WO2023152663A1

WO2023152663A1 - Wearable breath tracking device, system and method for operation of wearable breath tracking device

Info

Publication number: WO2023152663A1
Application number: PCT/IB2023/051141
Authority: WO
Inventors: Eduard Johannis Adrianus REUVERS
Original assignee: Reuvers Eduard Johannis Adrianus
Priority date: 2022-02-11
Filing date: 2023-02-09
Publication date: 2023-08-17

Abstract

The present disclosure provides a wearable breath tracking device, and a system and method for operation of the device. The system includes a wearable breath tracking device adapted to be removably fitted on a nose of a user. The device includes a first set of sensors adapted to be positioned inside one or both nostrils of the user and configured to generate signals indicative of an air pressure. The system further includes a controller configured to receive, from the first set of sensors, signals indicative of the air pressure in one or both nostrils of the user; determine a peak air pressure difference defined as a deviation in values of air pressure from a mean value of air pressure during a predefined duration of time; and evaluate a breathing score based on peak air pressure difference. The breathing score is indicative of breathing fitness and health of the user.

Description

WEARABLE BREATH TRACKING DEVICE, SYSTEM AND METHOD FOR OPERATION OF WEARABLE BREATH TRACKING DEVICE

TECHNICAL FIELD

[1] The present disclosure relates in general to a wearable device for monitoring fitness and health of a user. In particular, the present disclosure relates to a wearable device for tracking breathing fitness and health of a user.

BACKGROUND

[2] Background description includes information that may be useful in understanding the present invention. It is not an admission that any of the information provided herein is prior art or relevant to the presently claimed invention, or that any publication specifically or implicitly referenced is prior art.

[3] Wearable fitness devices are commonly used to track a cardio-vascular fitness and health of a user. An equally important parameter to be tracked is the pulmonary or breathing fitness and health of the user. Conventionally, breathing fitness and health is determined by measuring airflow characteristics of the user while at rest or while performing activities, by measuring parameters of the user, such as, respiratory rate, minute volume, tidal volume, vital capacity, peak expiratory flow, end-tidal CO2, VC^max, respiratory effort, respiratory drive, etc. Such parameters may be measured using different devices, such as, a spirometer, a peak flow meter, a VO2 max metabolic measurement system, etc. However, these devices are bulky pieces of equipment, and may not be a feasible means to continuously monitor the breathing of the user during their daily activities. To better understand how the user’s breathing changes throughout the day while doing their daily activities, there is a wellfelt need to accurately monitor the actual breathing airflow of the user in a lightweight, unobtrusive manner.

[4] Measuring the actual breathing airflow during athletic exercise or while doing daily activities may be done using wearable metabolic systems such as the COSMED K5, which uses a mask and an array of diagnostic equipment worn on the back of the user. This method is not unobtrusive and does not allow the user to perform sports and athletic activity as usual during competition, and is not suitable for use during daily life as the user is not able to talk and drink and eat as usual while wearing the COSMED K5 respiratory monitoring system. [5] United States patent document USD730761S1 discloses a wearable patch and method for monitoring the breathing using an acoustic sensor. While this patch is unobtrusive, the audio signal is rather inaccurate when compared to the accuracy provided by other respiratory sensors such as airflow, oxygen, CO2, and air pressure sensors. Also, by using a patch worn on the neck or on clothing, the measurement takes place far from the nose and mouth where the breathing occurs.

[6] United States patent document US11363995B2 discloses a method for determining the respiratory rate by detecting a series of heart beats and calculating heart rate variability, which may be used in smart fitness watches. While this method is unobtrusive, it does not directly measure the airflow of the user and is thus less accurate than true airflow monitoring with direct measurement of minute volume, tidal volume, respiratory effort, and respiratory drive.

[7] PCT patent document WO 2015/008047 discloses an attachable module with respiratory sensing of temperature and humidity of the airflow of the user. It processes and combines signals from a temperature sensor and a humidity sensor to determine a respiration rate of the user, for physiological monitoring of patients in the battlefield environment, to make sure the patient is still breathing and not in medical distress. The humidity and temperature sensors are located outside of the nose and the mouth of the patient, in the vicinity of the nose and mouth of the patient. The module may be clipped to the nose of the patient to also measure heart rate using a rate sensor, but in this case the humidity and temperature sensors are still located outside of the nose. While this module may be rather unobtrusive, it focuses on medical monitoring of patients in a battlefield environment rather than tracking breathing fitness and health of athletes and people living normal lives. By only measuring respiratory rate, it is unable to accurately track minute volume, tidal volume, respiratory effort, and respiratory drive. It also does not correlate the respiratory rate of the user with the users’ level of intensity of physical activity to calculate a breathing fitness score which is relevant to athletes and people leading a regular life.

[8] There are also known various breathing monitoring systems using image sensors (such as, disclosed by patent documents US10874332B2, US8790269B2 and CN111372516A) which measure respiratory rate, but do not measure actual airflow and are thus not able to accurately measure minute volume, tidal volume, respiratory effort, and respiratory drive. These monitoring systems work only while seated or lying down, not while awake and moving about at home, outside or at work. They do not correlate the respiratory rate of the user with the users’ level of intensity of physical activity to calculate a breathing fitness score relevant for athletes and people leading a regular life.

SUMMARY

[9] In a first aspect, the present disclosure provides a system for operation of a wearable breath tracking device. The system includes a wearable breath tracking device adapted to be removably fitted on a nose of a user. The wearable breath tracking device includes a first set of sensors adapted to be positioned, on fitment of the wearable breath tracking device on the nose of the user, inside one or both nostrils of the user. The first set of sensors is configured to generate signals indicative of an air pressure in the one or both nostrils of the user. The system further includes a controller communicably coupled with the wearable breath tracking device. The controller includes a processor and a memory communicably coupled with the processor. The controller is configured to receive, from the first set of sensors of the wearable breath tracking device, signals indicative of the air pressure in one or both nostrils of the user. The controller is further configured to determine a peak air pressure difference defined as a deviation in values of air pressure from a mean value of air pressure during a predefined duration of time. The peak air pressure difference is indicative of a volume of air breathed by the user during a breathing cycle, a respiratory effort, and a natural respiratory drive of the user. The controller is further configured to evaluate a breathing score based on peak air pressure difference. The breathing score is indicative of breathing fitness and health of the user.

[10] The respiratory effort may be indicative of an effort or energy expended by breathing muscles of the user to enable the user to breathe. The natural respiratory drive may be a neurological impulse to actuate the breathing muscles of the user to enable the user to breathe.

[11] In some embodiments, the system further includes an ambient pressure sensor communicably coupled to the controller. The ambient pressure sensor is configured to generate signals indicative of an ambient pressure in a region that the user is in. The controller is further configured to determine the peak air pressure difference defined as a deviation in values of air pressure from the ambient pressure during the predefined duration of time.

[12] In some embodiments, the system further includes a movement sensor and/or a heart rate sensor communicably coupled to the controller. The movement and/or heart rate sensors are configured to generate signals indicative of an intensity of activity of the user. The controller is further configured to receive, from one or both of the movement and heart rate sensors, signals indicative of the intensity of activity of the user. The controller is further configured to update the breathing score based on peak air pressure difference and corresponding intensity of activity of the user. The intensity of activity of the user may reflect a current intensity of athletic activity or physical performance of the user. By correlating the determined peak air pressure difference and the corresponding intensity of activity of the user, the controller may improve and supplement the breathing score.

