future respiratory sensor entrust be designed and the respiratory signal will be acquired. Then this signal can be given to the microcontroller directly.3.2 RESPIRATORY SIGNAL make-believeThe respiratory signal simulation circuit consists of an excitation source and a constant current source circuit which gives a high frequency, low voltage and constant current signal. This constant current will be applied to the thorax of the subject. But due to the ethical issues the current is applied on the electrical resistivity circuit which acts as the thorax impedance. This circuit in turn gives a voltage signal. This voltage signal will be amplified by an instrumentation amplifier. The amplified signal will be fed to the LabVIEW for classification of normal and apnea signal and also types of apnea. Figure 3.2.1 shows the block diagram to simulate respiratory signal and the hardware design of the circuit3.2.1 EXCITATION stockThe wien bridge oscillator which produces 50kHz and 8 V jacket crown to peak signal is used as the excitation signal. The operational amplifier used in the circuit is LF351. The electromotive force gain of the amplifier must be at least 3. The input resistance of the amplifier must be high compared toRso that theRCnetwork is not overloaded and alter the requir ed conditions.The output resistance of the amplifier must be low so that the effect of external loading is minimized. Some method of stabilizing the bounteousness of the oscillations must be provided because if the voltage gain of the amplifier is too small the want oscillation will decay and if it is too large the waveform becomes misrepresented3.2.2 CONSTANT CURRENT SOURCEThe constant source circuit is used to generate a 4mA constant current to be applied on the resistance circuit. CL100 and CK100 transistors are used in this circuit and these are npn and pnp diametric transistors. The base emitter on voltage of these transistors is 0.9V. The collector current can be found by using the formula, Ic= (Vcc-Vbe)/Rc Where Vcc-Supply voltage Rc-Collector Resistance Vbe-Base emitter on voltage 3.2.3 PHANTOM MODEL The model consists of four resistors of 500 ohms which mimics the thoracic resistance.3.3 DATA COLLECTIONTo know about characteristics of normal respiration and apnea their corresponding signals were essential. So 40 respiration data sets with 100 sample determine in each data set were collected from PHYSIONET -PHYSIOBANK ATM. Among these 20 were normal data sets obtained from SLEEP HEART HEALTH STUDY POLYSOMNOGRAPHY DATABASE (SHHPSGDB) while the other 20 were apnea data sets obtained from UCD SLEEP APNEA DATABASE (UCDDB). In Apnea data sets 10 belonged to Central Sleep Apnea and remaining 10 to Obstructive Sleep Apnea. Each data set contained 100 samples whose units are volts(V).They were recorded for 100seconds.So on plotting each data we get time in X-axis and volts in Y axis. 3.4 CLASSIFICATION OF APNEA victimisation RESPIRATION RATEInput data which contains 60 samples each. Normalizing of the signal by squaring the signal. Extraction of maximum peak for every 5 samples.Display of respiratory cycles. If the peak value is greater than 6V it will be counted as normal respiratory cycle. If the count is between 10 and 20 the signal will be having no rmal respiratory rate. If the count is less than 10 the signal will be classified advertisement as bradypnea. If the count is greater than 20 the signal will be classified as tachypnea As the parameter of respiratory rate alone is not enough for classifying the types of apnea the statistical parameters are cypher and then signals are classified using LabVIEW.FLOWCHART3.5 CLASSIFICATION OF APNEA apply STATISTICAL PARAMETERSThe signal data was imported from a spread tag into labview using READ FROM SPREADSHEET block in labview. Then signal was plan as a graph using WAVEFORM CHART block. The data cannot be manipulated directly so the transpose of the data is taken to find the statistical parameters using TRANSPOSE ARRAY block. Now using the STATISTICS block the signals various parameters like arithmetic mean, median, mode, maximum peak, minimum peak, range, standard divergency variance, and rms value are found and recorded. Considering the range and mean of the signal it can be c lassified as its respective type. Give the upper and (or) lower limit for range and mean. Now using AND operator the signal is classified when its condition are satisfied. When the signal s range is greater than 7 and its mean is less than 0.1 it is normal. When the signal s range is lesser than 6 and its mean is greater than 0.21 it is abnormal. When the signal s range lies below 3.0 it is obstructive. When the signal s range lies between 3.1 and 6.99 it is central.FLOWCHARTCHAPTER 44.1 RESULTS AND DISCUSSION4.1.1 computer hardware ResultsOutput from the excitation source (wein bridge oscillator) was checked in MULTISIM and then implemented using hardware. On applying the constant current to a resistance network that imitates human thoracic impedance , the current varied to a greater extent because of loading effect. The same problem will occur even when the patient is connected to the high frequency, low voltage, constant current module. Also, due to ethical issues the constant cu rrent generated cannot be given to the patient directly. So monitoring of real time data could not be done using the hardware design. Hence ,the idea of respiration signal simulation was dropped and offline data were collected from respiration databases for further classification.4.1.2 Normal and Apnea DataTo know about characteristics of normal respiration and apnea their corresponding signals were essential. So 40 respiration data sets with 100 sample values in each data set were collected from PHYSIONET -PHYSIOBANK ATM. Among these 20 were normal data sets obtained from SLEEP HEART HEALTH STUDY POLYSOMNOGRAPHY DATABASE (SHHPSGDB) while the other 20 were apnea data sets obtained from UCD SLEEP APNEA DATABASE(UCDDB).The Resulting plot for each type of respiration signal is plan below. The following figure shows the normal respiration data plotted for 100 samples with time in x-axis and amplitude in y-axis with a maximum peak to peak voltage of 8V and 24 respiration cycles for 100s econds. The following figure 4.4 shows Ce