report final.pdf

VISVESVARAYA TECHNOLOGICAL UNIVERSITY
"Jnana Sangama" Belagavi- 590018
“DESIGN OF LOW-COST MECHANICAL
VENTILATOR FOR COVID-19 PANDEMIC”
A project report submitted in partial fulfillment of the requirement for the
award of Degree of
Bachelor of Engineering
in
MECHATRONICS
Submitted by
G H SIRISHA 1VE18MT006
PRASAD SAPATE 1VE19MT403
SOWMYA S 1VE19MT404
SUSHANT BANAPATTI 1VE19MT405
Under the Guidance of
Mr. SURESH D B
Assistant Professor
Dept. of MT, SVCE
Bengaluru
Department of Mechatronics
Sri Venkateshwara College of Engineering
(Affiliated to VTU, Belagavi, NBA* Accredited, Approved by AICTE New Delhi)
Kempegowda International Airport Road, Vidyanagar, Bengaluru – 562157
2021 – 2022

SRI VENKATESHWARA COLLEGE OF ENGINEERING
Vidyanagar, Bengaluru - 562157
Department of Mechatronics
CERTIFICATE
This is to certify that the Project Work entitled
“DESIGN OF LOW-COST MECHANICAL VENTILATOR FOR
COVID-19 PANDEMIC”
Carried out by
NAME OF THE STUDENTS USN
SOWMYA S
SUSHANT BANAPATTI
1VE19MT404
1VE19MT405
In partial fulfillment of the requirements for the award of the Degree of Bachelor of
Engineering in Mechatronics of Viveshvaraya Technological University, Belagavi, during
the year 2021–2022. It is certified that all corrections/suggestions indicated for Internal
Assessment have been incorporated. The Project Report has been approved as it satisfies
the academic requirements in respect of Project Work prescribed for the said Degree.
Signature of the Guide Signature of the Program
Co-ordinator
Signature of the Principal
(Mr. Suresh D B) (Dr. Bharath V) (Dr. Nageswara Guptha M)
External Viva -Voce
Name of the Examiners Signature with date
1.
2.

ACKNOWLEDGEMENT
The euphoria and complacency of completing this technologically advanced project will not
be complete until I/we think all the people who have helped us in complete this enthusiastic
work. Submission of this project report marks a milestone in our academic career.
After years of schooling, there are lots of people who have helped us, either directly or
indirectly, in our achievements in life. It is a pleasure to acknowledge such people.
We would like to show our appreciation to our Chairman, Sri. V Muniyappa, our Chief
Executive Director, Dr. Shashidhar Muniyappa, and our Management for providing us with
the necessary equipment and assistance to complete this project.
Our deepest thankfulness goes to our principal, Dr. Nageswara Guptha M for his continuous
encouragement and support.
We would like to thank beloved Dr. Bharath V, Program Co-ordinator of the Mechatronics
Department for her encouragement and support.
Our deepest thankfulness goes to our project coordinators, Mr. Murugesh P D, Assistant
Professor, Department of Electrical and Electronics. We do consider ourselves privileged to
have had the opportunity to work under her guidance.
We wish to express our sincere appreciation for our committee members who took the time to
go through our project work. Mr. Suresh D B, Assistant Professor of the Mechatronics
Department and our internal guide. Who although remained a supportive person.
We would like to express our gratitude to Professors and Lab instructors of Department of
Mechatronics of their encouragement. Finally, we thank our parents who were on our side
whenever we needed them and the almighty whose blessings are always there.
ⅰ

ABSTRACT
The main idea behind the work is the open-source mechanical ventilator construction at low-
cost. In response to a worldwide scarcity of mechanical ventilators for treating COVID-19
patients, a company has developed a new type of ventilator that can be used to treat COVID-
19 patients. A low-cost, open-source mechanical ventilator will help alleviate this scarcity in
such places. Only commercially available spare components are used in the equipment
described here. In addition, a numerical approach for tracking the health of the patients' lungs
is demonstrated in this effort. The approach takes into account pressure data from the
inspiratory limb and informs doctors in real-time if the patient is in a healthy or unhealthy
state. The benefits of the derived mechanical ventilator were demonstrated in laboratory
experiments that mimicked healthy and unwell individuals.
ii

DECLARATION
We G H Sirisha, Prasad Sapate, Sowmya S, Sushant Banapatti, the students of Department
of Mechatronics, Sri Venkateshwara College of Engineering, hereby declare that the project
report entitled, “DESIGN OF LOW-COST MECHANICAL VENTILATOR FOR
COVID-19 PANDEMIC” has been carried out independently by under the guidance of Mr.
Suresh D B Assistant professor, Department of Mechatronics, SVCE, Bengaluru.
We declare that project report submitted is our own and is not submitted previously for the
degree at any other institute/university.
Date:
Place: Bengaluru
SOWMYA S 1VE19MT404
SUSHANT BANAPATTI 1VE19MT405
iii

CONTENTS
Chapter No. Contents Page No
ACKNOWLEDGEMENT i
ABSTRACT ii
DECLARATION iii
LIST OF CONTENTS iv
LIST OF FIGURS v
1 INTRODUCTION 1
2 LITERATURE SURVEY 7
3 PROPOSED WORK 11
3.1 Problem statement
3.2 Objective
3.3 Methodology
3.4 Flow chart
3.5 Circuit Diagram
3.6 Applications
3.7 Advantages
4 SOFTWARE AND HARDWARE 19
4.1 Software Requirements
4.2 Hardware Requirements
5 RESULT AND DISCUSSION 31
CONCLUSION 32
FUTURE SCOPE 33
REFERENCES 34
APPENDIX 36
ⅳ

LIST OF FIGURES
Fig. No TITLE Page No
1.3.1 Positive Pressure Ventilator (PPV) 4
1.3.2 Negative Pressure Ventilator (NPV) 6
3.3 Block Diagram of Mechanical ventilator 13
3.4 Flow Chart of Mechanical Ventilator 16
3.5 Circuit Diagram of Mechanical Ventilator 17
4.1.1 Arduino IDE Software 19
4.1.2 Blynk Application 20
4.2.1 Node MCU 21
4.2.2 Blood-Oxygen Sensor 23
4.2.3 DHT Temperature Sensor 24
4.2.4 L298 Motor Driver 26
4.2.5 DC Motor 27
4.2.6 LCD Display (16×2) 28
4.2.7 Ambu bag 29
4.2.8 Adaptor 30
v

Design of Low-cost Mechanical Ventilator for Covid-19 Pandemic 2021-2022
Dept. of MT, SVCE, Bengaluru Page 1
CHAPTER 1
INTRODUCTION
In the latter half of 2019, a previously unknown coronavirus was discovered in the Chinese
province of Wuhan. The virus, which was subsequently determined to be severe acute respiratory
syndrome coronavirus-2, also known as COVID-19, is the agent that is now causing a pandemic
all over the globe. According to the preliminary statistics from China, somewhere between 14 and
17 percent of hospitalized patients needed additional breathing assistance. Italy is notable for being
one of the first western nations to experience widespread sickness. An estimated 16 percent of
actively infected patients needed to be admitted to an intensive care unit due to hypoxic respiratory
failure caused by COVID-19, and their critical care facilities looked to be carrying an immense
weight as a result of the patients.
In the last several months, there has been an increasing demand for ventilators in the
treatment of patients who have COVID-19. As a result of this fact, there is now a ventilator
shortage all over the globe. The effects of this scarcity are disastrous, particularly for the
communities who are already struggling the most. Even well-equipped hospitals have developed
protocols for sharing the same ventilator between two patients. This is a questionable practice due
to the fact that it opens up the possibility of patients not only sharing their bacterial and viral load
with one another, but also of inadvertently causing one of the patients to experience unintended
harm. Researchers have begun a project to produce low-cost and open-source ventilators in an
effort to combat the global issue of a ventilator scarcity. This article makes a contribution to the
whole effort.
Researchers are in agreement that the use of mechanical ventilation may be detrimental to
one's lungs, leading to a condition known as ventilation-induced lung damage. Volutrauma and
atelectrauma are the two forms of injury that are seen most often. Volutrauma develops when
excessive ventilation causes distention of the airways and alveoli, which in turn leads to
overstretching of the lung parenchyma that corresponds to those structures. Volutrauma results in
an inflammatory response, which, in the long run, causes the alveolar walls to burst and results in
edema.
Atelectrauma, on the other hand, seems to be produced by inadequate ventilation;
inadequate ventilation enables alveolar units to collapse and reopen in a repeating, sequential
action, which may also lead to harm. The majority of studies advise practitioners to use mechanical
ventilation with positive end-expiratory pressure in order to reduce the risk of atelectrauma
(PEEP). After the publication of the foundational data in, PEEP rapidly evolved into a widely used
instrument for the prevention of atelectrauma. Recent research suggests that PEEP causes further
effects, such as inflammation and the production of edema in the lungs; nonetheless, the use of
PEEP to prevent lung injury remains controversial due to these results.