[13] In some embodiments, the system further includes any one or a combination of an oximeter sensor, a humidity sensor, a carbon-dioxide sensor, an airflow sensor, a microphone, a heart rate variability (HRV) sensor, a GPS location sensor, and a thermal sensor. The controller is configured to improve and supplement the breathing score based on peak air pressure difference of the user and data received from the any one or a combination of the oximeter sensor, humidity sensor, carbon-dioxide sensor, airflow sensor, microphone, heart rate variability (HRV) sensor, GPS location sensor, and thermal sensor.

[14] In some embodiments, the system further includes an indication unit communicably coupled with the controller. The indication unit is configured to indicate data generated by the controller during an operation of the controller.

[15] In some embodiments, the indication unit includes any one or a combination of a display device, an audio device, and a haptic device.

[16] In some embodiments, the controller is further configured to generate an alert when the breathing score of the user is outside of a desirable range of values.

[17] In some embodiments, the controller is further configured to generate an alert when peak air pressure difference corresponding to the rate of motion of the user is outside of a desirable range of values.

[18] In some embodiments, the system further includes a transceiver unit communicably coupled to the controller. The transceiver unit is configured to exchange data signals with an external device via any one or a combination of wired and wireless communication networks.

[19] In some embodiments, the controller is operatively coupled with an external device. The external device includes a computing device configured to execute instructions to host an application including an interface between the controller and a user of the external device.

[20] In some embodiments, the system further includes a learning engine communicably coupled with the controller. The learning engine is configured to be trained to predict the breathing score based on a historical data of the user pertaining to the peak air pressure difference of the user and the corresponding intensity of activity of the user.

[21] In some embodiments, the controller is further configured to generate, based on historical logs of operation, an average breathing score of the user for a predefined period of time.

[22] In some embodiments, the system further includes a storage device communicably coupled with the controller. The controller is configured to generate a log of operations and store the log of operations in the storage device.

[23] In some embodiments, the wearable breath tracking device further includes a body including a spring-loaded clip. The clip is adapted to be removably attached to the nose of the user. The clip includes first and second arms adapted to grip a region of the nose therebetween.

[24] In some embodiments, the first and second arms of the clip are adapted to grip a flare of a nostril of the user therebetween, such that the first arm is positioned outside the nostril and the second arm is positioned inside the nostril. The second arm is provided with the first set of sensors.

[25] In some embodiments, the first arm of the clip is adapted to grip a flare of a first nostril of the user, and the second arm of the clip is adapted to grip a flare of a second nostril of the user. The first and second arms are connected to the body of the wearable breath tracking device, such that the first arm is positioned inside the first nostril and the second arm is positioned inside the second nostril. The first and second arms are provided with the first set of sensors.

[26] In some embodiments, the first and second arms of the clip are adapted to grip a nasal septum of the nose of the user therebetween, such that the first arm is positioned in a first nostril of the user, and the second arm is positioned in a second nostril of the user. The first and second arms are provided with the first set of sensors.

[27] In some embodiments, the clip is adapted to be actuated by a handle.

[28] In some embodiments, the wearable breath tracking device is adapted to be positioned on the nose via a nose piercing. The first set of sensors is situated on an arm of the wearable breath tracking device that is adapted to be positioned inside the nostril through the piercing.

[29] In some embodiments, the wearable breath tracking device further includes an airflow obstruction provided, such that, upon the fitment of the wearable breath tracking device on the nose of the user, the airflow obstruction is positioned in any one or both of the nostrils of the user. The airflow obstruction facilitates more pronounced fluctuation of air pressure in the nostrils of the user.

[30] In some embodiments, the airflow obstruction is removably provided on the wearable breath tracking device.

[31] During instances when a minute volume of the user is low due to the user being at rest, inclusion of the obstruction may facilitate better measurement of air pressure as the obstruction may serve to direct airflow towards the first set of sensors. The airflow obstruction may be removed when the minute volume of the user is high, and the user requires an unrestricted airflow for optimal performance during physical exercise.

[32] In some embodiments, a degree of the airflow obstruction is adjusted using a movement mechanism configured to automatically retract and/or extend the airflow obstruction of the wearable breath tracking device.

[33] In some embodiments, the first set of sensors include a set of inhalation sensors configured to generate signals indicative of an air pressure during the inhalation in the nostrils of the user. The first set of sensors further include a set of exhalation sensors configured to generate signals indicative of an air pressure during the exhalation in the nostrils of the user.

[34] In some embodiments, the controller is further configured to determine, from the signals received from the first set of sensors, an inhalation phase, an exhalation phase, a respiratory rate, a minute volume, a tidal volume, an estimated VO2 max, a respiratory drive and an estimated peak expiratory flow of the user.

[35] In a second aspect, the present disclosure provides a method for operation of a wearable breath tracking device. The method includes providing a wearable breath tracking device adapted to be removably fitted on a nose of a user. The wearable breath tracking device includes a first set of sensors adapted to be positioned, on fitment of the wearable breath tracking device on the nose of the user, inside one or both nostrils of the user. The first set of sensors is configured to generate signals indicative of an air pressure in the one or both nostrils of the user. The method further includes receiving, by a controller, from the first set of sensors of the wearable breath tracking device communicably coupled to it, signals indicative of the air pressure in one or both nostrils of the user. The method further includes determining, by the controller, a peak air pressure difference defined as a deviation in values of air pressure from a mean value of air pressure during a predefined duration of time. The peak air pressure difference is indicative of a volume of air breathed by the user during a breathing cycle, a respiratory effort, and a natural respiratory drive of the user. The method further includes evaluating, by the controller, a breathing score based on peak air pressure difference, wherein the breathing score is indicative of breathing fitness and health of the user.

[36] In a third aspect, the present disclosure provides a wearable breath tracking device adapted to be removably fitted on a nose of a user. The wearable breath tracking device includes a first set of sensors adapted to be positioned, on fitment of the wearable breath tracking device on the nose of the user, inside one or both nostrils of the user. The first set of sensors is configured to generate signals indicative of an air pressure in the one or both nostrils of the user. The wearable breath tracking device further includes a controller communicably coupled with the wearable breath tracking device. The controller includes a processor and a memory communicably coupled with the processor. The controller is configured to receive, from the first set of sensors of the wearable breath tracking device, signals indicative of the air pressure in one or both nostrils of the user. The controller is further configured to determine a peak air pressure difference defined as a deviation in values of air pressure from a mean value of air pressure during a predefined duration of time. The peak air pressure difference is indicative of a volume of air breathed by the user during a breathing cycle, a respiratory effort, and a natural respiratory drive of the user. The controller is further configured to evaluate a breathing score based on peak air pressure difference. The breathing score is indicative of breathing fitness and health of the user.

[37] Various objects, features, aspects, and advantages of the inventive subject matter will become more apparent from the following detailed description of preferred embodiments, along with the accompanying drawing figures in which like numerals represent like components.

