Patent Application
20230112963
The present technology relates generally to methods and apparatus for treating respiratory disorders, such as those involving controlled pressure swing adsorption to generate oxygen enriched air. Such methodologies may be implemented in an oxygen concentrator. In some examples, the technology more specifically concerns such methods and apparatus for managing the power consumption of a portable oxygen concentrator.
The respiratory system of the body facilitates gas exchange. The nose and mouth form the entrance to the airways of a patient.
The airways include a series of branching tubes, which become narrower, shorter and more numerous as they penetrate deeper into the lung. The prime function of the lung is gas exchange, allowing oxygen to move from the inhaled air into the venous blood and carbon dioxide to move in the opposite direction. The trachea divides into right and left main bronchi, which further divide eventually into terminal bronchioles. The bronchi make up the conducting airways, and do not take part in gas exchange. Further divisions of the airways lead to the respiratory bronchioles, and eventually to the alveoli. The alveolated region of the lung is where the gas exchange takes place, and is referred to as the respiratory zone. See “Respiratory Physiology”, by John B. West, Lippincott Williams & Wilkins, 9th edition published 2012.
A range of respiratory disorders exist. Examples of respiratory disorders include respiratory failure, Obesity Hyperventilation Syndrome (OHS), Chronic Obstructive Pulmonary Disease (COPD), Neuromuscular Disease (NMD) and Chest wall disorders.
Respiratory failure is an umbrella term for respiratory disorders in which the lungs are unable to inspire sufficient oxygen or exhale sufficient CO2 to meet the patient's needs. Respiratory failure may encompass some or all of the following disorders.
A patient with respiratory insufficiency (a form of respiratory failure) may experience abnormal shortness of breath on exercise.
Obesity Hyperventilation Syndrome (OHS) is defined as the combination of severe obesity and awake chronic hypercapnia, in the absence of other known causes for hypoventilation. Symptoms include dyspnea, morning headache and excessive daytime sleepiness.
Chronic Obstructive Pulmonary Disease (COPD) encompasses any of a group of lower airway diseases that have certain characteristics in common. These include increased resistance to air movement, extended expiratory phase of respiration, and loss of the normal elasticity of the lung. Examples of COPD are emphysema and chronic bronchitis. COPD is caused by chronic tobacco smoking (primary risk factor), occupational exposures, air pollution and genetic factors. Symptoms include: dyspnea on exertion, chronic cough and sputum production.
Neuromuscular Disease (NMD) is a broad term that encompasses many diseases and ailments that impair the functioning of the muscles either directly via intrinsic muscle pathology, or indirectly via nerve pathology. Some NMD patients are characterized by progressive muscular impairment leading to loss of ambulation, being wheelchair-bound, swallowing difficulties, respiratory muscle weakness and, eventually, death from respiratory failure. Neuromuscular disorders can be divided into rapidly progressive and slowly progressive. Rapidly progressive disorders are characterized by muscle impairment that worsens over months and results in death within a few years (e.g., Amyotrophic lateral sclerosis (ALS) and Duchenne muscular dystrophy (DMD) in teenagers). Variable or slowly progressive disorders are characterized by muscle impairment that worsens over years and only mildly reduces life expectancy (e.g., Limb girdle, Facioscapulohumeral and Myotonic muscular dystrophy). Symptoms of respiratory failure in NMD include: increasing generalized weakness, dysphagia, dyspnea on exertion and at rest, fatigue, sleepiness, morning headache, and difficulties with concentration and mood changes.
Chest wall disorders are a group of thoracic deformities that result in inefficient coupling between the respiratory muscles and the thoracic cage. The disorders are usually characterized by a restrictive defect and share the potential of long term hypercapnic respiratory failure. Scoliosis and/or kyphoscoliosis may cause severe respiratory failure. Symptoms of respiratory failure include: dyspnea on exertion, peripheral oedema, orthopnea, repeated chest infections, morning headaches, fatigue, poor sleep quality and loss of appetite.
Various respiratory therapies, such as Non-invasive ventilation (NIV), Invasive ventilation (IV), and High Flow Therapy (HFT) have been used to treat one or more of the above respiratory disorders.
Respiratory pressure therapy (RPT) is the application of a supply of air to an entrance to the airways at a controlled target pressure that is nominally positive with respect to atmosphere throughout the patient's breathing cycle (in contrast to negative pressure therapies such as the tank ventilator or cuirass).
Non-invasive ventilation (NIV) provides ventilatory support to a patient through the upper airways to assist the patient breathing and/or maintain adequate oxygen levels in the body by doing some or all of the work of breathing. The ventilatory support is provided via a non-invasive patient interface. NIV has been used to treat respiratory failure, in forms such as OHS, COPD, NMD and Chest Wall disorders. In some forms, the comfort and effectiveness of these therapies may be improved.
Invasive ventilation (IV) provides ventilatory support to patients that are no longer able to effectively breathe themselves and may be provided using a tracheostomy tube. In some forms, the comfort and effectiveness of these therapies may be improved.
