Description:Technical Field [001] This disclosure relates generally to mechanical ventilators for providing respiratory assistance to patients, and more particularly to systems and methods for flushing the components of the ventilators. Background [002] Ventilators are medical devices used to provide supplemental oxygen support to patients. The ventilators may include a source of pressurized Oxygen and an air source fluidly connected to the patient through a conduit, to supply Oxygen-air mixture to the patient. A humidifier may also be present in ventilators, which humidifies the dry air-Oxygen mixture to be sent to patients. Components of the ventilator may include connecting tubes and various sensors like pressure sensors, flow sensors etc. These components are regularly exposed to the humidified air-Oxygen mixture from the humidifier and breathed-out air (from patients) which may contain moisture as well as other fluids and micro-organisms from the respiratory tract of the patient. Such exposure can adversely affect the components and even damage them over long periods of usage. It therefore becomes important to regularly clean these components, even when the ventilator is connected to the patient and is running. [003] Several technologies exist to clean these components using rinse flow. Conventionally known ventilator technologies typically require a high-pressure gas storage unit and/or a pressure regulator to deliver the rinse flow to the connecting tubes and other components of the ventilator. As such, these technologies require additional space in the device to incorporate the gas storage unit and/or requires an additional pressure regulator. Further, these technologies deliver rinse flow to either proximal pressure sensing tube, proximal flow sensing tubes, or expiratory flow sensing tubes, but not to all of them through a single device. Furthermore, some of these technologies do not have any provision to stop the delivery of the rinse flow to the proximal sensing tubes in case a proximal flow element is not connected to the patient circuit, thereby leading to system leakage. Moreover, some of these technologies deliver the rinse flow to the expiratory flow sensing tubes during the expiration phase, which results in errors in the measurements of the expiratory flow rate, and therefore requires correction. Therefore, the conventional ventilators flushing systems are bulky, costly, prone to leakage and measurement errors. SUMMARY [004] A ventilator is disclosed. In some embodiments, the ventilator includes an Oxygen source, an air source, and a mixing chamber fluidically coupled to the Oxygen source and the air source and configured to mix a supply of Oxygen from the Oxygen source and a supply of air from the air source, to generate Oxygen-air mixture. The ventilator further includes a first tube-assembly configured to couple the mixing chamber to a proximal flow element. The first tube-assembly includes a set of proximal tubes, a first control valve positioned between the mixing chamber and the set of proximal tubes, a proximal pressure sensor provided on the set of proximal tubes, and a proximal differential pressure sensor provided on the set of proximal tubes. The first control valve may be configured to open, causing flushing of at least one of the set of proximal tubes, the proximal pressure sensor, and the proximal differential pressure sensor, with the Oxygen-air mixture. The ventilator further includes an expiratory module and a second tube-assembly coupling the Oxygen source to the expiratory module. The second tube-assembly includes a set of expiratory tubes, a second control valve positioned between the Oxygen source and the set of expiratory tubes, and an expiratory differential pressure sensor provided on the set of expiratory tubes. The second control valve may be configured to open, causing flushing of the set of expiratory tubes and the expiratory differential pressure sensor, with the supply of Oxygen. [005] A ventilator is disclosed, in accordance with another embodiment. The ventilator includes an Oxygen source, an air source, and a mixing chamber fluidically coupled to the Oxygen source and the air source and configured to mix a supply of Oxygen from the Oxygen source and a supply of air from the air source, to generate Oxygen-air mixture. The ventilator further includes an expiratory module and a second tube-assembly coupling the Oxygen source to the expiratory module. The second tube-assembly may include a set of expiratory tubes, a second control valve positioned between the Oxygen source and the set of expiratory tubes, and an expiratory differential pressure sensor provided on the set of expiratory tubes. The second control valve is configured to open, causing flushing of the set of expiratory tubes and the expiratory differential pressure sensor, with the supply of Oxygen. [006] It is to be understood that both the foregoing general description and the following detailed description are exemplary and explanatory only and are not restrictive of the invention, as claimed. BRIEF DESCRIPTION OF THE DRAWINGS [007] The accompanying drawings, which are incorporated in and constitute a part of this disclosure, illustrate exemplary embodiments and, together with the description, serve to explain the