In spite of the fact that more work is required to get a comprehensive grasp of the mechanical
ventilation process, it is certain that mechanical ventilators are beneficial to patients who are
coping with acute respiratory issues.
1.1 PHYSIOLOGY
The lungs' primary role is to facilitate gas exchange through the process of oxygenation and
ventilation. The physiologic concepts of air flow, tidal volume, compliance, resistance, and dead
space are all involved in this phenomena of respiration. Additionally, arterial PaCO2, alveolar
volume, and FiO2 are also crucial elements to keep in mind. The amount of gas that enters the
alveoli and participates in gas exchange is called alveolar ventilation. A measure of how efficiently
carbon dioxide is expelled from the body is known as PaCO2 (partial pressure of carbon dioxide
in arterial blood). Volume of alveolar air per minute is referred to as alveolar volume. In ventilator
design and function, mechanical dead space is defined as the volume of gas breathed again as a
result of mechanical device use.
An endotracheal tube is needed to link the patient's natural airway to the ventilator in this
illustration. Image Positive-pressure ventilation requires additional steps to ensure that air does not
enter the esophagus or stomach due to anatomical differences among humans' pharyngeal,
laryngeal, and esophageal structures and the circumstances in which ventilation is required. A tube
is inserted into the trachea as the most usual procedure. Either an endotracheal tube can be placed
in the mouth or nose to allow for easy breathing, or an artificial opening in the neck can be made
to allow for easy breathing. Oropharyngeal or laryngeal mask airways, basic airway maneuvers,
and other options are also available. Non-invasive or negative-pressure breathing does not
necessitate the use of an airway adjunct.
Opioid pain medication is sometimes prescribed to adults and newborns who require
mechanical breathing. Mechanically ventilated infants, whether preterm or full term, do not require
opioid or sedative prescriptions on a regular basis. However, some infants who require mechanical
ventilation may require pain medication such as opioids. Clonidine is not known to be safe or
effective for use as a sedative in mechanically ventilated preterm and full term newborns.
To compute the next FiO2 and estimate the shunt fraction for an adult, it is simple to start
with 100% oxygen (1.00 FiO2). The estimated shunt fraction refers to the quantity of oxygen that
is not absorbed into the circulation. The alveoli in the lungs are where the exchange of oxygen and
carbon dioxide takes place in normal physiology. A shunt refers to any mechanism that inhibits
this gas exchange, resulting in lost oxygen inspired and the passage of un-oxygenated blood back
to the left heart, which ultimately supplies the rest of the body with deoxygenated blood. In the
presence of 100 percent oxygen, the shunting pressure is predicted to be 700 mmHg (measured in
millipascals, or PaO2). The shunt is 5% larger for every 100 mmHg difference. There should be
an investigation into what caused the hypoxia, such as mainstem intubation or pneumothorax, and
the patient should be treated accordingly if the shunt is greater than 25%. A positive end-expiratory

pressure (PEEP) should be employed to treat an intrapulmonary shunt if any of these problems are
not evident.
Other such causes of a shunt include:
1) Alveolar collapse from severe atherosclerosis might result in shunting.
2) Alveolar collection of non-gaseous material, such as pus from pneumonia, water and protein
from acute respiratory distress syndrome, water from congestive heart failure or blood from
hemorrhage.
1.2 MECHANICAL VENTILATOR
Medically, it refers to the use of a machine called a ventilator to give some or all of an individual's
breathing support. Mechanical ventilation aids in the delivery of oxygen and the elimination of
carbon dioxide by moving air into and out of the lungs. There are several reasons to employ
mechanical ventilation, including to protect the airway from mechanical or neurological causes, to
provide enough oxygenation, or to eliminate too much carbon dioxide from the body. In the
intensive care unit, patients who require mechanical ventilation are under the supervision of a
variety of medical professionals.
When a patient is undergoing surgery or is unable to breathe on their own because of a
critical illness, a mechanical ventilator is used to assist them in breathing. One end of an artificial
airway (a hollow tube) is inserted into the patient's mouth and the other ends are connected to the
ventilator via their main airway (the trachea). If an instrument is used to construct an airway inside
the trachea, mechanical ventilation is considered intrusive. An endotracheal tube or a nasotracheal
tube is used for this procedure. Non-invasive ventilation in awake patients is carried out by using
face or nasal masks, respectively.
In order to reduce the workload of breathing, a mechanical ventilator is employed. An
oxygen supply and carbon dioxide removal are ensured by the equipment. When breathing is
impaired due to a variety of conditions, this is a vital tool.
Air is drawn into the lungs by negative pressure ventilation whereas positive pressure
ventilation pushes air into the lungs through trachea and other airways. Mechanical ventilation can
take numerous forms, and as the technology has evolved, so has the nomenclature for each.

1.3 TYPES OF VENTILATORS
The two main types of mechanical ventilation include:
• Positive pressure ventilation: where air is pushed into the lungs through the airways.
• Negative pressure ventilation: where air is pulled into the lungs.
1.3.1 POSITIVE PRESSURE VENTILATION (PPV)
Positive pressure ventilation is a type of respiratory therapy that uses air or a mixture of oxygen
and other gases to give oxygen to the lungs. Until the machine supplying the mixture detects a
change in flow or pressure, or until the predetermined volume of gas has been given to mark the
end of a breath, the interalveolar pressure rises as gas enters the lungs. As a result of the alveolar
pressure buildup, which escapes into the less pressurized conductive airways, air is passively
expelled. To treat acute respiratory failure in poliomyelitis patients, a "negative pressure
ventilation" (PPV) machine was commonly utilized, which involved hermetically sealing the
patient's body inside a vacuum-producing "iron lung." The outbreak of polio in Copenhagen in
1952 and a lack of "iron lungs" prompted the introduction of PPV into clinical practice.
Fig.1.3.1: Positive Pressure Ventilator(PPV)
As shown in the above Fig.1.3.1. The Ventilator as a Whole For the design of modern positive-
pressure ventilators, the military's efforts during World War II largely influenced their
development. As safe endotracheal tubes with high-volume/low-pressure cuffs were created, these
ventilators took the role of iron lungs. During the polio pandemic of the 1950s in Scandinavia and
the United States, positive-pressure ventilators surged in popularity and were the beginning of
contemporary ventilation therapy. Patients with polio and respiratory paralysis who received 50
percent oxygen through a tracheostomy tube had a lower mortality rate. Because of this,