Not all respiratory therapies aim to deliver a prescribed therapeutic pressure. Some respiratory therapies aim to deliver a prescribed respiratory volume, by delivering an inspiratory flow rate profile over a targeted duration, possibly superimposed on a positive baseline pressure. In other cases, the interface to the patient's airways is ‘open’ (unsealed) and the respiratory therapy may only supplement the patient's own spontaneous breathing with a flow of conditioned or enriched air. In one example, High Flow therapy (HFT) is the provision of a continuous, heated, humidified flow of air to an entrance to the airway through an unsealed or open patient interface at a “treatment flow rate” that is held approximately constant throughout the respiratory cycle. The treatment flow rate is nominally set to exceed the patient's peak inspiratory flow rate. HFT has been used to treat respiratory failure, COPD, and other respiratory disorders. One mechanism of action is that the high flow rate of air at the airway entrance improves ventilation efficiency by flushing, or washing out, expired CO2 from the patient's anatomical deadspace. Hence, HFT is thus sometimes referred to as a deadspace therapy (DST). Other benefits may include the elevated warmth and humidification (possibly of benefit in secretion management) and the potential for modest elevation of airway pressures. As an alternative to constant flow rate, the treatment flow rate may follow a profile that varies over the respiratory cycle.
Another form of flow therapy is long-term oxygen therapy (LTOT) or supplemental oxygen therapy. Doctors may prescribe a continuous flow of oxygen enriched air at a specified oxygen concentration (from 21%, the oxygen fraction in ambient air, to 100%) at a specified flow rate (e.g., 1 litre per minute (LPM), 2 LPM, 3 LPM, etc.) to be delivered to the patient's airway.
For certain patients, oxygen therapy may be combined with a respiratory pressure therapy or HFT by adding supplementary oxygen to the pressurized flow of air. When oxygen is added to respiratory pressure therapy, this is referred to as RPT with supplementary oxygen. When oxygen is added to HFT, the resulting therapy is referred to as HFT with supplementary oxygen.
These respiratory therapies may be provided by a respiratory therapy system or device. Such systems and devices may also be used to screen, diagnose, or monitor a condition without treating it. A respiratory therapy system as described herein may comprise an oxygen source, an air circuit, and a patient interface.
Experts in this field have recognized that exercise for respiratory failure patients provides long term benefits that slow the progression of the disease, improve quality of life and extend patient longevity. Most stationary forms of exercise like tread mills and stationary bicycles, however, are too strenuous for these patients. As a result, the need for mobility has long been recognized. Until recently, this mobility has been facilitated by the use of small compressed oxygen tanks or cylinders mounted on a cart with dolly wheels. The disadvantage of these tanks is that they contain a finite amount of oxygen and are heavy, weighing about 50 pounds when mounted.
Oxygen concentrators have been in use for about 50 years to supply oxygen for respiratory therapy. Oxygen concentrators may implement cyclic processes such as vacuum swing adsorption (VSA), pressure swing adsorption (PSA), or vacuum pressure swing adsorption (VPSA). For example, oxygen concentrators may work based on depressurization (e.g., vacuum operation) and/or pressurization (e.g., compressor operation) in a swing adsorption process (e.g., Vacuum Swing Adsorption, Pressure Swing Adsorption or Vacuum Pressure Swing Adsorption, each of which are referred to herein as a “swing adsorption process”). Pressure swing adsorption may involve using one or more compressors to increase gas pressure inside one or more canisters that contains particles of a gas separation adsorbent. Such a canister when containing a mass of gas separation adsorbent such as a layer of gas separation adsorbent may be referred to as a sieve bed. As the pressure increases, certain molecules in the gas may become adsorbed onto the gas separation adsorbent. Removal of a portion of the gas in the canister under the pressurized conditions allows separation of the non-adsorbed molecules from the adsorbed molecules. The adsorbed molecules may then be desorbed by venting the canisters. Further details regarding oxygen concentrators may be found, for example, in U.S. patent application Ser. No. 12/163,549, entitled “Oxygen Concentrator Apparatus and Method”, which published as U.S. Publication No. 2009/0065007 A1 on Mar. 12, 2009 and is incorporated herein by reference.
Ambient air usually includes approximately 78% nitrogen and 21% oxygen with the balance comprised of argon, carbon dioxide, water vapor and other trace gases. If a feed gas mixture such as air, for example, is passed under pressure through a canister containing a gas separation adsorbent that attracts nitrogen more strongly than it does oxygen, part or all of the nitrogen will be adsorbed by the adsorbent, and the gas coming out of the canister will be enriched in oxygen. When the adsorbent reaches the end of its capacity to adsorb nitrogen, the adsorbed nitrogen may be desorbed by venting. The canister is then ready for another cycle of producing oxygen enriched air. By alternating pressurization of the canisters in a two-canister system, one canister can be separating (or concentrating) oxygen (the “adsorption phase”) while the other canister is being vented (resulting in a near-continuous separation of oxygen from the air). This alternation results in a near-continuous separation of the oxygen from the nitrogen. In this manner, oxygen enriched air can be accumulated, such as in a storage container or other pressurizable vessel or conduit coupled to the canisters, for a variety of uses including providing supplemental oxygen to users.
Vacuum swing adsorption (VSA) provides an alternative gas separation technique. VSA typically draws the gas through the separation process of the canisters using a vacuum such as a compressor configured to create a vacuum within the canisters. Vacuum Pressure Swing Adsorption (VPSA) may be understood to be a hybrid system using a combined vacuum and pressurization technique. For example, a VPSA system may pressurize the canisters for the separation process and also apply a vacuum for depressurizing the canisters.
Traditional oxygen concentrators have been bulky and heavy making ordinary ambulatory activities with them difficult and impractical. Recently, companies that manufacture large stationary oxygen concentrators began developing portable oxygen concentrators (POCs). The advantage of POCs is that they can produce a theoretically endless supply of oxygen and provide mobility for patients (users). In order to make these devices small for mobility, the various systems necessary for the production of oxygen enriched air are condensed. POCs seek to utilize their produced oxygen as efficiently as possible, in order to minimize weight, size, and power consumption. In some implementations, this may be achieved by delivering the oxygen as series of pulses, each pulse or “bolus” timed to coincide with the onset of inhalation. This therapy mode is known as pulsed oxygen delivery (POD) or demand mode, in contrast with traditional continuous flow delivery more suited to stationary oxygen concentrators. POD mode may be implemented with a conserver, which is essentially an active valve with a sensor to determine the onset of inhalation.