disclosed principles. [008] FIG. 1 illustrates a schematic diagram of a ventilator, in accordance with an embodiment of the present disclosure. [009] FIG. 2 illustrates a magnified schematic diagram of an expiratory module of the ventilator of FIG. 1, in accordance with an embodiment of the present disclosure. [010] FIG. 3 illustrates a schematic diagram of a ventilator, in accordance with another embodiment of the present disclosure. DETAILED DESCRIPTION [011] Exemplary embodiments are described with reference to the accompanying drawings. Wherever convenient, the same reference numbers are used throughout the drawings to refer to the same or like parts. While examples and features of disclosed principles are described herein, modifications, adaptations, and other implementations are possible without departing from the spirit and scope of the disclosed embodiments. It is intended that the following detailed description be considered as exemplary only, with the true scope and spirit being indicated by the following claims. Additional illustrative embodiments are listed below. [012] In one embodiment, a schematic diagram of a ventilator 100 and in particularly a ventilator circuit is illustrated in FIG. 1, in accordance with an embodiment. The ventilator 100 may include an Oxygen source 102, an air source 104 and a mixing chamber 106. The mixing chamber 106 may be fluidically coupled to the Oxygen source 102 and the air source 104. The mixing chamber 106 may be configured to receive a supply of Oxygen from the Oxygen source 102 and a supply of air from the air source 104. The mixing chamber 106 may mix the supply of Oxygen and the supply of air to generate Oxygen-air mixture. To this end, the mixing chamber 106 may be Y-shaped member which may include two input ports to receive the supply of Oxygen and the supply of air respectively. The supply of Oxygen and the supply of air may be mixed inside the Y-shaped member to generate Oxygen-air mixture and the Oxygen-air mixture may be outputted via a single output port. The output port may be connected to the patient to supply the Oxygen-air mixture. [013] The ventilator 100 may further include a humidifier 108. As will be appreciated by those skilled in the art, the Oxygen-air mixture may cause dryness in the respiratory tract of the patient if supplied directly to the patient as is. Therefore, the Oxygen-air mixture may be passed through the humidifier 108 before supplying to the patient. The humidifier 108 may add humidity to the air Oxygen-air mixture, to reduce the dryness effect which may be otherwise caused by the dry Oxygen-air mixture. The construction and working of the humidifier 108 may be same as is being used in those already known in the art. Thereafter, the Oxygen-air mixture upon humidification may be supplied to the patient 110 (also referred to as user 110 in this disclosure). It should be noted that the various fluidic couplings, i.e., the fluidic coupling between the Oxygen source 102 and the mixing chamber 106, the fluidic coupling between the air source 104 and the mixing chamber 106, the fluidic coupling between the mixing chamber 106 and the proximal flow element 112 may be implemented via various associated tubes. [014] In some applications, especially when the ventilator 100 is for assisting breathing of a younger patient (i.e. neo-natal usage), the ventilator 100 may further include a proximal flow element 112 which may be connected to such patient for providing the Oxygen-air flow. Therefore, in such applications, the Oxygen-air mixture upon humidification may be supplied to the patient 110 via the proximal flow element 112. To this end, in some embodiments, a Y-shaped member 150 may fluidically couple the humidifier 308 with the proximal flow element 112, via an inspiratory limb 152. The Y-shaped member 150 may further provide for coupling the proximal flow element 112 with an expiratory module 126 via an expiratory limb 208. [015] It may be important to measure the gas flow rate from the Oxygen source and/or air source being supplied to the patient, to track the operation of the ventilator and monitor the breathing of the patient. In some embodiments, the gas flow rate may be determined using a proximal differential pressure sensor 116. To this end, the ventilator 100 may further include a first tube-assembly 118 which may couple the mixing chamber 106 to the proximal flow element 112. The first tube-assembly 118 may include a set of proximal tubes 120. For example, the set of proximal tubes 120 may include two proximal tubes fluidically coupling the mixing chamber 106 to the proximal flow element 112. The set of proximal tubes 120 may be made of rigid or flexible material, selected from a metal, an alloy, a plastic, or a polymer. The proximal pressure sensor 114 and the proximal differential pressure sensor 116 may be configured to measure the gas pressure within the set of proximal tubes 120 and the gas flow rate across the proximal flow element 112, respectively. It should be noted that the proximal pressure sensor 114 and the proximal differential pressure sensor 116 may be selected from the conventional pressure sensors and the differential pressure sensors already known in the art. [016] In some embodiments, the proximal differential pressure sensor 