BRIEF DESCRIPTION OF DRAWINGS

[38] The accompanying drawings are included to provide a further understanding of the present disclosure and are incorporated in and constitute a part of this specification. The drawings illustrate exemplary embodiments of the present disclosure and, together with the description, serve to explain the principles of the present disclosure.

[39] FIG. 1 illustrates a schematic representation of a system for operation of the wearable breath tracking device, according to an embodiment of the present disclosure;

[40] FIG. 2 illustrates a schematic block diagram of a controller of the system for operation of the wearable breath tracking device of FIG. 1, according to an embodiment of the present disclosure; [41] FIG. 3 illustrates a schematic flow diagram for a method for operation of the wearable breath tracking device of FIG. 1, according to an embodiment of the present disclosure;

[42] FIGs. 4A and 4B illustrate schematic views of a wearable breath tracking device, according to an embodiment of the present disclosure;

[43] FIG. 5 illustrates a schematic view of a wearable breath tracking device, where the wearable breath tracking device is fitted to the columella, according to another embodiment of the present disclosure;

[44] FIG. 6 illustrates a schematic view of a wearable breath tracking device, where the wearable breath tracking device is fitted to both nasal flares, according to another embodiment of the present disclosure;

[45] FIGs. 7A and 7B illustrate schematic views of a wearable breath tracking device, where the wearable breath tracking device utilizes a piercing through nasal flares, according to another embodiment of the present disclosure;

[46] FIG. 8A illustrates a schematic views of a wearable breath tracking device, according to another embodiment of the present disclosure;

[47] FIG. 8B illustrates a schematic views of a wearable breath tracking device, according to another embodiment of the present disclosure;

[48] FIG. 9 illustrates an exemplary plot depicting a relationship between minute volume and intensity of activity for three users; and

[49] FIG. 10 illustrates an exemplary schematic block diagram of a hardware platform for implementation of the controller of FIG. 2.

DETAILED DESCRIPTION

[50] The following is a detailed description of embodiments of the disclosure depicted in the accompanying drawings. The embodiments are in such details as to clearly communicate the disclosure. However, the amount of detail offered is not intended to limit the anticipated variations of embodiments; on the contrary, the intention is to cover all modifications, equivalents, and alternatives falling within the spirit and scope of the present disclosure as defined by the appended claims.

[51] Wearable fitness devices are commonly used to track a cardio-vascular fitness and health of a user. An equally important parameter to be tracked is the pulmonary or breathing fitness and health of the user. Conventionally, breathing fitness and health is determined by measuring airflow characteristics of the user while at rest or while performing activities, by measuring parameters of the user, such as, respiratory rate, minute volume, tidal volume, vital capacity, peak expiratory flow, end-tidal CO2, VO2 max, respiratory effort, respiratory drive, etc. Such parameters may be measured using different devices, such as, a spirometer, a peak flow meter, a VO2 max metabolic measurement system, etc. However, these devices are bulky pieces of equipment, and may not be a feasible means to continuously monitor the breathing of the user during their daily and athletic activities. To better understand how the user’s breathing changes throughout the day while doing their daily activities, there is a well-felt need to accurately monitor the actual breathing airflow of the user in a lightweight, unobtrusive manner.

[52] There is, therefore, a requirement for a means to accurately monitor the actual breathing airflow and breathing health of a user that is unobtrusive, lightweight, and convenient to wear and carry around.

[53] In a first aspect, the present disclosure provides a system for operation of a wearable breath tracking device. The system includes a wearable breath tracking device adapted to be removably fitted on a nose of a user. The wearable breath tracking device includes a first set of sensors adapted to be positioned, on fitment of the wearable breath tracking device on the nose of the user, inside one or both nostrils of the user. The first set of sensors is configured to generate signals indicative of an air pressure in the one or both nostrils of the user. The system further includes a controller communicably coupled with the wearable breath tracking device. The controller includes a processor and a memory communicably coupled with the processor. The controller is configured to receive, from the first set of sensors of the wearable breath tracking device, signals indicative of the air pressure in one or both nostrils of the user. The controller is further configured to determine a peak air pressure difference defined as a deviation in values of air pressure from a mean value of air pressure during a predefined duration of time. The peak air pressure difference is indicative of a volume of air breathed by the user during a breathing cycle, a respiratory effort, and a natural respiratory drive of the user. The controller is further configured to evaluate a breathing score based on peak air pressure difference. The breathing score is indicative of breathing fitness and health of the user.

[54] In a second aspect, the present disclosure provides a method for operation of a wearable breath tracking device. The method includes providing a wearable breath tracking device adapted to be removably fitted on a nose of a user. The wearable breath tracking device includes a first set of sensors adapted to be positioned, on fitment of the wearable breath tracking device on the nose of the user, inside one or both nostrils of the user. The first set of sensors is configured to generate signals indicative of an air pressure in the one or both nostrils of the user. The method further includes receiving, by a controller, from the first set of sensors of the wearable breath tracking device communicably coupled to it, signals indicative of the air pressure in one or both nostrils of the user. The method further includes determining, by the controller, a peak air pressure difference defined as a deviation in values of air pressure from a mean value of air pressure during a predefined duration of time. The method further includes evaluating, by the controller, a breathing score based on peak air pressure difference, wherein the breathing score is indicative of breathing fitness and health of the user.

[55] In a third aspect, the present disclosure provides a wearable breath tracking device adapted to be removably fitted on a nose of a user. The wearable breath tracking device includes a first set of sensors adapted to be positioned, on fitment of the wearable breath tracking device on the nose of the user, inside one or both nostrils of the user. The first set of sensors is configured to generate signals indicative of an air pressure in the one or both nostrils of the user. The wearable breath tracking device further includes a controller communicably coupled with the wearable breath tracking device. The controller includes a processor and a memory communicably coupled with the processor. The controller is configured to receive, from the first set of sensors of the wearable breath tracking device, signals indicative of the air pressure in one or both nostrils of the user. The controller is further configured to determine a peak air pressure difference defined as a deviation in values of air pressure from a mean value of air pressure during a predefined duration of time. The peak air pressure difference is indicative of a volume of air breathed by the user during a breathing cycle, a respiratory effort, and a natural respiratory drive of the user. The controller is further configured to evaluate a breathing score based on peak air pressure difference. The breathing score is indicative of breathing health of the user.

[56] FIG. 1 illustrates a schematic representation of a system 100 for operation of a wearable breath tracking device 400, according to an embodiment of the present disclosure. The wearable breath tracking device 400 may be interchangeably referred to as “the device 400”. The device 400 may be adapted to be removably fitted on a nose of a user 190. The device 400 may be configured to monitor a breathing fitness and health of the user 190. In some alternate embodiments, the system 100 may include any one of the devices 500, 600, 700, 800, or 850 (shown in FIGs. 5 to 8B, respectively), instead of the device 400.

[57] The device 400 includes a first set of sensors 402 adapted to be positioned, on fitment of the device 400 on the nose of the user, inside one or both nostrils of the user 190. The first set of sensors 402 are configured to generate signals indicative of an air pressure in the one or both nostrils of the user 190.

[58] The system 100 further includes a controller 200 communicably coupled with the device 100. The controller 200 may be configured to operate the device 100. In some embodiments, the controller 200 may be a part of the device 100.