An air circuit is a conduit or a tube constructed and arranged to allow, in use, a flow of air to travel between two components of a respiratory therapy system such as the oxygen source and the patient interface. In some cases, there may be separate limbs of the air circuit for inhalation and exhalation. In other cases, a single limb air circuit is used for both inhalation and exhalation.
A patient interface may be used to interface respiratory equipment to its wearer, for example by providing a flow of air to an entrance to the airways. The flow of air may be provided via a mask to the nose and/or mouth, a tube to the mouth or a tracheostomy tube to the trachea of a patient. Depending upon the therapy to be applied, the patient interface may form a seal (e.g., with a region of the patient's face) to facilitate the delivery of gas at a pressure at sufficient variance with ambient pressure to effect therapy (e.g., at a positive pressure of about 10 cmH2O relative to ambient pressure). For other forms of therapy, such as the delivery of oxygen, the patient interface may not include a seal sufficient to facilitate delivery to the airways of a supply of gas at a positive pressure of about 10 cmH2O. For flow therapies such as nasal HFT, the patient interface is configured to insufflate the nares but specifically to avoid a complete seal. One example of such a patient interface is a nasal cannula.
Examples of the present technology may provide methods and apparatus for controlled operations of an oxygen concentrator, such as a portable oxygen concentrator (POC). In particular, the technology provides methods and apparatus for managing the power consumption of a POC. In some implementations, the POC has a prescribed mode of operation and a standby mode of operation. During a prescribed mode of operation, the POC may be configured to deliver a prescribed therapeutic pressure, volume, and/or concentration of oxygen to a user. During a standby mode of operation, the POC may power off or reduce the power provided to one or more components. In some implementations, the POC may be configured to automatically switch between different modes of operation based on whether and/or how the POC is being used.
In accordance with one aspect of the present technology, there is disclosed an oxygen concentration system comprising a compression system, a canister system, a pressure sensor, and one or more processors. The compression system is configured to generate a pressurized stream of ambient air. The canister system comprises a canister containing a gas separation adsorbent, wherein the gas separation adsorbent is configured to separate at least some nitrogen from the pressurized stream of ambient air to produce oxygen enriched air. The pressure sensor is configured to generate pressure signals, and pneumatically coupled to a delivery conduit for providing a user with the oxygen enriched air. The one or more processors are communicatively coupled to the pressure sensor, and configured to: compare a trigger threshold with the pressure signals generated by the pressure sensor to detect breaths of the user; transition the oxygen concentration system to a prescribed mode of operation when a number of detected breaths during a first predetermined period of time is greater than a first predetermined threshold, wherein a predetermined volume or concentration of oxygen enriched air is supplied by the oxygen concentration system to the user during the prescribed mode of operation; and transition the oxygen concentration system to a standby mode of operation when a number of detected breaths during a second predetermined period of time is less than a second predetermined threshold, wherein a reduced power is provided to the compression system during the standby mode of operation.
In some implementations, the predetermined volume or concentration of oxygen enriched air is supplied by the oxygen concentration system to the user as a series of boluses during the prescribed mode of operation. In some implementations, the prescribed mode of operation comprises a hybrid mode of delivery.
In some implementations, during the standby mode of operation, a reduced volume or concentration of oxygen enriched air, relative to the predetermined volume or concentration of oxygen enriched air, is supplied by the oxygen concentration system to the user. In some implementations, during the standby mode of operation, no oxygen enriched air is supplied by the oxygen concentration system to the user. In some implementations, the compression system is powered off during the standby mode of operation. In some implementations, the pressure sensor is powered on during the standby mode of operation.
In some implementations, the oxygen concentration system is a portable oxygen concentrator comprising an internal power source.
In accordance with another aspect of the present technology, there is disclosed an oxygen concentration system comprising a compression system, a canister system, a movement sensor, and one or more processors. The compression system is configured to generate a pressurized stream of ambient air. The canister system comprises a canister containing a gas separation adsorbent, wherein the gas separation adsorbent is configured to separate at least some nitrogen from the pressurized stream of ambient air to produce oxygen enriched air. The movement sensor is configured to generate a movement signal. The one or more processors are communicatively coupled to the movement sensor, and configured to: transition the oxygen concentration system to a prescribed mode of operation when an estimated energy content of the movement signal generated by the movement sensor during a first predetermined period of time is greater than a first predetermined threshold, wherein a predetermined volume or concentration of oxygen enriched air is supplied by the oxygen concentration system to a user during the prescribed mode of operation; and transition the oxygen concentration system to a standby mode of operation when an estimated energy content of the movement signal generated by the movement sensor during a second predetermined period of time is less than a second predetermined threshold, wherein a reduced power is provided to the compression system during the standby mode of operation.
In some implementations, the movement sensor is powered on during the standby mode of operation. In some implementations, the movement sensor comprises an accelerometer coupled to a delivery conduit for providing the user with the oxygen enriched air. In some implementations, the movement sensor comprises a strain gauge coupled to a delivery conduit for providing the user with the oxygen enriched air.
In some implementations, the system further comprises a pressure sensor configured to generate pressure signals, wherein the pressure sensor is pneumatically coupled to a delivery conduit for providing the user with oxygen enriched air. In some such implementations, the one or more processors are communicatively coupled to the pressure sensor, and further configured to: adjust a trigger threshold based on an initial pressure signal obtained from the pressure sensor and the movement signal obtained from the movement sensor, and compare the adjusted trigger threshold with a subsequent pressure signal obtained from the pressure sensor to determine when to provide the user with a bolus of oxygen enriched air through the conduit.