mechanical positive-pressure ventilators have become more and more prevalent in hospitals
around the country.
Using an endotracheal or tracheostomy tube, positive-pressure ventilators increase the
patient's airway pressure. Until the ventilator breath is extinguished, the positive pressure lets air
to enter the lungs. Passive exhalation occurs when the airway pressure decreases to zero and the
lungs and chest wall elastic rebound push the tidal volume out.
1.3.2 NEGATIVE PRESSURE VENTILATION (NPV)
Small, field-type, and large-format negative pressure mechanical ventilators are all available. The
cuirass, a shell-like item that is employed to produce negative pressure only to the chest, is the
most prominent design of the smaller devices. For biphasic cuirass ventilation, a high-pressure
oscillation pump and various-sized polycarbonate shells with multiple seals have been used in
recent years in the construction of this device. Patients with residual muscle function due to
neuromuscular diseases have primarily benefitted from its use. Hospitals in England with polio
wings like St. Thomas' Hospital in London and John Radcliffe in Oxford use the larger forms.
One of the first negative-pressure machines used for long-term ventilation is known as the
iron lung, or the Drinker and Shaw tank, invented in 1928 by J.H. Emerson Company and named
for its inventor, Drinker and Shaw The polio epidemic of the 1940s was a major factor in its
development and widespread use in the 20th century. Patients are encased in a tank that extends
up to their necks in a big, elongated machine. In order to expose the patient's face (and airway) to
the room's air, the patient's neck is sealed using rubber gaskets. In contrast to the diffusion of
oxygen and carbon dioxide between the circulation and pulmonary airspace, the movement of air
into and out of the lungs is necessary for the gas exchange process to occur. Spontaneous breathing
occurs when muscles of respiration create a negative pressure in the pleural cavity, which in turn
causes a pressure differential between outside air and the pressure inside the thorax to cause air to
flow, As show in the below Fig.1.3.2.
Fig.1.3.2: Negative Pressure Ventilator (NPV)

In the iron lung, the air is physically drained to create a vacuum inside the tank, resulting in a
negative pressure inside the tank. As a result of the decrease in intrapulmonary pressure caused by
the negative pressure, the chest expands, allowing more outside air to enter the lungs. Passive
exhalation occurs as the tank's pressure is equalized to the surrounding air pressure, resulting from
the chest and lungs' elastic recoil. This causes a pooling of venous blood in the lower extremities
because the abdomen expands with the lung, preventing blood from returning to the heart. The
patients are able to communicate and eat normally, and they can see the outside world through
strategically positioned mirrors. Some of them may survive for years in these iron lungs. It was
difficult to manage flow rates and ratios of inhalation and exhalation using a full-body
configuration. This design also resulted in a buildup of blood in the lower extremities.

CHAPTER 2
LITERATURE REVIEW
[1] M. N. Mohammed, Halim Syamsudin, and Mnel A H Abdelgnei. "Toward a Novel Design
for Mechanical Ventilator System to Support Novel Coronavirus (Covid-19) Infected
Patients Using IoT Based Technology" 2021 IEEE International Conference on Automatic
Control & Intelligent Systems (I2CACIS). IEEE, 2021
• The ventilator plays important role in saving the Covid-19 patients. Ventilator can aid the
patient to breath easily and supporting the lungs by letting in the sufficient air while
encountering the hard breathing.
• In developed area, the ventilator is limited while the demand during pandemic gets
increased. This paper proposes a low-cost prototype of ventilator for Covid-19 patient
which integrated with IoT.
• The technology supports the clinicians to monitor the patient condition by letting the
ventilator and the phone or tablet to be connected and exchange information.
[2] Sergio Morales, Styven Palomino, Ricardo Terreros, and Victor Ulloque. "Pressure and
Volume Control of a Non-invasive Mechanical Ventilator: a PI and LQR Approach." 2021
9th International Conference on Control, Mechatronics and Automation (ICCMA). IEEE,
2021
• In this regard, the development of mechanical ventilation systems became very
important for the care of patients with moderate symptoms caused by the virus.
• Most of the works developed used the non invasive mechanical ventilation system,
since this is rapidly assembled and replicated.
• This work is centered on automating the manual Bag-Valve-Mask (BVM) ventilation
of the Emergency Mechanical Ventilator for ICU (UTEC-AE EMV-ICU).
• it is necessary to implement a satisfactory control system to reach the adequate volume
or pressure for patients.
• The LQR control system of the UTEC-AE EMV-ICU was tested in an artificial lung
where the obtained results were compared and discussed with the obtained results from
a PI control system.

[3] Saad Pasha, Eesha Tur Razia Babar,and Jack Schneider. "A Low-cost, Automated,
Portable Mechanical Ventilator for Developing World." 2021 IEEE Global Humanitarian
Technology Conference (GHTC). IEEE, 2021
• A large portion of world's population, especially in developing world, gets affected by
the respiratory diseases. Often these patients need a medical device called a ventilator
for assistance with their breathing.
• The ventilator is an expensive and complicated equipment and is often unavailable to
patients, leading to severe complications and mortality. In this paper, we present a
system that automates the use of a conventional bag valve mask (BVM) and regulates
its operation to mimic the response of an ICU Ventilator for life saving applications.
• The system consists of motorized actuators, sensors, valves and a control system to
achieve controlled volume ventilation. This paper presents system design and
implementation techniques for this low-cost design.
• The system has been tested extensively using ventilator testers and is being developed
into a product for use in under-resourced settings.
[4] Jozef zivcak; Michal Kelemen;and Ivan Virgala. "A Portable BVM-based Emergency
Mechanical Ventilator." A Portable BVM-based Emergency Mechanical Ventilator." A
Portable BVM-based Emergency Mechanical Ventilator.IEEE, 2021
• The paper deals with development of an artificial lung ventilation. The aim of the paper
is to present developed ventilator based on bag-valve-mask, which could be used as
alternative to mechanical ventilator in critical situations related to COVID-19.
• At first, we present basic principles of positive pressure ventilation. Subsequently, we
introduce a requirements to emergency mechanical ventilator in order to be suitable
alternative in hospitals as well as in households. The mechanical and control design are
presented in the next section.
• Finally, we experimentally verify developed ventilator with focus on measured
pressure of patient airways. The presented results show a potential of developed
ventilator to be used at practical level.
[5] Joey Reinders, Bram Hunnekens, and Frank Heck. "Adaptive Control for Mechanical
Ventilation for Improved Pressure Support." 2020 IEEE Transactions on Control Systems
Technology. IEEE, 2020
• Respiratory modules are medical devices used to assist patients to breathe. The aim of
this article is to develop a control method that achieves exact tracking of a time-varying
target pressure, for unknown patient-hose-leak parameters and in the presence of
patient breathing effort.
• This is achieved by an online estimation of the hose characteristics that enables
compensation for the pressure drop over the hose.

• Stability of the closed-loop system is proven, and the performance improvement
compared to the existing control strategies is demonstrated by simulation and
experimental case studies.
[6] Leonardo Acho,Alessandro N. Vargas,and Gisela Pujol-Vazquez. "Low-Cost, Open-
Source Mechanical Ventilator with Pulmonary Monitoring for COVID-19 Patients." 2020
3rd IEEE Conference on Advance in Science. IEEE, 2020.
• This paper shows the construction of a low-cost, open-source mechanical ventilator.
• The motivation for constructing this kind of ventilator comes from the worldwide
shortage of mechanical ventilators for treating COVID-19 patients—the COVID-19
pandemic has been striking hard in some regions, especially the deprived ones.
Constructing a low-cost, open-source mechanical ventilator aims to mitigate the effects
of this shortage on those regions.
• The equipment documented here employs commercial spare parts only. This paper also
shows a numerical method for monitoring the patients’ pulmonary condition.
• The method considers pressure measurements from the inspiratory limb and alerts
clinicians in real-time whether the patient is under a healthy or unhealthy situation.
[7] Md. Rakibul Islam, Mohiuddin Ahmad and Md. Shahin Hossain. "Designing an Electro-
Mechanical Ventilator Based on Double CAM Integration Mechanism." 2019 1st IEEE
International Conference. IEEE, 2019
• This paper proposes a simplified structure of microcontroller based mechanical
ventilator integrated with a Bag-Valve-Musk (BVM) ventilation mechanism.
• An Ambu bag is operated with computer-aided manufacturing (CAM) arm that is
commanded via a microcontroller and manual switches by sending a control signal to
the mechanical system and according to this control signal, the mechanical computer-
aided manufacturing (CAM) arm simultaneously compresses and decompresses the
Ambu bag.
• It is a self-inflating bag and like a one-way valve around its inlet and outlet corner. By
compressing the Ambu bag it delivers air and by relaxing, it takes air from the
environment through a mechanical scavenger. The control signals are designed with
three modes named adult mode, pediatric mode, and child mode based on the
respiratory rate.
• The device is in assist controlled mode by dint of fixing the tidal volume for all unique
control signals. The control signal is visualized by a platform known as the BIOPAC
student’s lab system.
• The proposed device is portable, compact, low weight, and efficient performable. It can
be supplied around the rural area hospitals for immediate medication with cost
efficiency and risk avoidance.