[59] The device 400, and the system 100 may be designed based on the Buteyko Breathing philosophy, which teaches that it is an indication of better breathing fitness and health when a user physically performs at a certain intensity of activity while breathing a smaller minute volume of air than they were able to before. According to Buteyko Breathing, the Bohr Effect explains how a lower minute volume leads to higher oxygen release by the blood and increased cellular oxygen uptake. It is also commonly known in various athletic disciplines that when an athlete is breathing at a very high minute volume, opening his mouth to achieve additional airflow, he is nearing his limit and near exhaustion. When an athlete is comfortable at his current intensity of activity and is breathing at a rather low minute volume, using only nasal breathing, and not requiring mouth breathing, he still has ample room to increase the intensity of his activity before reaching his limit and reaching exhaustion. Thus, it is commonly known that breathing characteristics at various levels of intensity of activity may be used to determine the level of breathing fitness and health of a person. This principle is illustrated in FIG. 9.

[60] In some other embodiments, the controller 200 may be communicably coupled to the device 100 through a communication network 102. In such embodiments, the controller 200 may be implemented on a server 104 communicably coupled to the device 100 via the communication network 102. The server 104 may be any, such as, without limitations, a stand-alone server, a remote server, cloud computing server, a dedicated server, a rack server, a server blade, a server rack, a bank of servers, a server farm, hardware supporting a part of a cloud service or system, a home server, hardware running a virtualized server, one or more processors executing code to function as a server, one or more machines performing serverside functionality as described herein, at least a portion of any of the above, some combination thereof, and the like. The communications network 102 may be a wired communication network or a wireless communication network. The wireless communication network may be any wireless communication network capable of transferring data between entities of that network such as, without limitations, a carrier network including circuit switched network, a public switched network, a Content Delivery Network (CDN) network, a Long-Term Evolution (LTE) network, a Global System for Mobile Communications (GSM) network and a Universal Mobile Telecommunications System (UMTS) network, an Internet, intranets, local area networks, wide area networks, mobile communication networks, combinations thereof, and the like.

[61] In some embodiments, the user 190 may further be provided with additional sensors. In some embodiments, the additional sensors may be included in the device 400. In some other embodiments, the additional sensors may be provided on separate devices, such as, without limitations, smart watches, smart bands, mobile devices, etc. some examples of the additional sensors may include, without limitations, heart rate sensor, movement sensor, ambient pressure sensor, oximeter sensor, humidity sensor, carbon-dioxide sensor, airflow sensor, microphone, heart rate variability (HRV) sensor, GPS location sensor, and thermal sensor.

[62] The system 100 may further include an electronic device 106. The electronic device 106 may be associated with the user 190. The electronic device 106 may be communicably coupled to the device 400, the additional sensors and the controller 200. The electronic device 106 may be used to provide data to or receive data from any one or more components of the system 100. In some instances, the electronic device 106 may include audio-visual devices, such as display screens, LED lighting displays, speakers, etc. The electronic device 106 may be any electrical, electronic, electromechanical, and computing device. The electronic device 106 may include, without limitations, a mobile device, a smart phone, a Personal Digital Assistant (PDA), a tablet computer, a phablet computer, a wearable device, a Virtual Reality/ Augment Reality (VR/AR) device, a laptop, a desktop, and the like.

[63] The system 100 may further include a transceiver unit (not shown) communicably coupled to the controller 200. The transceiver unit may be provided on the device 100. The transceiver unit may be configured to facilitate exchange of data signals between the controller 200 and the device 100 and the additional sensors through the communication network 102. In some embodiments, the transceiver unit may be part of the electronic device 106.

[64] The system 100 may further include an external device. The external device may include a computing device configured to execute instructions to host an application including an interface between the controller 200 and a user of the external device. In some embodiments, the external device may be the electronic device 106 associated with the user 190. In some embodiments, the application may an internet browser configured to access the device 100 via an interface. [65] The system 100 may further include an indication unit 108 communicably coupled with the controller 200. In some embodiments, the indication unit 108 may be provided on the electronic device 106. In some embodiments, the indication unit 108 may be a separate unit. The indication unit 108 may be configured to indicate data generated by the controller 200 during an operation of the controller 200. In some embodiments, the indication unit 108 may be configured to indicate the data in the form of a visual data, an audio data, a haptic data, a text data, or combinations thereof. In some embodiments, the indication unit 108 may include any one or a combination of a display device, an audio device, and a haptic device (not shown).

[66] Further, the system 100 may also include other units such as a display unit, an input unit, an output unit and the like; however, the same are not shown in the FIG. 1, for the purpose of clarity. Also, in FIG. 1, only few units are shown; however, the system 100 may include multiple such units or the system 100 may include any such numbers of the units, obvious to a person skilled in the art or as required to implement the features of the present invention. The system 100 may include a hardware device including a processor executing machine-readable program instructions. The “hardware” may include a combination of discrete components, an integrated circuit, an application-specific integrated circuit, a field programmable gate array, a digital signal processor, or other suitable hardware. The “software” may include one or more objects, agents, threads, lines of code, subroutines, separate software applications, two or more lines of code or other suitable software structures operating in one or more software applications or on one or more processors. The processor may include, for example, without limitations, microprocessors, microcomputers, microcontrollers, digital signal processors, central processing units, state machines, logic circuits, any devices that manipulate data or signals based on operational instructions, and the like. Among other capabilities, the processor may fetch and execute computer-readable instructions in the memory operationally coupled with the system 100 for performing tasks such as data processing, input/output processing, feature extraction, and/or any other functions. Any reference to a task in the present disclosure may refer to an operation being or that may be performed on data.

[67] FIG. 2 illustrates a schematic block diagram of the controller 200 of the system 100, according to an embodiment of the present disclosure. The controller 200 includes a processor 202, and a memory 204 communicably coupled to the processor 202. The memory 204 may store instructions executable by the processor 202 to implement the functionality of the controller 200. The controller 200 further includes an interface 206. The interface 206 may include a variety of interfaces, for example, interfaces for data input and output devices, referred to as I/O devices, storage devices, and the like. The interface 206 may also provide a communication pathway for one or more components of the controller 200. The controller 200 may be communicably coupled to a database 250. The database 250 may be configured to store data generated during operation of the controller 200. An example of the data generated may include logs of operation. The database 250 may also be configured to store other data such as data pertaining to the user of the device 500 (shown in FIG. 1).

[68] The controller 200 further includes a processing engine 210. The processing engine 210 may be implemented as a combination of hardware and programming (for example, programmable instructions) to implement one or more functionalities of the processing engine 210. In some examples, the processing engine 210 may be implemented by electronic circuitry.

[69] Referring now to FIGs. 1 and 2, the processing engine 210 includes an air pressure detection engine 212, a peak air pressure difference engine 214, a breathing score engine 216, an additional sensors engine 218, an alert engine 220, a notification engine 222, a learning engine 224, and other engine(s) 226. The other engine(s) 226 may include engines configured to perform one or more functions ancillary functions associated with the processing engine 210.