As noted above, in some implementations, the system further comprises a pressure sensor configured to generate pressure signals, wherein the pressure sensor is pneumatically coupled to a delivery conduit for providing the user with oxygen enriched air. In some such implementations, the one or more processors are communicatively coupled to the pressure sensor, and further configured to: compare a trigger threshold with the pressure signals generated by the pressure sensor to detect breaths of the user; transition the oxygen concentration system to the prescribed mode of operation when (a) an estimated energy content of the movement signal generated by the movement sensor during the first predetermined period of time is greater than the first predetermined threshold and (b) a number of detected breaths during a third predetermined period of time is greater than a third predetermined threshold; and transition the oxygen concentration system to a standby mode of operation when (a) an estimated energy content of the movement signal generated by the movement sensor during the second predetermined period of time is less than the second predetermined threshold and (b) a number of detected breaths during a fourth predetermined period of time is greater than a fourth predetermined threshold.
As noted above, in some implementations, the system further comprises a pressure sensor configured to generate pressure signals, wherein the pressure sensor is pneumatically coupled to a delivery conduit for providing the user with oxygen enriched air. In some such implementations, the one or more processors are communicatively coupled to the pressure sensor, and further configured to: compare a trigger threshold with the pressure signals generated by the pressure sensor to detect breaths of the user; transition the oxygen concentration system to the prescribed mode of operation when (a) an estimated energy content of the movement signal generated by the movement sensor during a third predetermined period of time is greater than a third predetermined threshold and (b) a number of detected breaths during a fourth predetermined period of time is greater than a fourth predetermined threshold; and transition the oxygen concentration system to a standby mode of operation when (a) an estimated energy content of the movement signal generated by the movement sensor during a fifth predetermined period of time is less than a fifth predetermined threshold and (b) a number of detected breaths during a sixth predetermined period of time is greater than a sixth predetermined threshold. In some such implementations, the one or more processors are further configured to: transition the oxygen concentration system to the prescribed mode of operation when a number of detected breaths during a seventh predetermined period of time is greater than a seventh predetermined threshold and transition the oxygen concentration system to the standby mode of operation when a number of detected breaths during an eighth predetermined period of time is less than an eighth predetermined threshold.
In some implementations, the oxygen concentration system is a portable oxygen concentrator comprising an internal power source.
In accordance with yet another aspect of the present technology, there is disclosed a method for operating an oxygen concentration system comprising: a compression system configured to generate a pressurized stream of ambient air; a canister system comprising a canister containing a gas separation adsorbent, wherein the gas separation adsorbent is configured to separate at least some nitrogen from the pressurized stream of ambient air to produce oxygen enriched air; and at least one of (a) a pressure sensor configured to generate pressure signals, wherein the pressure sensor is pneumatically coupled to a delivery conduit for providing a user with the oxygen enriched air or (b) a movement sensor configured to generate a movement signal. The method comprises: transitioning the oxygen concentration system to a prescribed mode of operation when at least one of (a) a number of breaths detected from the pressure signals generated by the pressure sensor during a first predetermined period of time is greater than a first predetermined threshold or (b) an estimated energy content of the movement signal generated by the movement sensor during a second predetermined period of time is greater than a second predetermined threshold, wherein a predetermined volume or concentration of oxygen enriched air is supplied by the oxygen concentration system to the user during the prescribed mode of operation, and transitioning the oxygen concentration system to a standby mode of operation when at least one of (a) a number of breaths detected from the pressure signals generated by the pressure sensor during a third predetermined period of time is less than a third predetermined threshold or (b) an estimated energy content of the movement signal generated by the movement sensor during a fourth predetermined period of time is less than a fourth predetermined threshold, wherein a reduced power is provided to the compression system during the standby mode of operation.
In some implementations, the predetermined volume or concentration of oxygen enriched air is supplied by the oxygen concentration system to the user as a series of boluses during the prescribed mode of operation. In some implementations, the compression system is powered off during the standby mode of operation. In some implementations, the oxygen concentration system is a portable oxygen concentrator comprising an internal power source.
Of course, portions of the aspects may form sub-aspects of the present technology. Also, various ones of the sub-aspects and/or aspects may be combined in various manners and also constitute additional aspects or sub-aspects of the present technology. Other features of the technology will be apparent from consideration of the information contained in the following detailed description, abstract, drawings and claims.
Advantages of the present technology will become apparent to those skilled in the art with the benefit of the following detailed description of implementations and upon reference to the accompanying drawings in which similar reference numerals indicate similar components:
Aspects of the present technology are described in detail with reference to the drawing figures wherein like reference numerals identify similar or identical elements. It is to be understood that the disclosed implementations are merely examples of the technology, which may be implemented in various forms. Well-known functions or constructions are not described in detail to avoid obscuring the present disclosure in unnecessary detail. Therefore, specific structural and functional details disclosed herein are not to be interpreted as limiting, but merely as a basis for the claims and as a representative basis for teaching one skilled in the art to variously employ the present technology in virtually any appropriately detailed structure.
As described herein, oxygen concentrator 100 uses a pressure swing adsorption (PSA) process (which is cyclic) to produce oxygen enriched air. However, in other implementations, oxygen concentrator 100 may be modified such that it uses a cyclic vacuum swing adsorption (VSA) process or a cyclic vacuum pressure swing adsorption (VPSA) process to produce oxygen enriched air.