[8] Man Ting Kwong, Glen Wright Colopy, and Anika M. Weber. "The efficacy and
effectiveness of machine learning for weaning in mechanically ventilated patients at the
intensive care unit: a systematic review." 2019 1st Conference of applied sciece and
technology computer science. IEEE, 2019
• Prolonged mechanical ventilation (MV) leads to a range of medical complications that
increases length of stay and costs as well as contributes to morbidity and even mortality
and long-term quality of life.
• The need to reduce MV is both clinical and economical. Artificial intelligence or
machine learning (ML) methods are promising opportunities to positively influence
patient outcomes.
• There is a particular interest in empirical methods (such as ML) to improve
management of “difficult-to-wean” patients, due to the associated costs and adverse
events associated with this population.
[9] Yan SHI, Hao ZHANG, and Zihao LUO. "Mechanical Ventilation Intelligent Control
Technology Based on Fuzzy Adaptive PID." 2019 IEEE 8th International Conference on
Fluid Power and Mechatronics (FPM). IEEE, 2019
• The ventilator is an important means of assisting and even replacing spontaneous
breathing and has an unshakable position in the medical field.
• IT mainly studies the method of fuzzy adaptive PID control and traditional PID control
of mechanical ventilation pressure based on the dual lung model.
• A mathematical model of the lungs during breathing is established and simulated.
Furthermore, the experimental platform was built based on a mechanical ventilation
system, and the classic PID control and fuzzy adaptive PID control were realized by
programming the single chip.
• The study of the two-lung model and the two control algorithms not only provides a
simple and easy test method, but also has guiding significance for the development of
mechanical ventilation control mode.
[10] Carlo Massaroni, Daniela Lo Presti, and Paola Saccomandi. "Fiber Bragg Grating
Probe for Relative Humidity and Respiratory Frequency Estimation: Assessment
During Mechanical Ventilation." 2017 IEEE Sensors Journal. IEEE, 2017
• Fiber Bragg grating (FBG) sensors have gained popularity in medicine for some
valuable features, such as small size, immunity to electromagnetic interferences, and
good metrological properties.
• This information can be used as a feedback to improve the performance of the
HWHs.
• This solution allows an easy insertion of the probe within the ducts connecting the
ventilator to the patient.

CHAPTER 3
PROPOSED PROJECT WORK
3.1 PROBLEM STATEMENT
In an effort to address the worldwide problem of a lack of ventilators—for which there was an
extremely high demand during the pandemic—the cost of oxygen ventilation became prohibitively
expensive at a time when there was no adequate system for monitoring patients in accordance with
their individual states of health. People have breathing problems because they find it difficult to
breathe on their own or because they are unable to breathe on their own. Even in well-equipped
hospitals, protocols have been developed for sharing the same ventilator between two patients.
This is a questionable practice for a number of reasons, including the fact that it raises the risk of
transmitting bacterial and viral loads between patients as well as the possibility of causing
unintended harm.
Due to the fact that inadequate ventilation enables alveolar units to collapse and reopen in a
manner that is repeated and sequential, this movement can also result in harm.
There was no such ventilator that was a low-cost, portable prototype that can be used in
ambulances, small hospitals, or during disaster management to provide volume and pressure-
controlled air for patients. This ventilator would have been useful in providing volume and
pressure-controlled air for patients.
3.2 OBJECTIVES
The objectives of our project are:
• To build a low-cost air volume control emergency mechanical ventilator for respiratory support
while designing a prototype and working out the kinks in the process.
• To ensure that patients receive the best possible respiratory treatment from smart ventilators
that can adjust to the unique circumstances of each patient and the changing conditions of the
environment in which they are being treated.
• In order to get better understanding of the characteristics and outcomes of patients on IMV.
• To keep up the gas exchange while decreasing or replacing the amount of work done by the
respiratory system.
• To devise a device that may be used by the general population and that also contributes to
ventilation in cases of acute respiratory distress syndrome.
• In order to lessen the likelihood of problems and also to make the patient more comfortable.

3.3 METHODOLOGY
The embedded model mainly consists of following Components:
• Node MCU
• L298 motor driver
• 12 v Adaptor
• DHT Temperature sensor
• Blood oxygen sensor (MAX30100)
• LCD (16×2)
• Ambu Bag
• DC Motors(30RPM)
As Fig.3.3 Depictes the block diagram of the Mechanical ventilator Where 12V, is supplied to the
Node MCU from the from Adaptor, the Arduino controls the DC motor that drives the wheels. The
wheels squeeze the Ambu bag at predetermined time intervals based upon this user's settings.
Furthermore, the arduino manages the motor movement so that the squeezing process of Ambu
bag matches the setting, which includes the frequency of respiratory, inspiration-to-expiration
ration at each cycle of the respiratory cycle, and the provided air volume to the patient.
In addition, the Arduino manages the motor movement in such a way that the squeezing
process of the Ambu bag matches the settings. These settings include the frequency of the patient's
respiratory cycles, the inspiration-to-expiration ration at each cycle of the respiratory cycle, and
the air volume that is provided to the patient.
When the patient touches the tip of their finger on the sensors, which comprise a blood-
oxygen sensor, a pulse sensor, and a temperature sensor, the measurements are taken. All of these
sensor data are sent to an Arduino Uno, which is used to store the information before it is sent to
the Blynk application through the Blynk cloud and kept there.
The information is also saved in the cloud. The program will not operate until it first reads
the blood-oxygen data of the patient from the sensor. This is because the blood-oxygen data plays
an essential part in analyzing the patient's circumstances and also activates the other sensors.
By downloading the Blynk app on our mobile devices, we are able to check the condition of
the patient at any time. If the patient's pulse or blood oxygen levels are too low, we may turn on
the mechanical ventilator. Through the Arduino's built-in USB connection, the data that has been
gathered will be transmitted to the cloud.
This information will be stored in the cloud, and the clinician will be able to get it via an
Android app that has been installed on the device. The patient, who is now connected to a
ventilator, will be under close observation by the Android application thanks to its monitoring
capabilities.
The clinician is able to remotely monitor and configure the ventilator if necessary. The record
of the patient's current state is also displayed here. The patient's condition is summed up and all of
the data that was received by the ventilators is shown by the application for Android.