[70] The air pressure detection engine 212 is configured to receive, from the first set of sensors 402 of the device 400, signals indicative of the air pressure in one or both nostrils of the user 190. In some embodiments, the air pressure in the one or both nostrils may be detected by the first set of sensors 402 continuously. In some other embodiments, the air pressure in the one or both nostrils may be detected by the first set of sensors 402 intermittently at regular intervals.

[71] The peak air pressure difference engine 214 is configured to determine a peak air pressure difference. The peak air pressure difference may be defined as a deviation in values of air pressure from a mean value of air pressure during a predefined duration of time. In some embodiments, the predefined duration of time may be one or more breathing cycles of the user 190. In some embodiments, the predefined duration of time may be any duration of time during which a fluctuation may be present in the detected air pressure. In some embodiments, more recently measured air pressure values may be given a higher weight in the calculation of the peak air pressure difference. In some cases, the peak air pressure difference may also be defined as the average deviation of the air pressure measured by the first set of sensors 402 from a mean value of air pressure during the predefined duration of time. The peak air pressure difference is indicative of a volume of air breathed by the user 190 during a breathing cycle. The peak air pressure difference is further indicative of respiratory effort and natural respiratory drive of the user 190. The respiratory effort is the intensity of the effort made by the breathing muscles of the user 190. The natural respiratory drive is a neurological impulse of the user 190 to breathe.

[72] In some embodiments, an additional sensor provided at the device 400 or provided in the system 100 may be an ambient pressure sensor. The ambient pressure sensor may be communicably coupled to the controller 200. The ambient pressure sensor may be configured to generate signals indicative of an ambient pressure in a region that the user 190 is in. The peak air pressure difference engine 214 may be further configured to determine the peak air pressure difference defined as a deviation in values of air pressure from the ambient pressure during the predefined duration of time. In some cases, the peak air pressure difference may also be defined as the average deviation of the air pressure measured by the first set of sensors 402 from the ambient air pressure during the predefined duration of time. It would be obvious to a person ordinarily skilled in the art that other roughly equivalent peak air pressure difference values may be determined using other calculation methods based on reflecting the variance of the air pressure values measured in the nostrils over the course of a full breathing cycle defined as an inhalation and exhalation.

[73] In some embodiments, the peak air pressure difference engine 214 may be further configured to determine an inhalation phase and an exhalation phase of the user 190 based on whether the pressure inside the one or both nostrils of the user 190 is continuously lower or higher, respectively, relative to the ambient pressure in the region that the user 190 is in.

[74] The air pressure measured in the nostrils will naturally be higher than the ambient air pressure during exhalations and it will be lower than the ambient air pressure during inhalations, provided the user is breathing forcefully enough so that the airflow causes a fluctuation of air pressure in the nostrils. During the course of a breathing cycle composed of the inhalation and exhalation phases, the air pressure measured in the nostrils will reach a maximum peak value with its associated maximum deviation from the ambient air pressure during exhalation, and a minimum peak value with its associated maximum deviation from the ambient air pressure during inhalation. The variance of the measured air pressure values during a breathing cycle is most pronounced if the air pressure is measured inside the nostrils rather than outside the nostrils. Measuring the air pressure on the clip inside the nasal cavity has the additional benefit of being unobtrusive. [75] In some embodiments, the first set of sensors 402 may include a set of inhalation sensors configured to generate signals indicative of an air pressure during the inhalation in the nostrils of the user 190. The inhalation sensors may be positioned in such a way that the inhalation airflow directly flows into the inhalation sensors, thus creating a larger variance in air pressure values measured during the course of the inhalation. In some embodiments, the first set of sensors 402 may include a set of exhalation sensors configured to generate signals indicative of an air pressure during the exhalation in the nostrils of the user 190. The exhalation sensors may be positioned in such a way that the exhalation airflow directly flows into the inhalation sensors, thus creating a larger variance in air pressure values measured during the course of the exhalation.

[76] In some embodiments, the peak air pressure difference engine 214 may be further configured to determine a respiratory rate, a minute volume and a tidal volume of the user 190. In some embodiments, dimensions of the user’s nasal airway passages and the characteristics of the airflow through the nasal passages may be used as an input for the peak air pressure difference engine to aid in the determination of minute volume and tidal volume of the user based on the air pressure measurements.

[77] The breathing score engine 216 is configured to evaluate a breathing score based on peak air pressure difference. The breathing score is indicative of breathing health of the user 190. The breathing score may be evaluated as a value in a scale, or as a percentage.

[78] The additional sensors engine 218 may be configured to receive signals from the additional sensors provided in the device 400 or by the user 190. The signals from the additional sensors may be used to update the evaluated breathing score of the user 190. The updated breathing score may indicate an improved breathing score by correlating peak air pressure difference with the corresponding intensity of activity of the user 190.

[79] In some embodiments, the additional sensors may include any one or a combination of a movement sensor and a heart rate sensor or another sensor giving an accurate representation of the intensity of the users’ physical activity. The movement sensors and/or heart rate sensor may be configured to generate signals indicative of an intensity of activity of the user 190. The additional sensors engine 218 may be configured to receive, from one or both of the movement and heart rate sensors, signals indicative of the intensity of activity of the user. The breathing score engine 216 may be further configured to update the breathing score based on peak air pressure difference with the corresponding intensity of activity of the user 190 to determine an estimated VO2 max, a respiratory drive and an estimated peak expiratory flow. [80] The alert engine 220 may be configured to generate an alert. The alert may be generated when any of the parameters determined by the processing engine 210 is outside of normal or desirable ranges. In some embodiments, the alert engine 222 may be configured to generate the alert when the breathing score of the user 190 is outside of a desirable range of values. In some embodiments, the alert engine 222 may be configured to generate the alert when peak air pressure difference corresponding to the rate of motion of the user 190 is outside of a desirable range of values.

[81] The notification engine 222 may be configured to operate the indication unit 108 to indicate data generated by the processing engine 210. The data may include, without limitations, any one or a combination of detected air pressure in the one or both nostrils of the user 190, a peak air pressure difference, the ambient pressure, inhalation phase, exhalation phase, respiratory rate, minute volume, tidal volume, the period of the predefined duration of time, data from the additional sensors, the evaluated breathing score, the generated alerts, etc.

[82] In some embodiments, the notification engine 222 may be further configured to generate, based on historical logs of operation, an average breathing score of the user 190 for a predefined period of time. The predefined period of time may be an hour, a day, a week, a month, etc. The predefined period of time may further be a duration that the user 190 has worn the device 400.

[83] The learning engine 224 may be configured to be trained to predict the breathing score based on a historical data of the user 190 pertaining to the peak air pressure difference of the user 190.