Oxygen enriched air may be produced from ambient air by pressurizing ambient air in canisters 302 and 304, which contain a gas separation adsorbent and are therefore referred to as sieve beds. Gas separation adsorbents useful in an oxygen concentrator are capable of separating at least nitrogen from an air stream to produce oxygen enriched air. Examples of gas separation adsorbents include molecular sieves that are capable of separating nitrogen from an air stream. Examples of adsorbents that may be used in an oxygen concentrator include, but are not limited to, zeolites (natural) or synthetic crystalline aluminosilicates that separate nitrogen from an air stream under elevated pressure. Examples of synthetic crystalline aluminosilicates that may be used include, but are not limited to: OXYSIV adsorbents available from UOP LLC, Des Plaines, Ill.; SYLOBEAD adsorbents available from W. R. Grace & Co, Columbia, Md.; SILIPORITE adsorbents available from CECA S.A. of Paris, France; ZEOCHEM adsorbents available from Zeochem AG, Uetikon, Switzerland; and AgLiLSX adsorbent available from Air Products and Chemicals, Inc., Allentown, Pa.
As shown in
Compression system 200 may include one or more compressors configured to compress air. Pressurized air, produced by compression system 200, may be fed into one or both of the canisters 302 and 304. In some implementations, the ambient air may be pressurized in the canisters to a target pressure approximately in a range of 13-20 pounds per square inch gauge (psig). Other target pressure values may also be used, depending on the type of gas separation adsorbent disposed in the canisters.
Coupled to each canister 302/304 are inlet valves 122/124 and outlet valves 132/134. As shown in
In some implementations, a two-step valve actuation voltage may be generated to control inlet valves 122/124 and outlet valves 132/134. For example, a high voltage (e.g., 24 V) may be applied to an inlet valve to open the inlet valve. The voltage may then be reduced (e.g., to 7 V) to keep the inlet valve open. Using less voltage to keep a valve open may use less power (Power=Voltage*Current). This reduction in voltage minimizes heat buildup and power consumption to extend run time from the power supply 180 (described below). When the power is cut off to the valve, it closes by spring action. In some implementations, the voltage may be applied as a function of time that is not necessarily a stepped response (e.g., a curved downward voltage between an initial 24 V and a final 7 V).
In an implementation, pressurized air is sent into one of canisters 302 or 304 while the other canister is being vented. For example, during use, inlet valve 122 is opened while inlet valve 124 is closed. Pressurized air from compression system 200 is forced into canister 302, while being inhibited from entering canister 304 by inlet valve 124. In an implementation, a controller 400 is electrically coupled to valves 122, 124, 132, and 134. Controller 400 includes one or more processors 410 operable to execute program instructions stored in memory 420. The program instructions configure the controller to perform various predefined methods that are used to operate the oxygen concentrator, such as the methods described in more detail herein. The program instructions may include program instructions for operating inlet valves 122 and 124 out of phase with each other, e.g., when one of inlet valves 122 or 124 is opened, the other valve is closed. During pressurization of canister 302, outlet valve 132 is closed and outlet valve 134 is opened. Similar to the inlet valves, outlet valves 132 and 134 are operated out of phase with each other. In some implementations, the voltages and the durations of the voltages used to open the input and output valves may be controlled by controller 400. The controller 400 may also include a transceiver 430 that may communicate with external devices to transmit data collected by the processor 410 or receive instructions from an external device for the processor 410.
Check valves 142 and 144 are coupled to the “product ends” of canisters 302 and 304, respectively. Check valves 142 and 144 may be one-way valves that are passively operated by the pressure differentials that occur as the canisters are pressurized and vented, or may be active valves. Check valves 142 and 144 are coupled to the canisters to allow oxygen enriched air produced during pressurization of each canister to flow out of the canister, and to inhibit back flow of oxygen enriched air or any other gases into the canister. In this manner, check valves 142 and 144 act as one-way valves allowing oxygen enriched air to exit the respective canisters during pressurization.
The term “check valve”, as used herein, refers to a valve that allows flow of a fluid (gas or liquid) in one direction and inhibits back flow of the fluid. The term “fluid” may include a gas or a mixture of gases (such as air). Examples of check valves that are suitable for use include, but are not limited to: a ball check valve; a diaphragm check valve; a butterfly check valve; a swing check valve; a duckbill valve; an umbrella valve; and a lift check valve. Under pressure, nitrogen molecules in the pressurized ambient air are adsorbed by the gas separation adsorbent in the pressurized canister. As the pressure increases, more nitrogen is adsorbed until the gas in the canister is enriched in oxygen. The nonadsorbed gas molecules (mainly oxygen) flow out of the pressurized canister when the pressure reaches a point sufficient to overcome the resistance of the check valve coupled to the canister. In one implementation, the pressure drop of the check valve in the forward direction is less than 1 psi. The break pressure in the reverse direction is greater than 100 psi. It should be understood, however, that modification of one or more components would alter the operating parameters of these valves. If the forward flow pressure is increased, there is, generally, a reduction in oxygen enriched air production. If the break pressure for reverse flow is reduced or set too low, there is, generally, a reduction in oxygen enriched air pressure.
In an exemplary implementation, canister 302 is pressurized by compressed air produced in compression system 200 and passed into canister 302. During pressurization of canister 302 inlet valve 122 is open, outlet valve 132 is closed, inlet valve 124 is closed and outlet valve 134 is open. Outlet valve 134 is opened when outlet valve 132 is closed to allow substantially simultaneous venting of canister 304 to atmosphere while canister 302 is being pressurized.