The configuration will first be sent to the cloud by the application, and then it will be
downloaded to the ventilators. This approach illustrates the process of data exchange that takes
place between the ventilators and the device by utilizing cloud technology.
A sensor with the model number Max30100 is also included in the ventilator. This sensor
delivers data in real time regarding the rise and fall of a patient's pulse rate as well as the oxygen
level in their blood.
A two-channel relay and a direct current motor are both included in the Mechanical Ventilator.
The relay serves as a switch to active and deactivate the DC motor.
Fig.3.3: Block Diagram of Mechanical ventilator
NODE
MCU
Blood – Oxygen
Sensor
Temperature Sensor
Power
supply
L298
Motor
Driver
Dc Motor
Mechanical
Ventilator
Blynk
Cloud
Blynk Application
Device
LCD Display

3.3.1 Node MCU
Node MCU is an open source firmware for which open source prototyping board designs are
available. The name "Node MCU" combines "node" and "MCU" (micro-controller unit).The term
"Node MCU" strictly speaking refers to the firmware rather than the associated development kits.
Both the firmware and prototyping board designs are open source. The firmware uses the Lua
scripting language. The firmware is based on the eLua project, and built on the Espressif Non-OS
SDK for ESP8266. It uses many open source projects, such as lua-cjson and SPIFFS. Due to
resource constraints, users need to select the modules relevant for their project and build a firmware
tailored to their needs. Support for the 32-bit ESP32 has also been implemented.
3.3.2 Blood-Oxygen Sensor
A blood oxygen sensor is a device that measures the amount of oxygen in the blood. A pulse
oximeter (also known as a pulse ox) is a noninvasive device that measures the quantity of oxygen
in your blood. It accomplishes this by directing infrared light into the capillaries of your finger,
toe, or earlobe. The amount of light reflected off the gases is then measured.
3.3.3 Temperature Sensor
A LM35 temperature sensor is a temperature measurement device with an analogue output
voltage proportional to the temperature. It produces output voltage in degrees Celsius (Celsius).
The major goal of our project for Covid patients is to determine whether or not the patient has a
fever. For this aim, we are employing an LM35 sensor to monitor the body temperature.
3.3.4 Blynk application
Blynk is a firm that specializes in the Internet of Things (IoT) and offers a platform for the
development of mobile applications (both for iOS and Android). These applications have the
ability to connect electrical devices to the Internet and to remotely monitor and manage these
devices.
Using the many different widgets that we supply, the Blynk App enables you to design
incredible user interfaces for your projects.
Blynk Server is in charge of handling all of the communications that take place between the
smartphone and the hardware. You have the option of using the Blynk Cloud or running your own
private Blynk server on your local computer. It is open-source and has the capability of effortlessly
managing thousands of devices.
Blynk Libraries are available for all of the most common hardware platforms. These libraries
enable communication with the server and execute all commands sent to and received from the
device. Therefore, if you push a Button inside the Blynk app, the message is sent to the Blynk

Cloud, and from there, it somehow makes its way to the hardware you have installed. Everything
happens in the blink of an eye, and it works exactly the same way while going in the other direction.
3.4 Flow Chart
Fig.3.4 depicts the flow chart of the mechanical ventilator and the control algorithm for the
automated adjustment of the patient's breathing support level. When a patient's measured
respiratory elastance and airway resistance are taken into account in a flow-chart, a major cycle
begins at A where the values of the patient's measured end-tidal PCO2 (PetCO2) are read.
The computer then checks to see if the patient is able to breathe on their own. If he isn't,
then equations are used to determine the appropriate ventilation and respiratory rate, and those
values are then restricted to acceptable levels. After that, the ventilator receives control signals,
and the program returns to A after a few breathing cycles have passed. For patients who are already
breathing on their own, their ventilation needs are calculated using Equations and confined to a
safe range in the following phase.
In the next step, the ventilator is checked to determine if there has been enough time to
modify the support level since the last adjustment. A patient's average measured ventilation is
calculated if sufficient time has not passed. After a single breath of waiting, the software returns
to level A with no changes to the support level.
For patients who have not had a recent modification to their support level, they are compared
to their average measured ventilation to see if they need more or less assistance. There is no change
in support level and the program returns to A after one breathing cycle when the average ventilation
is within a particular range (e.g., 90–110 percent) of the needed value. If this occurs. Otherwise, a
new support level is computed and restricted to a safe range if the average ventilation does not fall
within an acceptable range of the needed value.
In the next step, the ventilator's control signal is transmitted, and the program returns to A.
The PAV support level can be adjusted based on the patient's WOB using the technique described
in this article. This means that if the patient's WOB is monitored, the support level is adjusted
correspondingly if WOB exceeds a maximum permissible limit to avoid tiredness during weaning.
For the sake of brevity, the algorithm's complete flowchart is not included here. The patient's WOB
and the patient's necessary ventilation can both be utilized to automatically regulate the degree of
PAV assistance that the PAV is providing. In this instance, the system will employ the highest
support level indicated by the algorithms, although they can also be used in parallel.

Fig.3.4: Flow Chart of Mechanical Ventilator

3.5 CIRCUIT DIAGRAM
Fig 3.5: Circuit Diagram
As Fig 3.5 depicts the Circuit Diagram that gives the brief about the Working of the hardware
components and also the connections of each components how its interfaced with each other. Here
the circuit shows the connections of every components where all the components are attached to
the Breadboard.
The Node MCU is the main component that is a micro-controller, where it stores the data
and this gives signals to all the other components as well, this also controls the operation of other
components too.
The DHT Temperature sensor and the Blood-Oxygen are connected to the Node MCU which
are the analog signals. This is there connected to the Analog pins of the Node MCU.
The LCD Display is also connected to the Node MCU for the digital Outputs where the input
pins are analog and the output pins connected are digital.
There is also L298 Motor Driver which is used for acting as the stabilizer between the
Components and the Dc Motor for the stable Power Supply.

3.6 APPLICATION
• The patients are supplied with oxygen-rich air by these ventilators, which are intended to help
them breathe.
• It is possible to apply it during the surgical procedures.
• This ventilator serves an emergency purpose and is utilized in the ambulance.
• When a patient has acute severe asthma, this is the treatment that is administered.
• During the time of respiratory acidosis, this might be utilized.
• Due to the inexpensive cost of this ventilation system, it is suitable for use in the smaller clinics.
3.6 ADVANTAGES
• The patient's respiratory muscles relax since they do not have to exert themselves to the same
degree to breathe.
• Time has been given to the patient so that they may recuperate in the hopes that their breathing
will return to normal.
• Assists the patient in receiving an appropriate supply of oxygen and rids the body of excess
carbon dioxide.
• Maintains an open airway while minimizing the risk of harm caused by aspiration.
• The apparatus ensures that the body is provided with the necessary amount of oxygen while
also removing carbon dioxide from the blood.
• In cases where certain disorders hinder proper breathing, it is vital to do so.

Chapter 4
SOFTWARE AND HARDWARE
4.1 SOFTWARE REQUIREMENTS
4.1.1 Arduino IDE
Fig.4.1.1: Arduino IDE Software
Any programming language with compilers that create binary machine code for the target
processor may be used to write the code for a program that will run on Arduino hardware. Atmel
offers two different versions of its programming environment, which can be used with their 8-bit
AVR and 32-bit ARM Cortex-M based microcontrollers. These versions are known as AVR Studio
(the older one) and Atmel Studio (newer).
Java is the programming language used in the Arduino integrated development environment
(IDE), which is a cross-platform application (it may run on Microsoft Windows, macOS, and
Linux). It was born out of the integrated development environment (IDE) for the programming
languages Processing and Wiring. It provides simple one-click mechanisms to compile and upload
programs to an Arduino board, as well as a code editor with features such as text cutting and
pasting, searching and replacing text, automatic indenting, brace matching, and syntax
highlighting. Additionally, it includes a code editor with features such as text searching and
replacing text. In addition, it has a text terminal, a message area, a toolbar with buttons for typical
actions, and a hierarchy of different menus to choose from while doing operations. The GNU
General Public License, version 2, is the license that governs the distribution of the IDE's source
code.
The integrated development environment (IDE) for Arduino supports the programming
languages C and C++ and uses specialized rules for the organization of code. The Arduino
Integrated Development Environment (IDE) includes a software library that was developed as part
of the Wiring project. This library covers a variety of standard input and output operations. The