[84] FIG. 3 illustrates a schematic flow diagram for a method 300 for operation of the device 400, according to an embodiment of the present disclosure. In some embodiments, the method 300 may be implemented for any one of the devices 500, 600, 700, 800 or 850 (shown in FIGs. 5 to 8B, respectively). Referring now to FIGs. 1 to 3, at step 302, the method 300 includes providing the device 400 adapted to be removably fitted on the nose of the user 190. At step 304, the method 300 further includes receiving, by the controller 200, from the first set of sensors 402of the device 400 communicably coupled to it, signals indicative of the air pressure in one or both nostrils of the user 190. At step 306, the method 600 further includes determining, by the controller 200, the peak air pressure difference defined as a deviation in values of air pressure from a mean value of air pressure during a predefined duration of time. At step 308, the method 600 further includes evaluating, by the controller 200, the breathing score based on peak air pressure difference, wherein the breathing score is indicative of breathing health of the user 190. [85] FIGs.4A and 4B illustrate schematic views of the device 400, according to an embodiment of the present disclosure. The device 400 is adapted to be removably fitted on a nose of a user (for e.g., the user 190 shown in FIG. 1). The device 400 includes a body 410including a spring-loaded clip 412. The clip 412 is adapted to be removably attached to the nose of the user. The clip 412 includes first and second arms 414, 416 adapted to grip a region of the nose therebetween. In some embodiments, the clip is adapted to be actuated by a handle 418.

[86] In some embodiments, the first and second arms 414, 416 of the clip 412 are adapted to grip a flare of a nostril of the user therebetween, such that the first arm 414 is positioned outside the nostril and the second arm 416 is positioned inside the nostril. The second arm 416 is provided with the first set of sensors 402.

[87] FIG. 5 illustrates a schematic view of a wearable breath tracking device 500, according to another embodiment of the present disclosure. The wearable breath tracking device 500 may be interchangeably referred to as “the device 500”. The device 500 may be adapted to be removably fitted on a nose of a user (for e.g., the user 190 shown in FIG. 1). The device 500 includes a first set of sensors 502 adapted to be positioned, on fitment of the device 500 on the nose of the user, in both nostrils of the user. The first set of sensors 502 are configured to generate signals indicative of an air pressure in both nostrils of the user.

[88] The device 500 includes a body 510 including a clip 512. The clip 512 is adapted to be removably attached to the nose of the user. The clip 512 includes first and second arms 514, 516 adapted to grip a region of the nose therebetween. The first and second arms 514, 516 are coupled by a spring-loaded mechanism 518 to facilitate removal and comfortable fitting. The first and second arms 514, 516 of the clip 512 are adapted to grip a nasal septum of the nose of the user therebetween, such that the first arm 514 is positioned in a first nostrils of the user, and the second arm 516 is positioned in a second nostril of the user. The first and second arms 514, 516 are provided with the first set of sensors 502.

[89] FIG. 6 illustrates a schematic view of a wearable breath tracking device 600, according to another embodiment of the present disclosure. The wearable breath tracking device 600 may be interchangeably referred to as “the device 600”. The device 600 may be adapted to be removably fitted on a nose of a user (for e.g., the user 190 shown in FIG. 1). The device 600 includes a first set of sensors 602 adapted to be positioned, on fitment of the device 600 on the tip or bridge of the nose of the user, inboth nostrils of the user. The device 600 includes a body 610. The body 610 is adapted to fit on the flares of the nostrils of the user, around a nose ridge of the user. In some embodiments, the body 610 is a clip. Herein, the body 610 may be interchangeably referred to as the “clip 610”. The clip 610 further includes first and second arms 614, 616. The first arm 614 of the clip 610 is adapted to grip a flare of a first nostril of the user, and the second arm 616 of the clip 610 is adapted to grip a flare of a second nostril of the user. The first and second arms 614, 616 are connected to the body 610 of the device 600, such that the first arm 614 is positioned inside the first nostril and the second arm 616 is positioned inside the second nostril. The first and second arms 614, 616 are provided with the first set of sensors 602.

[90] FIGs. 7A and 7B illustrate schematic views of a wearable breath tracking device 700, according to an embodiment of the present disclosure. The wearable breath tracking device 700 may be interchangeably referred to as “the device 700”. The device 700 may be adapted to be removably fitted on a nose of a user (for e.g., the user 190 shown in FIG. 1). The device 700 includes a first set of sensors 702 adapted to be positioned, on fitment of the device 700 on the nose of the user, in one or both nostrils of the user. The device 700 includes a body 710. The body 710 includes an arm 704, and the first set of sensors 702 are disposed on an end of the arm 704. The arm 704 is adapted to be inserted through a flare of the nostril of the user, through a hole drilled in a skin of the user. When inserted, the device 700 is positioned, such that the first set of sensors 702 are located within the nostril of the user. In some embodiments, the device 700 is adapted to be positioned on the nose via a nose piercing. Referring to FIG. 7B, the device 700 may include a stopper 706 adapted to be removably coupled to a free end of the arm 704. When the arm 704 is inserted through the hole in the nose, and the stopper 706 is coupled to the free end of the arm 704, the device 700 may be secured in place.

[91] FIG. 8A illustrates a schematic view of a wearable breath tracking device 800, according to another embodiment of the present disclosure. The wearable breath tracking device 800 may be interchangeably referred to as “the device 800”. The device 800 may be adapted to be removably fitted on a nasal flare of a user (for e.g., the user 190 shown in FIG. 1). The device 800 includes a first set of sensors 802 adapted to be positioned, on fitment of the device 800 on the nasal flare of the user, inside one nostril of the user. The first set of sensors 802 are configured to generate signals indicative of an air pressure in the one nostril of the user.

[92] The device 800 includes a body 810 including a clip 812. The clip 812 is adapted to be removably attached to the nose of the user. The clip 812 includes first and second arms 814, 816 adapted to grip a region of the nose therebetween. In some embodiments, the first and second arms 814, 816 of the clip 812 are adapted to grip a flare of a nostril of the user therebetween, such that the first arm 814 is positioned outside the nostril and the second arm 816 is positioned inside the nostril. The second arm 816 is provided with the first set of sensors 802. The device 800 further includes an airflow obstruction 818 provided, such that, upon the fitment of the device 800 on the nose of the user, the airflow obstruction 818 is positioned in any one or both of the nostrils of the user. The airflow obstruction 818 directs the air with additional force into the air pressure sensor and also forces the airflow to flow around the airflow obstruction 818, facilitating an increase of the measured peak air pressure difference which helps generate a measurable peak air pressure difference in the nostrils of the user even when the user is at rest and has a low minute volume. The airflow obstruction 818 is shaped in such a way as to guide a portion of the breathing airflow to flow directly into the airflow sensor, thus creating a more pronounced measured peak air pressure difference. The airflow obstruction 818 may be shaped such to perform this function for both the inhalation and exhalation airflow. Without airflow obstruction 818, the peak air pressure difference may be zero when the user is breathing very little and very softly. To prevent the measurement of a peak air pressure difference of zero when the user is breathing very gently and also allow the user to breathe a high minute volume during physical exercise, in some embodiments the airflow obstruction 818 is removably provided on the device 800.The user may thus remove airflow obstruction 818 during physical exercise when the user needs to be able to breathe more air without any airflow obstructions. In some embodiments, a degree of the airflow obstruction 818 may be adjusted automatically using a miniature movement mechanism adapted to retract and/or extend the airflow obstruction 818 of the device 800.

[93] FIG. 8B illustrates a schematic view of a wearable breath tracking device 850, according to another embodiment of the present disclosure. The wearable breath tracking device 850 may be interchangeably referred to as “the device 850”. The device 850 may be adapted to be removably fitted on a nose of a user (for e.g., the user 190 shown in FIG. 1). The device 850 includes two sets of devices 800-1, 800-2, which are substantially similar to the device 800 shown in FIG. 8 A. the devices 800-1, 800-2 are communicably coupled to each other via a communication means, such as a cable. The devices 800-1, 800-2 are adapted to fitted into the first and second nostrils, respectively.