After some time, the pressure in canister 302 is sufficient to open check valve 142. Oxygen enriched air produced in canister 302 passes through check valve 142 and, in one implementation, is collected in accumulator 106.
After some further time, the gas separation adsorbent in canister 302 becomes saturated with nitrogen and is unable to separate significant amounts of nitrogen from incoming air. This point is usually reached after a predetermined time of oxygen enriched air production. In the implementation described above, when the gas separation adsorbent in canister 302 reaches this saturation point, the inflow of compressed air is stopped and canister 302 is vented to remove nitrogen. During venting of canister 302, inlet valve 122 is closed, and outlet valve 132 is opened. While canister 302 is being vented, canister 304 is pressurized to produce oxygen enriched air in the same manner described above. Pressurization of canister 304 is achieved by closing outlet valve 134 and opening inlet valve 124. After some time, the oxygen enriched air exits canister 304 through check valve 144.
During venting of canister 302, outlet valve 132 is opened allowing exhaust gas (mainly nitrogen) to exit canister 302 to atmosphere through concentrator outlet 130. In an implementation, the vented exhaust gas may be directed through muffler 133 to reduce the noise produced by releasing the pressurized gas from the canister. As exhaust gas is vented from canister 302, the pressure in the canister 302 drops, allowing the nitrogen to become desorbed from the gas separation adsorbent. The desorption of the nitrogen resets the adsorbent in canister 302 to a state that allows renewed separation of nitrogen from an air stream. Muffler 133 may include open cell foam (or another material) to muffle the sound of the gas leaving the oxygen concentrator. In some implementations, the combined muffling components/techniques for the input of air and the output of oxygen enriched air may provide for oxygen concentrator operation at a sound level below 50 decibels.
During venting of the canisters, it is advantageous that at least a majority of the nitrogen is removed. In an implementation, at least about 50%, at least about 60%, at least about 70%, at least about 80%, at least about 90%, at least about 95%, at least about 98%, or substantially all of the nitrogen in a canister is removed before the canister is re-used to separate nitrogen from air.
In some implementations, nitrogen removal may be assisted using an oxygen enriched air stream that is introduced into the canister from the other canister or stored oxygen enriched air. In an exemplary implementation, a portion of the oxygen enriched air may be transferred from canister 302 to canister 304 when canister 304 is being vented of exhaust gas. Transfer of oxygen enriched air from canister 302 to canister 304 during venting of canister 304 helps to desorb nitrogen from the adsorbent by lowering the partial pressure of nitrogen adjacent the adsorbent. The flow of oxygen enriched air also helps to purge desorbed nitrogen (and other gases) from the canister. In an implementation, oxygen enriched air may travel through flow restrictors 151, 153, and 155 between the two canisters. Flow restrictor 151 may be a trickle flow restrictor. Flow restrictor 151, for example, may be a 0.009D flow restrictor (e.g., the flow restrictor has a radius 0.009″ which is less than the diameter of the tube it is inside). Flow restrictors 153 and 155 may be 0.013D flow restrictors. Other flow restrictor types and sizes are also contemplated and may be used depending on the specific configuration and tubing used to couple the canisters. In some implementations, the flow restrictors may be press fit flow restrictors that restrict air flow by introducing a narrower diameter in their respective conduits. In some implementations, the press fit flow restrictors may be made of sapphire, metal or plastic (other materials are also contemplated).
Flow of oxygen enriched air between the canisters is also controlled by use of valve 152 and valve 154. Valves 152 and 154 may be opened for a short duration during the venting process (and may be closed otherwise) to prevent excessive oxygen loss out of the purging canister. Other durations are also contemplated. In an exemplary implementation, canister 302 is being vented and it is desirable to purge canister 302 by passing a portion of the oxygen enriched air being produced in canister 304 into canister 302. A portion of oxygen enriched air, upon pressurization of canister 304, will pass through flow restrictor 151 into canister 302 during venting of canister 302. Additional oxygen enriched air is passed into canister 302, from canister 304, through valve 154 and flow restrictor 155. Valve 152 may remain closed during the transfer process, or may be opened if additional oxygen enriched air is needed. The selection of appropriate flow restrictors 151 and 155, coupled with controlled opening of valve 154 allows a controlled amount of oxygen enriched air to be sent from canister 304 to canister 302. In an implementation, the controlled amount of oxygen enriched air is an amount sufficient to purge canister 302 and minimize the loss of oxygen enriched air through venting valve 132 of canister 302. While this implementation describes venting of canister 302, it should be understood that the same process can be used to vent canister 304 using flow restrictor 151, valve 152 and flow restrictor 153.
The pair of equalization/vent valves 152/154 work with flow restrictors 153 and 155 to optimize the gas flow balance between the two canisters. This may allow for better flow control for purging one of the canisters with oxygen enriched air from the other of the canisters. It may also provide better flow direction between the two canisters. It has been found that, while flow valves 152/154 may be operated as bi-directional valves, the flow rate through such valves varies depending on the direction of fluid flowing through the valve. For example, oxygen enriched air flowing from canister 304 toward canister 302 has a flow rate faster through valve 152 than the flow rate of oxygen enriched air flowing from canister 302 toward canister 304 through valve 152. If a single valve was to be used, eventually either too much or too little oxygen enriched air would be sent between the canisters and the canisters would, over time, begin to produce different amounts of oxygen enriched air. Use of opposing valves and flow restrictors on parallel air pathways may equalize the flow pattern of the oxygen enriched air between the two canisters. Equalizing the flow may allow for a steady amount of oxygen enriched air to be available to the user over multiple cycles and also may allow a predictable volume of oxygen enriched air to purge the other of the canisters. In some implementations, the air pathway may not have restrictors but may instead have a valve with a built-in resistance or the air pathway itself may have a narrow radius to provide resistance.