116 may be further configured to correlate and convert the respective pressure readings into gas flow readings. For example, the proximal differential pressure sensor 116 may be programmed with a suitable algorithm to enable the above corelation and conversion. As such, the proximal differential pressure sensor 116 may be able to determine the gas flow rate that is being supplied to the patient 110 during the inspiration phase (i.e. when the patient is breathing in). However, since the proximal pressure sensor 114 and the proximal differential pressure sensor 116 may be exposed to the humidified Oxygen-air mixture, the proximal pressure sensor 114 and the proximal differential pressure sensor 116 may be affected by the moisture content in the humidified Oxygen-air mixture. As such, the proximal pressure sensor 114 and the proximal differential pressure sensor 116 may require cleaning. [017] The cleaning may be performed by flushing the proximal pressure sensor 114 and the proximal differential pressure sensor 116 with the Oxygen-air mixture directly from the mixing chamber 106 (i.e. un-humidified Oxygen-air mixture). This un-humidified Oxygen-air mixture may be supplied from the mixing chamber 106 to the flushing the proximal pressure sensor 114 and the proximal differential pressure sensor 116 via the set of proximal tube 120 and a first control valve 124. The first control valve 124 may be positioned between the mixing chamber 106 and the set of proximal tubes 120. The first control valve 124 may be configured to open and close, for example, based on a sensory input. When the first control valve 124 is open, the first control valve 124 may fluidically couple the mixing chamber 106 with the set of proximal tubes 120, the proximal pressure sensor 114, and the proximal differential pressure sensor 116. As such, when the first control valve 124 is open, the first control valve 124 may flush at least one of the set of proximal tubes 120, the proximal pressure sensor 114, and the proximal differential pressure sensor 116, with the Oxygen-air mixture. The sensory input for controlling the first control valve 124 may be obtained from a control unit installed within the ventilator 100 which may sense the inspiration or the expiration phase of the patient’s breathing. To this end, in some embodiments, the first control valve 124 may be a pneumatic valve or a hydraulic valve. Further, in some embodiments, first control valve 124 may be a 2/2 flow control valve. Furthermore, in some embodiments, the first control valve 124 may be a fully-open/fully-close controlled or proportional controlled valve. [018] For the expiration phase, the ventilator 100 may include an expiratory module 126. The expiratory module 126 is further explained in detail in conjunction with FIG. 2. [019] Referring now to FIG. 2, a magnified view of the expiratory module 126 of FIG. 1 is illustrated, in accordance with some embodiments of the present disclosure. As shown in FIG. 2, the expiratory module 126 may include a moveable diaphragm 202 positioned near a gateway. The moveable diaphragm 202 may be sensitive to air pressure across it, and the air pressure may cause the moveable diaphragm 202 to move relative to gateway, to thereby open or close the gateway. During the inspiration phase (i.e., when the patient is breathing in), the actuator 206 may energize the movable diaphragm 202 to move it downwards relative to the gateway, to close the gateway, thereby blocking the passage of gas across the gateway”. Further, during expiration phase (i.e. when the patient is breathing out), the actuator 206 may de-energize the movable diaphragm 202, as a result of which the moveable diaphragm 202 may move upwards relative to gateway, to open the gateway, thereby opening the passage of air across the gateway. [020] The expiratory module 126 may further include an expiratory pressure sensor 204. The expiratory pressure sensor 204 may be fluidically coupled to the expiratory module 126 and may be used to measure the gas pressure developed within the expiratory module 126 during the inspiration phase or the expiration phase of the ventilation cycle. [021] The expiratory module 126 may further include an atmospheric vent, through which the air can be let out of the ventilator circuit 100 into the atmosphere. Therefore, the air breathed out by the patient during the expiration cycle is removed from the ventilator circuit 100 and let into the atmosphere. [022] Referring back to FIG. 1, the ventilator 100 may further include a second tube-assembly 128 coupling the Oxygen source 102 to the expiratory module 126. The second tube-assembly 128 may include a set of expiratory tubes 130. The set of expiratory tubes 130, for example, may include two expiratory tubes fluidically coupling the Oxygen source 102 to the expiratory module 126. The set of expiratory tubes 130 may be made of rigid or flexible material, selected from a metal, an alloy, a plastic, or a polymer. The second tube-assembly 128 may further include a control valve 132 (also referred to as a second control valve 132) positioned between the Oxygen source 102 and the set of expiratory tubes 130. The second tube-assembly 128 may further include an expiratory differential pressure sensor 134 which may be provided on the set