[94] The device 850 further includes an external computing device 860. The external computing device 860 may be similar in function to the controller 200.

[95] FIG. 9 illustrates an exemplary plot 900 depicting a relationship between minute volume and intensity of activity for three users. Specifically, the plot 900 shows three curves 902, 904, 906 corresponding to first, second, and third users. The three users may be similar to the user 190 (shown in FIG. 1), and may be provided with the device 400 (shown in FIGs. 1, 4A, 4B). The users may also alternately be provided with any one of the devices 500, 600, 700, 800 or 850 (shown in FIGs. 5 to 8B, respectively). The plot 900 depicts a variation in minute volume of the users, and corresponding intensity of activity. In the illustrated embodiment of FIG. 9, the users are performing an activity of starting from rest and walking or running at different speeds.

[96] From the curves 902, 904, 906, it may be seen that for any specific intensity of activity, the minute volume of the first user is greater than that of the second user. Similarly, it may be seen that for any specific intensity of activity, the minute volume of the second user is greater than that of the third user. In other words, for any specified intensity of activity, the minute volume of the third user is lesser than that of the first and second users. Thus, as previously described, the breathing fitness and health of the third user may be higher than that of the first and second users, and the breathing fitness and health of the second user may be higher than that of the first user. An arrow 908 accordingly indicates that better breathing fitness and health is indicated by a shift of the curve to the lower right.

[97] FIG. 10 illustrates an exemplary schematic block diagram of a hardware platform for implementation of the controller 200 shown in FIGs. 1 and 2. As shown in FIG. 1, a computer systemlOOO can include an external storage device 1010, a bus 1020, a main memory 1030, a read only memory 1040, a mass storage device 1050, communication port 1060, and a processor 1070. A person skilled in the art will appreciate that the computer system may include more than one processor and communication ports. Examples of processor 1070 include, but are not limited to, an Intel® Itanium® or Itanium 2 processor(s), or AMD® Opteron® or Athlon MP® processor(s), Motorola® lines of processors, FortiSOC™ system on chip processors or other future processors. Processor 1070 may include various modules associated with embodiments of the present invention. Communication port 1060 can be any of an RS-232 port for use with a modem-based dialup connection, a 10/100 Ethernet port, a Gigabit or 10 Gigabit port using copper or fibre, a serial port, a parallel port, or other existing or future ports. Communication port 1060 may be chosen depending on a network, such a Local Area Network (LAN), Wide Area Network (WAN), or any network to which computer system connects. Memory 1030 can be Random Access Memory (RAM), or any other dynamic storage device commonly known in the art. Read-only memory 1040 can be any static storage device(s) e.g., but not limited to, a Programmable Read Only Memory (PROM) chips for storing static information e.g., start-up or BIOS instructions for processor 1070. Mass storage 1050 may be any current or future mass storage solution, which can be used to store information and/or instructions. Exemplary mass storage solutions include, but are not limited to, Parallel Advanced Technology Attachment (PATA) or Serial Advanced Technology Attachment (SATA) hard disk drives or solid-state drives (internal or external, e.g., having Universal Serial Bus (USB) and/or Firewire interfaces), e.g. those available from Seagate (e.g., the Seagate Barracuda 7102 family) or Hitachi (e.g., the Hitachi Deskstar 7K1000), one or more optical discs, Redundant Array of Independent Disks (RAID) storage, e.g. an array of disks (e.g., SATA arrays), available from various vendors including Dot Hill Systems Corp., LaCie, Nexsan Technologies, Inc. and Enhance Technology, Inc.

[98] Bus 1020 communicatively couples processor(s) 1070 with the other memory, storage, and communication blocks. Bus 1020 can be, e.g., a Peripheral Component Interconnect (PCI) / PCI Extended (PCI-X) bus, Small Computer System Interface (SCSI), USB or the like, for connecting expansion cards, drives and other subsystems as well as other buses, such a front side bus (FSB), which connects processor 1070 to software system.

[99] Optionally, operator and administrative interfaces, e.g., a display, keyboard, and a cursor control device, may also be coupled to bus 1020 to support direct operator interaction with a computer system. Other operator and administrative interfaces can be provided through network connections connected through communication port 1060. The external storage device 1010 can be any kind of external hard-drives, floppy drives, IOMEGA® Zip Drives, Compact Disc - Read Only Memory (CD-ROM), Compact Disc-Re-Writable (CD- RW), Digital Video Disk-Read Only Memory (DVD-ROM). Components described above are meant only to exemplify various possibilities. In no way should the aforementioned exemplary computer system limit the scope of the present disclosure.

[100] It should be apparent to those skilled in the art that many more modifications besides those already described are possible without departing from the inventive concepts herein. The inventive subject matter, therefore, is not to be restricted except in the spirit of the appended claims. Moreover, in interpreting both the specification and the claims, all terms should be interpreted in the broadest possible manner consistent with the context. In particular, the terms “comprises” and “comprising” should be interpreted as referring to elements, components, or steps in a non-exclusive manner, indicating that the referenced elements, components, or steps may be present, or utilized, or combined with other elements, components, or steps that are not expressly referenced. Where the specification claims refer to at least one of something selected from the group consisting of A, B, C . . . .and N, the text should be interpreted as requiring only one element from the group, not A plus N, or B plus N, etc. The foregoing description of the specific embodiments will so fully reveal the general nature of the embodiments herein that others can, by applying current knowledge, readily modify and/or adapt for various applications such specific embodiments without departing from the generic concept, and, therefore, such adaptations and modifications should and are intended to be comprehended within the meaning and range of equivalents of the disclosed embodiments. It is to be understood that the phraseology or terminology employed herein is for the purpose of description and not of limitation. Therefore, while the embodiments herein have been described in terms of preferred embodiments, those skilled in the art will recognize that the embodiments herein can be practiced with modification within the spirit and scope of the appended claims.

[101] While the foregoing describes various embodiments of the invention, other and further embodiments of the invention may be devised without departing from the basic scope thereof. The scope of the invention is determined by the claims that follow. The invention is not limited to the described embodiments, versions, or examples, which are included to enable a person having ordinary skill in the art to make and use the invention when combined with information and knowledge available to the person having ordinary skill in the art.