At times, oxygen concentrator may be shut down for a period of time. When an oxygen concentrator is shut down, the temperature inside the canisters may drop as a result of the loss of adiabatic heat from the compression system. As the temperature drops, the volume occupied by the gases inside the canisters will drop. Cooling of the canisters may lead to a negative pressure in the canisters. Valves (e.g., valves 122, 124, 132, and 134) leading to and from the canisters are dynamically sealed rather than hermetically sealed. Thus, outside air may enter the canisters after shutdown to accommodate the pressure differential. When outside air enters the canisters, moisture from the outside air may be adsorbed by the gas separation adsorbent. Adsorption of water inside the canisters may lead to gradual degradation of the gas separation adsorbents, steadily reducing ability of the gas separation adsorbents to produce oxygen enriched air.
In an implementation, outside air may be inhibited from entering canisters after the oxygen concentrator is shut down by pressurizing both canisters prior to shutdown. By storing the canisters under a positive pressure, the valves may be forced into a hermetically closed position by the internal pressure of the air in the canisters. In an implementation, the pressure in the canisters, at shutdown, should be at least greater than ambient pressure. As used herein the term “ambient pressure” refers to the pressure of the surroundings in which the oxygen concentrator is located (e.g., the pressure inside a room, outside, in a plane, etc.). In an implementation, the pressure in the canisters, at shutdown, is at least greater than standard atmospheric pressure (e.g., greater than 760 mmHg (Ton), 1 atm, 101,325 Pa). In an implementation, the pressure in the canisters, at shutdown, is at least about 1.1 times greater than ambient pressure; is at least about 1.5 times greater than ambient pressure; or is at least about 2 times greater than ambient pressure.
In an implementation, pressurization of the canisters may be achieved by directing pressurized air into each canister from the compression system and closing all valves to trap the pressurized air in the canisters. In an exemplary implementation, when a shutdown sequence is initiated, inlet valves 122 and 124 are opened and outlet valves 132 and 134 are closed. Because inlet valves 122 and 124 are joined together by a common conduit, both canisters 302 and 304 may become pressurized as air and/or oxygen enriched air from one canister may be transferred to the other canister. This situation may occur when the pathway between the compression system and the two inlet valves allows such transfer. Because the oxygen concentrator operates in an alternating pressurize/venting mode, at least one of the canisters should be in a pressurized state at any given time. In an alternate implementation, the pressure may be increased in each canister by operation of compression system 200. When inlet valves 122 and 124 are opened, pressure between canisters 302 and 304 will equalize, however, the equalized pressure in either canister may not be sufficient to inhibit air from entering the canisters during shutdown. In order to ensure that air is inhibited from entering the canisters, compression system 200 may be operated for a time sufficient to increase the pressure inside both canisters to a level at least greater than ambient pressure. Regardless of the method of pressurization of the canisters, once the canisters are pressurized, inlet valves 122 and 124 are closed, trapping the pressurized air inside the canisters, which inhibits air from entering the canisters during the shutdown period.
Referring to
In some implementations, compression system 200 includes one or more compressors. In another implementation, compression system 200 includes a single compressor, coupled to all of the canisters of canister system 300. Turning to
In one implementation, compressor 210 includes a single head wobble type compressor having a piston. Other types of compressors may be used such as diaphragm compressors and other types of piston compressors. Motor 220 may be a DC or AC motor and provides the operating power to the compressing component of compressor 210. Motor 220, in an implementation, may be a brushless DC motor. Motor 220 may be a variable speed motor configured to operate the compressing component of compressor 210 at variable speeds. Motor 220 may be coupled to controller 400, as depicted in
Compression system 200 inherently creates substantial heat. Heat is caused by the consumption of power by motor 220 and the conversion of power into mechanical motion. Compressor 210 generates heat due to the increased resistance to movement of the compressor components by the air being compressed. Heat is also inherently generated due to adiabatic compression of the air by compressor 210. Thus, the continual pressurization of air produces heat in the enclosure. Additionally, power supply 180 may produce heat as power is supplied to compression system 200. Furthermore, users of the oxygen concentrator may operate the device in unconditioned environments (e.g., outdoors) at potentially higher ambient temperatures than indoors, thus the incoming air will already be in a heated state.
Heat produced inside oxygen concentrator 100 can be problematic. Lithium ion batteries are generally employed as power supplies for oxygen concentrators due to their long life and light weight. Lithium ion battery packs, however, are dangerous at elevated temperatures and safety controls are employed in oxygen concentrator 100 to shutdown the system if dangerously high power supply temperatures are detected. Additionally, as the internal temperature of oxygen concentrator 100 increases, the amount of oxygen generated by the concentrator may decrease. This is due, in part, to the decreasing amount of oxygen in a given volume of air at higher temperatures. If the amount of produced oxygen drops below a predetermined amount, the oxygen concentrator 100 may automatically shut down.
Because of the compact nature of oxygen concentrators, dissipation of heat can be difficult. Solutions typically involve the use of one or more fans to create a flow of cooling air through the enclosure. Such solutions, however, require additional power from the power supply 180 and thus shorten the portable usage time of the oxygen concentrator. In an implementation, a passive cooling system may be used that takes advantage of the mechanical power produced by motor 220. Referring to
Moreover, an external rotatable armature may help the efficiency of the motor, allowing less heat to be generated. A motor having an external armature operates similar to the way a flywheel works in an internal combustion engine. When the motor is driving the compressor, the resistance to rotation is low at low pressures. When the pressure of the compressed air is higher, the resistance to rotation of the motor is higher. As a result, the motor does not maintain consistent ideal rotational stability, but instead surges and slows down depending on the pressure demands of the compressor. This tendency of the motor to surge and then slow down is inefficient and therefore generates heat. Use of an external armature adds greater angular momentum to the motor which helps to compensate for the variable resistance experienced by the motor. Since the motor does not have to work as hard, the heat produced by the motor may be reduced.