user-written code only needs to include two fundamental functions, one for starting the sketch, and
another for the main program loop. These functions are then compiled and linked with a program
stub called main() to produce an executable cyclic executive program using the GNU toolchain,
which is also included with the distribution of the IDE. The Arduino Integrated Development
Environment (IDE) makes use of the software avrdude to convert executable code into a text file
with hexadecimal encoding. This file is then used by a loader program contained inside the
Arduino board's firmware to load the executable code into the Arduino board.
Since version 1.8.12, the Arduino IDE for Windows only supports operating systems that are
newer than Windows 7. When attempting to validate or upload a software on a Windows operating
system older than Windows Vista, the user receives the message "Unrecognized Win32
application." Users with older machines have the option of upgrading to version 1.8.11 or copying
the "arduino-builder" executable from version 11 into their existing install folder. This executable
is separate from IDE and may be used to run IDE on older machines.
4.1.2 Blynk Application
Fig.4.1.2: Blynk Application
You can manage and monitor your hardware projects from your iOS and Android devices using
the new Blynk platform. Blynk's program allows you to construct a dashboard for your project and
arrange buttons, sliders, graphs, and other widgets on the screen. You can toggle pins on and off
and view sensor data using the widgets.
When it comes to hardware projects, there are likely hundreds of tutorials available, but
establishing the software interface remains a challenge for many. With Blynk, on the software side,
things are even easier. Blynk is ideal for connecting to basic tasks like keeping tabs on your fish
tank's temperature or remotely switching on and off lighting. The RGB LED strips in my living
room are being controlled by it.

Today, the majority of Arduino and Raspberry Pi boards are supported by Blynk as are the
ESP8266 and Particle Core single-board computers. More are on the way. Even if you don't have
a Wi-Fi or Ethernet shield, you can still manage USB-connected hardware.
You may establish a Blynk server on your home network, allowing you to keep all of your
devices on the same network. If you need to build up a network at a remote area, or if you're
worried about your traffic flowing via other computers in the cloud, this is a great feature to have.
The few different systems for controlling devices via the internet, but Blynk is one of the
most user-friendly and open-source under an MIT license that I've come across yet.
4.2 HARDWARE REQUIREMENTS
4.2.1 Node MCU
Fig.4.2.1: Node MCU
NodeMCU is a low-cost open source IoT platform. It initially included firmware which runs on
the ESP8266 Wi-Fi SoC from Espressif Systems, and hardware which was based on the ESP-12
module. Later, support for the ESP32 32-bit MCU was added.
NodeMCU is an open source firmware for which open source prototyping board designs are
available. The name "NodeMCU" combines "node" and "MCU" (micro-controller unit). The term
"NodeMCU" strictly speaking refers to the firmware rather than the associated development kits.
Both the firmware and prototyping board designs are open source. The firmware uses the
Lua scripting language. The firmware is based on the eLua project, and built on the Espressif Non-
OS SDK for ESP8266. It uses many open source projects, such as lua-cjson and SPIFFS. Due to
resource constraints, users need to select the modules relevant for their project and build a firmware
tailored to their needs. Support for the 32-bit ESP32 has also been implemented.

The prototyping hardware typically used is a circuit board functioning as a dual in-line
package (DIP) which integrates a USB controller with a smaller surface-mounted board containing
the MCU and antenna. The choice of the DIP format allows for easy prototyping on breadboards.
The design was initially based on the ESP-12 module of the ESP8266, which is a Wi-Fi SoC
integrated with a Tensilica Xtensa LX106 core, widely used in IoT applications.
Through its pins we can read inputs - light on a sensor, a finger on a button, or a Twitter
message -and turn them into an output - activating a motor, turning on an LED, publishing
something online. It has also WiFi capabilities, so we can control it wirelessly and make it work
on a remote installation easily. We can tell our board what to do by sending a set of instructions to
the microcontroller on the board. To do so we can use the the Arduino Software (IDE).

4.2.2 Blood-oxygen Sensor
Fig.4.2.2: Blood-Oxygen Sensor
This electronic device measures the percentage of oxygen (O2) in the gas or liquid being analyzed.
It is called an oxygen sensor (or lambda sensor, where refers to the air–fuel equivalency ratio,
commonly indicated as).
As a result of the work of Dr. Günter Bauman, Robert Bosch GmbH developed it in the
late 1960s. An unheated version of the original sensing element is composed of a thimble-shaped
zirconia ceramic covered with a small coating of platinum on the exhaust and the reference sides.
The ceramic detecting element's bulk was greatly lowered, and the heater was built right into the
ceramic structure, thanks to the introduction of the first planar-style sensor in 1990. As a
consequence, the sensor was able to start and respond more quickly.
For automobiles and other vehicles with internal combustion engines, the most common
application is to measure the oxygen concentration in exhaust gas to calculate and, if necessary,
dynamically adjust the air-fuel ratio so that catalytic converters can work optimally and also
determine whether the converter is working properly. When the fuel-air combination is high and
the exhaust contains little unburned oxygen, an oxygen sensor can produce up to 0.9 volts.
Oxygen sensors are used by scientists to monitor respiration or the creation of oxygen.
Oxygen analyzers, such as anesthetic monitors, respirators, and oxygen concentrators, rely heavily
on oxygen sensors.
The partial pressure of oxygen in a diver's breathing gas is measured using oxygen sensors
(also known as ppO2 sensors). In open circuit scuba diving, a diver can simply predict how the
gas mixture will change during the dive, but in mixed gas rebreather diving, the diver must
constantly monitor the partial pressure of oxygen in the breathing loop to ensure that it does not
fall outside of acceptable limits during the dive.

For the purpose of continually monitoring the oxygen content within the protected volumes,
oxygen sensors are also utilized in hypoxic air fire prevention systems.
You may use a variety of methods to determine how much oxygen you have in your body.
Zirconia, electrochemical (also known as galvanic), infrared, ultrasonic and paramagnetic
approaches are only some of the technologies available.
After entering the lungs, oxygen is transported to the bloodstream. Our body's organs
receive oxygen via the blood. Hemoglobin is the primary carrier of oxygen in human blood. This
gadget is put on the finger, the earlobe or the toe to measure the oxygen saturation level of the
patient's blood.
The quantity of oxygen in the blood in the finger is measured by passing small beams of
light through the blood. A shift in light absorption in oxygenated vs. deoxygenated blood is
detected with this device.
The sensor is a pulse oximetry and heart rate monitor sensor system that is fully integrated
into one device. Pulse and heart rate signals may be detected using two LEDs, a photo detector,
appropriate optics, and low-noise analog signal processing. When the power supply is
disconnected, it consumes a tiny amount of standby current, allowing the power supply to be
connected at all times.
Features of Blood-oxygen sensor:
• It uses relatively little energy (operates from 1.8V and 3.3V)
• A very low shutdown current (about 0.7 A) is required.
• Capacity for Fast Data Output
4.2.3 Temperature Sensor
Fig.4.2.3: DHT Temperature Sensor
Analog signals are generated by the DHT temperature sensor, which are proportional to the current
temperature. It is simple to convert the output voltage into Celsius temperature readings. There is

no need for external calibration with the lm35 compared to the thermistor. Additionally, the
covering prevents the surface from overheating. Many hobbyists, DIY circuit builders, and
students use it because of its low cost and high precision. LM35 is utilized in many low-end goods
because of its low cost and high precision. The sensor has been around for at least 15 years and is
still in use today in a variety of goods.
It can measure temperatures from -55 degrees Celsius to a maximum temperature of 150
degrees Celsius. Accuracy is extremely high when the temperature and humidity conditions are
optimum. Also simple and straightforward is the conversion of output voltage to Celsius.
The linear scale factor must be understood in order to fully appreciate the DHT temperature
sensor's operation. It is stated in the DHT characteristics that it increases by +10 millivolts per
degree Celsius. As the sensor vout pin output increases by 10 millivolts, the temperature rises by
one. If the sensor outputs 100 millivolts at the vout pin, then the temperature in degrees Celsius
will be 10 degrees Celsius. Even a negative temperature measurement is a sign of something
sinister. The temperature will be -10 degrees Celsius if the sensor outputs -100 millivolts.
Features of the DHT temperature sensor:
• Straightforward Celsius Calibration (Centigrade)
• 10 mV/°C linearity Scale Factor 0.5°C. ' Precision (at 25°C) Ensured
• With a full operating temperature range of 55°C to 150°C, this product is a powerhouse. Range
• Appropriate for Use in Remote Settings
• The operating voltage ranges from four volts (V4) to thirty (V30).
• less than 60 a volt Drainage Currently Taking Place
• 0.08°C in Still Air Non-Linearity Self-Heating No more than 14 degrees Celsius, at most
Typical
• For 1-mA loads, low output impedance, 0.1