of expiratory tubes 130. The second control valve 132 may be configured to open and close, based on a sensory signal. It should be noted that the sensory signal may be obtained from a control unit installed within the ventilator 100. The control unit, for example, may detect the inspiration phase of breathing and the expiration phase of breathing, and may send a corresponding signal to the second control valve 132. Accordingly, the second control valve 132 may be reconfigured to be open or closed. To this end, in some embodiments, the second control valve 132 may be a pneumatic valve or a hydraulic valve. Further, in some embodiments, the second control valve 132 may be a 2/2 flow control valve. Furthermore, in some embodiments, the second control valve 132 may be a fully-open/fully-close controlled or proportional controlled valve. [023] This second control valve 132 may cause flushing of the set of expiratory tubes 130 and the expiratory differential pressure sensor 134, with the supply of Oxygen (from the Oxygen source 102). [024] By way of an example, each of the proximal pressure sensor 114 and the expiratory pressure sensor 204 may be a MPXV5010DP pressure sensor. Further, by way of example, the proximal differential pressure sensor 116 and the expiratory differential pressure sensor 134 may be a SDP810 differential pressure sensor. [025] Additionally, in some embodiments, the ventilator 100 may further include first-type orifice restrictors 136A, 136B provided on both proximal tubes of the set of proximal tubes 120, respectively. The first-type orifice restrictors 136A, 136B may be positioned between the first control valve 132 and the proximal flow element 112. In some example embodiments, the diameter of the first-type orifice restrictors 136A, 136B may be selected to be 0.3 millimeters. This size of the first-type orifice restrictors 136A, 136B allows to maintain a flow in the direction from the mixing chamber 106 to the proximal flow element 112 (i.e., left to right) and prevent flow in the opposite direction (i.e., right to left) while maintaining the accuracy of the gas flow rate measurement across the proximal flow element 112. [026] Further, the ventilator 100 may include a second-type orifice restrictors 138A, 138B provided on each expiratory tube of the set of expiratory tubes 130 and positioned between the second control valve 132 and the expiratory module 126. The diameter of the second-type orifice restrictors 138A, 138B may be selected to be 0.1 millimeters. This size of the second-type orifices 138A, 138B may allow to maintain a small flow in the direction from the second control valve 132 to the expiratory module 126 (i.e. left to right). Alongside the second-type orifice restrictors 138A, 138B, non-return valves 140A, 140B may be provided that when activated may prevent flow in the direction from the expiratory module 126 to the second control valve 132. As such, the non-return valves 140A, 140B may one-directional valves. [027] Further, in some embodiments, the ventilator 100 may include an Oxygen pressure regulator 142 positioned between the Oxygen source 102 and the mixing chamber 106, that may regulate the pressure of the Oxygen being supplied by the Oxygen source 102. Furthermore, an air pressure regulator 144 may be provided and positioned between the air source 104 and the mixing chamber 106, that may regulate the pressure of the air being supplied by the air source 104. Both the Oxygen pressure regulator 142 and the air pressure regulator 144 may prevent an over-pressure and may further provide an indication when the respective pressure falls below a predefined pressure threshold. [028] The ventilator 100 may further include an Oxygen control proportional valve 148 positioned between the Oxygen pressure regulator 142 and the mixing chamber 106. Further, the ventilator 100 may include an air control proportional valve 146 positioned between the air pressure regulator 144 and the mixing chamber 106. [029] During cyclic ventilation, when the proximal flow element 112 is connected, as shown in FIG. 1, during inspiration phase, the first control valve 124 is open. It should be noted that the first control valve 124 may be configured into open state or closed state, based on a sensory signal obtained from a control unit provided in the ventilator circuit. The control unit, for example, may detect the inspiration phase of breathing and the expiration phase of breathing, and may send a corresponding signal to the first control valve 124. To this end, in some embodiments, the first control valve 124 may be a pneumatic or a hydraulic valve, may be a 2/2 flow control valve, and may be fully-open/fully-close controlled or proportional controlled. It should be noted that pressure (P1) at distal side of the proximal flow element 112 is less than pressure (P3) at the point at which the proximal differential pressure sensor 116 is connected to one of the set of proximal tubes 120. Further, the pressure (P5) at the orifice restrictor 136B is greater than the pressure P3 and therefore pressure P1 (i.e. P1P2), and pressure P3 is greater than pressure P4 (i.e. P3>P4). As a result of the pressure difference (dP) across the proximal differential pressure sensor 116 (i.e. P4P2, and P3>P4. The pressure differential P1