Claims

: A system for operation of a wearable breath tracking device, the system comprising: a wearable breath tracking device adapted to be removably fitted on a nose of a user, the wearable breath tracking device comprising: a first set of sensors adapted to be positioned, on fitment of the wearable breath tracking device on the nose of the user, inside one or both nostrils of the user, the first set of sensors configured to generate signals indicative of an air pressure in the one or both nostrils of the user; and a controller communicably coupled with the wearable breath tracking device, the controller comprising a processor and a memory communicably coupled with the processor, the controller configured to: receive, from the first set of sensors of the wearable breath tracking device, signals indicative of the air pressure in one or both nostrils of the user; determine a peak air pressure difference defined as a deviation in values of air pressure from a mean value of air pressure during a predefined duration of time, wherein the peak air pressure difference is indicative of a volume of air breathed by the user during a breathing cycle, and a respiratory effort and natural respiratory drive of the user; and evaluate a breathing score based on peak air pressure difference, wherein the breathing score is indicative of breathing fitness and health of the user. The system of claim 1, further comprising an ambient pressure sensor communicably coupled to the controller, the ambient pressure sensor configured to generate signals indicative of an ambient pressure in a region that the user is in, wherein the controller is configured to determine the peak air pressure difference defined as a deviation in values of air pressure from the ambient pressure during the predefined duration of time. The system of claim 1, further comprising a movement sensor and/or a heart rate sensor communicably coupled to the controller, the movement and/or heart rate sensors configured to generate signals indicative of an intensity of activity of the user, and wherein the controller is configured to: receive, from one or both of the movement and heart rate sensors, signals indicative of the intensity of activity of the user; and update the breathing score based on peak air pressure difference and corresponding intensity of activity of the user. The system of claim 1, further comprising any one or a combination of an oximeter sensor, a humidity sensor, a carbon-dioxide sensor, an airflow sensor, a microphone, a heart rate variability (HRV) sensor, a GPS location sensor, and a thermal sensor, and wherein the controller is configured to update the breathing score based on peak air pressure difference of the user with data received from any one or a combination of the oximeter sensor, humidity sensor, carbon-dioxide sensor, airflow sensor, microphone, heart rate variability (HRV) sensor, GPS location sensor, and thermal sensor. The system of claim 1, further comprising an indication unit communicab ly coupled with the controller, wherein the indication unit is configured to indicate data generated by the controller during an operation of the controller. The system of claim 5, wherein the indication unit comprises any one or a combination of a display device, an audio device, and a haptic device. The system of claim 1, wherein the controller is further configured to generate an alert when the breathing score of the user is outside of a desirable range of values. The system of claim 3, wherein the controller is further configured to generate an alert when peak air pressure difference corresponding to the rate of motion of the user is outside of a desirable range of values. The system of claim 1, further comprising a transceiver unit communicably coupled to the controller, wherein the transceiver unit is configured to exchange data signals with an external device via any one or a combination of wired and wireless communication networks. The system of claim 1, wherein the controller is operatively coupled with an external device, wherein the external device comprises a computing device configured to execute instructions to host an application comprising an interface between the controller and a user of the external device. The system of claim 1, further comprising a learning engine communicably coupled with the controller, the learning engine configured to be trained to predict the breathing score based on a historical data of the user pertaining to the peak air pressure difference of the user. The system of claim 11, wherein the controller is configured to generate, based on historical logs of operation, an average breathing score of the user for a predefined period of time. The system of claim 1, further comprising a database communicably coupled with the controller, wherein the controller is configured to generate a log of operations and store the log of operations in the database. The system of claim 1, wherein the wearable breath tracking device further comprises a body comprising a spring-loaded clip, wherein the clip is adapted to be removably attached to a nose of the user, the clip comprising first, and second arms adapted to grip a region of the nose there between. The system of claim 14, wherein the first and second arms of the clip are adapted to grip a flare of a nostril of the user there between, such that the first arm is positioned outside the nostril and the second arm is positioned inside the nostril, and wherein the second arm is provided with the first set of sensors. The system of claim 14, wherein the first arm of the clip is adapted to grip a flare of a first nostril of the user, and the second arm of the clip is adapted to grip a flare of a second nostril of the user, wherein the first and second arms are connected to the body of the wearable breath tracking device, such that the first arm is positioned inside the first nostril and the second arm is positioned inside the second nostril, and wherein the first and second arms are provided with the first set of sensors. The system of claim 14, wherein the first and second arms of the clip are adapted to grip a nasal septum of the nose of the user there between, such that the first arm is positioned in a first nostril of the user, and the second arm is positioned in a second nostril of the user, and wherein the first and second arms are provided with the first set of sensors. The system of claim 14, wherein the clip is adapted to be actuated by a handle. The system of claim 1, wherein the wearable breath tracking device is adapted to be positioned on the nose via a nose piercing, and wherein the first set of sensors is situated on an arm of the wearable breath tracking device that is adapted to be positioned inside the nostril through the piercing. The system of claim 1, wherein the wearable breath tracking device further comprises an airflow obstruction provided, such that, upon the fitment of the wearable breath tracking device on the nose of the user, the airflow obstruction is positioned in any one or both of the nostrils of the user, wherein the airflow obstruction facilitates more pronounced fluctuation of the air pressure in the nostrils of the user. The system of claim 20, wherein the airflow obstruction is removably provided on the wearable breath tracking device. The system of claim 20, wherein a degree of the airflow obstruction is adjusted using a movement mechanism configured to automatically retract and/or extend the airflow obstruction of the wearable breath tracking device. The system of claim 1, wherein the first set of sensors comprise: a set of inhalation sensors configured to generate signals indicative of an air pressure during the inhalation in the nostrils of the user; and a set of exhalation sensors configured to generate signals indicative of an air pressure during the exhalation in the nostrils of the user. The system of claim 1, wherein the controller is configured to determine, from the signals received from the first set of sensors, an inhalation phase, an exhalation phase, a respiratory rate, a minute volume, a tidal volume, an estimated VCTmax, a respiratory drive, and an estimated peak expiratory flow of the user. A method for operation of a wearable breath tracking device, the method comprising: providing a wearable breath tracking device adapted to be removably fitted on a nose of a user, the wearable breath tracking device comprising: a first set of sensors adapted to be positioned, on fitment of the wearable breath tracking device on the nose of the user, inside one or both nostrils of the user, the first set of sensors configured to generate signals indicative of an air pressure in the one or both nostrils of the user; and receiving, by a controller, from the first set of sensors of the wearable breath tracking device communicably coupled to it, signals indicative of the air pressure in one or both nostrils of the user; determining, by the controller, a peak air pressure difference defined as a deviation in values of air pressure from a mean value of air pressure during a predefined duration of time, wherein the peak air pressure difference is indicative of a volume of air breathed by the user during a breathing cycle, and a respiratory effort and a natural respiratory drive of the user; and evaluating, by the controller, a breathing score based on peak air pressure difference, wherein the breathing score is indicative of breathing fitness and health of the user. A wearable breath tracking device adapted to be removably fitted on a nose of a user, the wearable breath tracking device comprising: a first set of sensors adapted to be positioned, on fitment of the wearable breath tracking device on the nose of the user, inside one or both nostrils of the user, the first set of sensors configured to generate signals indicative of an air pressure in the one or both nostrils of the user; and a controller communicably coupled with the wearable breath tracking device, the controller comprising a processor and a memory communicably coupled with the processor, the controller configured to: receive, from the first set of sensors of the wearable breath tracking device, signals indicative of the air pressure in one or both nostrils of the user; determine a peak air pressure difference defined as a deviation in values of air pressure from a mean value of air pressure during a predefined duration of time, wherein the peak air pressure difference is indicative of a volume of air breathed by the user during a breathing cycle, and a respiratory effort and a natural respiratory drive of the user; and evaluate a breathing score based on peak air pressure difference, wherein the breathing score is indicative of breathing fitness and health of the user.