4.2.4 L298 Motor Driver
Fig.4.2.4: L298 Motor Driver
This L298N Motor Driver Module is a high power motor driver module for driving DC and Stepper
Motors. This module consists of an L298 motor driver IC and a 78M05 5V regulator. L298N
Module can control up to 4 DC motors, or 2 DC motors with directional and speed control
The L298N Motor Driver module consists of an L298 Motor Driver IC, 78M05 Voltage
Regulator, resistors, capacitor, Power LED, 5V jumper in an integrated circuit.
78M05 Voltage regulator will be enabled only when the jumper is placed. When the power
supply is less than or equal to 12V, then the internal circuitry will be powered by the voltage
regulator and the 5V pin can be used as an output pin to power the microcontroller. The jumper
should not be placed when the power supply is greater than 12V and separate 5V should be given
through 5V terminal to power the internal circuitry, ENA & ENB pins are speed control pins for
Motor A and Motor B while IN1& IN2 and IN3 & IN4 are direction control pins for Motor A and
Motor B.
The features of L298 Motor Drive:
• Driver Chip: Double H Bridge L298N
• Motor Supply Voltage (Maximum): 46V
• Motor Supply Current (Maximum): 2A
• Logic Voltage: 5V
• Driver Voltage: 5-35V
• Driver Current:2A
• Logical Current:0-36mA

• Maximum Power (W): 25W Current Sense for each motor Heatsink for better performance
Power-On LED indicator
4.2.5 DC Motor
Fig.4.2.5: DC Motor
Direct current (DC) electrical energy is converted into mechanical energy using a rotary DC motor.
The most popular varieties rely on magnetic fields to generate the forces needed to operate. There
are several types of DC motors with internal mechanisms, either electromechanical or electronic,
that allow them to periodically reverse direction of current flow.
Because they could be powered by existing systems for distributing direct current
illumination, DC motors were the first type of motor to be widely employed. It is possible to alter
the speed of a DC motor across a large range by varying the supply voltage or the intensity of
current flowing through its field windings. Tools, toys, and appliances all employ small DC
motors. However, the universal motor, which can run on direct current but is utilized for portable
power tools and appliances, is a brushed motor. Electric vehicles, elevators, hoists, and steel rolling
mill drives all employ large DC motors. In many cases, the introduction of power electronics has
made it practical to replace DC motors with AC motors.
Features of DC Motor:
• In order to maintain a constant speed, you don't require a driving circuit.
• Optimized for efficiency
• Able to run at a rapid rate
• Torque at low RPMs
• Speed and torque may be regulated by voltage, making it responsive and easy to operate.

4.2.6 LCD Display (16×2)
Fig 4.2.6: LCD Display (16×2)
In LCD 16×2, the term LCD stands for Liquid Crystal Display that uses a plane panel display
technology, used in screens of computer monitors & TVs, smartphones, tablets, mobile devices,
etc. Both the displays like LCD & CRTs look the same but their operation is different. Instead of
electrons diffraction at a glass display, a liquid crystal display has a backlight that provides light
to each pixel that is arranged in a rectangular network.
An electronic device that is used to display data and the message is known as LCD 16×2. As
the name suggests, it includes 16 Columns & 2 Rows so it can display 32 characters (16×2=32) in
total & every character will be made with 5×8 (40) Pixel Dots. So the total pixels within this LCD
can be calculated as 32 x 40 otherwise 1280 pixels.
16×2 displays mostly depend on multi-segment LEDs. There are different types of displays
available in the market with different combinations such as 8×2, 8×1, 16×1, and 10×2, however,
the LCD 16×2 is broadly used in devices, DIY circuits, electronic projects due to less cost,
programmable friendly & simple to access.
Features of LCD Display(16×2)
• The operating voltage of this display ranges from 4.7V to 5.3V
• The display bezel is 72 x 25mm
• The operating current is 1mA without a backlight
• PCB size of the module is 80L x 36W x 10H mm
• HD47780 controller
• LED color for backlight is green or blue

• Number of columns – 16
• Number of rows – 2
• Number of LCD pins – 16
• Characters – 32
• It works in 4-bit and 8-bit modes
• Pixel box of each character is 5×8 pixel
• Font size of character is 0.125Width x 0.200height
4.2.7 Ambu Bag
Fig.4.2.7: Ambu bag
"self-inflating bag" or "bag valve mask" (BVM) are two terms for a hand-held equipment that
provides positive pressure ventilation to patients who are either not breathing or not breathing
sufficiently. As a common piece of equipment on a crash cart, in emergency departments, and in
other critical care settings, the device is required in out-of-hospital resuscitation kits for qualified
personnel. The American Heart Association (AHA) Guidelines for Cardiopulmonary
Resuscitation and Emergency Cardiac Care urge that "all healthcare personnel should be
conversant with the use of the bag-mask device," underscoring how often and widely BVMs are
used in the United States.
A manual resuscitator is also utilized in the hospital when the mechanical ventilator has to
be evaluated for probable malfunction or if ventilator-dependent patients need to be transferred
inside the hospital. The two main types of manual resuscitators are self-filling with air, however
additional oxygen (O2) can be supplied but is not required for the device to work. The flow-
inflation manual resuscitator is used extensively in the operating room for non-emergency
anesthetic induction and recovery ventilation.

Features of Ambu Bag:
• A resuscitation gadget that inflates on its own
• A tank with two one-way valves for storing oxygen.
• Directs new supply of oxygen to the patient while preventing exhaled gas from returning to the
bag.
• Adaptor for masks or tubes with a standard 15 mm diameter.
4.2.8 Adaptor
Fig.4.2.8: Adaptor
An adapter or adaptor is a device that converts attributes of one electrical device or system to those
of an otherwise incompatible device or system. Some modify power or signal attributes, while
others merely adapt the physical form of one connector to another.
Many countries with ties to use 230-volt, 50 Hz AC mains electricity, using a variety of
power plugs and sockets. Difficulty arises when moving an electrical device between countries
that use different sockets. A passive electric power adapter, sometimes called a travel plug or travel
adapter, allows using a plug from one region with a foreign socket. As other countries supply 120-
volt, 60 Hz AC, using a travel adapter in a country with a different supply poses a safety hazard if
the connected device does not support both input voltages.

CHAPTER 5
RESULT AND DISCUSSION
5.1 PROJECT OUTCOME
The covid-19 patients benefit from mechanical ventilation, which makes breathing easier and more
comfortable, the development of an open-source, low-cost mechanical ventilator The COVID-19
epidemic has been particularly harsh on some regions, notably the poorer ones, which prompted
the development of this new type of mechanical ventilator. Building an open-source, low-cost
mechanical ventilator is one way to help alleviate the shortage's consequences on such areas. When
you use a ventilator, it helps to pump oxygen into your body mechanically. A tube that runs from
your mouth to your windpipe transports the air. Both the ventilator and you have the option of
breathing out on your own. You may program the ventilator to take a specific number of breaths
per minute on your behalf. All of this is made possible by the use of this ventilation. Trauma or
oropharyngeal infection might obscure the patient's ability to breathe, making it difficult to
administer effective airway protection. Reduced minute ventilation causes hypercapnic respiratory
failure. Due to a lack of oxygenation, hypoxic respiratory failure. Cardiac distress in which
artificial ventilation can reduce the energy demands of breathing. Patient deterioration or transfer
are examples of expected outcomes. The potential advantages of the derived mechanical ventilator
were demonstrated in laboratory experiments that simulated healthy and unwell individuals. In
order to prevent these unwanted fevers and changes in pulse rate, we have devised a revolutionary
approach that monitors a patient's health state.

CONCLUSION
• In evident from the above study the ventilator pays an important role for the breath that lets the
patient or the person to breath comfortable. This however monitors the health conditions and it
updates the patient condition on its owns with alerting the authority.
• Mechanical ventilation's primary goals have, are, and always will be to provide adequate life
support while minimizing danger and maximizing comfort.
• In addition to helping the patient acquire enough oxygen and remove carbon dioxide, it gives
them time to recuperate in the hopes that their breathing will return to normal. As a result, it
maintains a stable airway and guards against aspiration damage.
• It's crucial to remember that artificial breathing doesn't help the patient get well. Instead, it gives
the patient a chance to maintain stability as the drugs and therapies aid in their recovery.
However, one uncommon kind of injury is atelectrauma, which appears to be caused by a
deficiency in breathing.

SCOPE FOR FUTURE WORK
• To put it another way, the bulk of mass-produced ventilators that have been manufactured
recently are called emergency ventilators.
• Patients with acute respiratory distress syndrome (ARDS) require precision air supply and
decision support tools for lung-protective ventilation, which these simpler ventilators cannot
offer. ICU ventilators that are developed for invasive ventilation of severely sick patients are
still in demand in some places.
• As a result, the pandemic has a favorable effect on the total respiratory care infrastructure sector.
ICU ventilators and related capital equipment, including as humidifiers, oxygen delivery
systems, and disposables, will continue to be purchased by countries all over the world in the
years to come.

REFERENCES
[1] M. N. Mohammed, Halim Syamsudin, and Mnel A H Abdelgnei. "Toward a Novel Design for
Mechanical Ventilator System to Support Novel Coronavirus (Covid-19) Infected Patients
Using IoT Based Technology" 2021 IEEE International Conference on Automatic Control &
Intelligent Systems (I2CACIS). IEEE, 2021
[2] Sergio Morales, Styven Palomino, Ricardo Terreros, and Victor Ulloque. "Pressure and
Volume Control of a Non-invasive Mechanical Ventilator: a PI and LQR Approach." 2021
9th International Conference on Control, Mechatronics and Automation (ICCMA). IEEE,
2021
[3] Saad Pasha, Eesha Tur Razia Babar,and Jack Schneider. "A Low-cost, Automated, Portable
Mechanical Ventilator for Developing World." 2021 IEEE Global Humanitarian Technology
Conference (GHTC). IEEE, 2021
[4] Jozef zivcak; Michal Kelemen;and Ivan Virgala. "A Portable BVM-based Emergency
Mechanical Ventilator." A Portable BVM-based Emergency Mechanical Ventilator." A
Portable BVM-based Emergency Mechanical Ventilator.IEEE, 2021
[5] Joey Reinders, Bram Hunnekens, and Frank Heck. "Adaptive Control for Mechanical
Ventilation for Improved Pressure Support." 2020 IEEE Transactions on Control Systems
Technology. IEEE, 2020
[6] Leonardo Acho,Alessandro N. Vargas,and Gisela Pujol-Vazquez. "Low-Cost, Open-Source
Mechanical Ventilator with Pulmonary Monitoring for COVID-19 Patients." 2020 3rd IEEE
Conference on Advance in Science. IEEE, 2020.
[7] Md. Rakibul Islam, Mohiuddin Ahmad and Md. Shahin Hossain. "Designing an Electro-
Mechanical Ventilator Based on Double CAM Integration Mechanism." 2019 1st IEEE
International Conference. IEEE, 2019
[8] Man Ting Kwong, Glen Wright Colopy, and Anika M. Weber. "The efficacy and effectiveness
of machine learning for weaning in mechanically ventilated patients at the intensive care unit:
a systematic review." 2019 1st Conference of applied sciece and technology computer science.
IEEE, 2019
[9] Yan SHI, Hao ZHANG, and Zihao LUO. "Mechanical Ventilation Intelligent Control
Technology Based on Fuzzy Adaptive PID." 2019 IEEE 8th International Conference on
Fluid Power and Mechatronics (FPM). IEEE, 2019
[10] Carlo Massaroni, Daniela Lo Presti, and Paola Saccomandi. "Fiber Bragg Grating Probe for
Relative Humidity and Respiratory Frequency Estimation: Assessment During Mechanical
Ventilation." 2017 IEEE Sensors Journal. IEEE, 2017

APPENDIX

Program Code used used in Arduino IDE
#define BLYNK_PRINT Serial
#define BLYNK_PRINT Serial
#include <ESP8266WiFi.h>
#include <BlynkSimpleEsp8266.h>
#include <Wire.h>
#include <DHT.h>
#include "MAX30100_PulseOximeter.h"
#define REPORTING_PERIOD_MS 1000
PulseOximeter pox;
uint32_t tsLastReport = 0;
#define DHTPIN D5
#define DHTTYPE DHT11
DHT dht(DHTPIN, DHTTYPE);
BlynkTimer timer;
int heartrate;
int SP;
int t;
int h;
char auth[] = "bD3Qs8EhiCR52tC_INDZyMSxrxz3DoB1";
char ssid[] = "venti";
char pass[] = "12345678";
int motor1 = D6;
int motor2 = D7;
int motor_speed = D8;

void setup()
{
Serial.begin(9600);
dht.begin();
pinMode(motor1, OUTPUT);
pinMode(motor2, OUTPUT);
pinMode(motor_speed, OUTPUT);
analogWrite(motor_speed,0);
digitalWrite(motor1, LOW);
pinMode(D0, OUTPUT);
pinMode(D4, OUTPUT);
digitalWrite(D0, HIGH);
digitalWrite(D4, HIGH);
Blynk.begin(auth, ssid, pass);
Serial.print("Initializing pulse oximeter..");
if (!pox.begin()) {
Serial.println("FAILED");
for(;;);
} else {
Serial.println("SUCCESS");
}
pox.setOnBeatDetectedCallback(onBeatDetected);
timer.setInterval(10000,temp);
}

void onBeatDetected()
{
Serial.println("Beat!");
}
void loop()
{
pul();
Blynk.run();
// put your main code here, to run repeatedly:
timer.run();
}
void pul()
{
pox.update();
// Asynchronously dump heart rate and oxidation levels to the serial
// For both, a value of 0 means "invalid"
if (millis() - tsLastReport > REPORTING_PERIOD_MS)
{
Serial.print("Heart rate:");
Serial.print(pox.getHeartRate());
Serial.print("bpm / SpO2:");
Serial.print(pox.getSpO2());
Serial.println("%");
heartrate = pox.getHeartRate();
SP = pox.getSpO2();

Blynk.virtualWrite(V4, heartrate);
Blynk.virtualWrite(V5, SP);
tsLastReport = millis();
if(heartrate >= 90 && heartrate <=130 || SP >=80 && SP <=93)
{
motor_start_med_speed();
Blynk.notify("Alert! Patient 1 HeartRate is HIGH");
}
else
{
motor_start_nor();
}
}
}
void temp()
{
t = dht.readTemperature();
h = dht.readHumidity();
Blynk.virtualWrite(V1, t);
Blynk.virtualWrite(V2, h);
}
void motor_start_med_speed()
{
digitalWrite(motor2, HIGH);

}
void motor_start_nor()
{
digitalWrite(motor2, HIGH);
}

report final.pdf

Recommended

Recommended

More Related Content

What's hot

What's hot (20)

Similar to report final.pdf

Similar to report final.pdf (20)

Recently uploaded

Recently uploaded (20)

report final.pdf