In an implementation, cooling efficiency may be further increased by coupling an air transfer device 240 to external rotatable armature 230. In an implementation, air transfer device 240 is coupled to the external armature 230 such that rotation of the external armature 230 causes the air transfer device 240 to create an air flow that passes over at least a portion of the motor. In an implementation, air transfer device 240 includes one or more fan blades coupled to the external armature 230. In an implementation, a plurality of fan blades may be arranged in an annular ring such that the air transfer device 240 acts as an impeller that is rotated by movement of the external rotatable armature 230. As depicted in
Further, referring to
In an implementation, the compressor outlet conduit 250 is composed of a heat exchange metal. Heat exchange metals include, but are not limited to, aluminum, carbon steel, stainless steel, titanium, copper, copper-nickel alloys or other alloys formed from combinations of these metals. Thus, compressor outlet conduit 250 can act as a heat exchanger to remove heat that is inherently caused by compression of the air. By removing heat from the compressed air, the number of molecules in a given volume at a given pressure is increased. As a result, the amount of oxygen enriched air that can be generated by each canister during each PSA cycle may be increased.
The heat dissipation mechanisms described herein are either passive or make use of elements required for the oxygen concentrator 100. Thus, for example, dissipation of heat may be increased without using systems that require additional power. By not requiring additional power, the run-time of the battery packs may be increased and the size and weight of the oxygen concentrator may be minimized. Likewise, use of an additional box fan or cooling unit may be eliminated. Eliminating such additional features reduces the weight and power consumption of the oxygen concentrator.
As discussed above, adiabatic compression of air causes the air temperature to increase. During venting of a canister in canister system 300, the pressure of the exhaust gas being vented from the canisters decreases. The adiabatic decompression of the gas leaving the canister causes the temperature of the exhaust gas to drop as it is vented. In an implementation, the cooled exhaust gas 327 vented from canister system 300 is directed toward power supply 180 and toward compression system 200. In an implementation, base 315 of canister system 300 receives the exhaust gas from the canisters. The exhaust gas 327 is directed through base 315 toward outlet 325 of the base 315 and toward power supply 180. The exhaust gas, as noted, is cooled due to decompression of the gases and therefore passively provide cooling to the power supply 180. When the compression system 200 is operated, the air transfer device 240 will gather the cooled exhaust gas 327 and direct the exhaust gas 327 toward the motor 220 of compression system 200. Fan 172 may also assist in directing the exhaust gas 327 across compression system 200 and out of the housing 170. In this manner, additional cooling may be obtained without requiring any further power from the battery.
Oxygen concentrator 100 may include at least two canisters, each canister including a gas separation adsorbent. The canisters of oxygen concentrator 100 may be disposed formed from a molded housing. In an implementation, canister system 300 includes two housing components 310 and 510, as depicted in
As shown, valve seats 322, 324, 332, and 334 and conduits 330 and 346 may be integrated into the housing component 310 to reduce the number of sealed connections needed throughout the air flow of the oxygen concentrator 100.
Air pathways/tubing between different sections in housing components 310 and 510 may take the form of molded conduits. Conduits in the form of molded channels for air pathways may occupy multiple planes in housing components 310 and 510. For example, the molded air conduits may be formed at different depths and at different positions in housing components 310 and 510. In some implementations, a majority or substantially all of the conduits may be integrated into the housing components 310 and 510 to reduce potential leak points.
In some implementations, prior to coupling housing components 310 and 510 together, O-rings may be placed between various points of housing components 310 and 510 to ensure that the housing components are properly sealed. In some implementations, components may be integrated and/or coupled separately to housing components 310 and 510. For example, tubing, flow restrictors (e.g., press fit flow restrictors), oxygen sensors, gas separation adsorbents, check valves, plugs, processors, power supplies, etc. may be coupled to housing components 310 and 510 before and/or after the housing components are coupled together.
In some implementations, apertures 337 leading to the exterior of housing components 310 and 510 may be used to insert devices such as flow restrictors. Apertures may also be used for increased moldability. One or more of the apertures may be plugged after molding (e.g., with a plastic plug). In some implementations, flow restrictors may be inserted into passages prior to inserting plugs to seal the passages. Press fit flow restrictors may have diameters that may allow a friction fit between the press fit flow restrictors and their respective apertures. In some implementations, an adhesive may be added to the exterior of the press fit flow restrictors to hold the press fit flow restrictors in place once inserted. In some implementations, the plugs may have a friction fit with their respective tubes (or may have an adhesive applied to their outer surface). The press fit flow restrictors and/or other components may be inserted and pressed into their respective apertures using a narrow tip tool or rod (e.g., with a diameter less than the diameter of the respective aperture). In some implementations, the press fit flow restrictors may be inserted into their respective tubes until they abut a feature in the tube to halt their insertion. For example, the feature may include a reduction in radius. Other features are also contemplated (e.g., a bump in the side of the tubing, threads, etc.). In some implementations, press fit flow restrictors may be molded into the housing components (e.g., as narrow tube segments).
In some implementations, spring baffle 139 may be placed into respective canister receiving portions of housing components 310 and 510 with the spring side of the baffle 139 facing the exit of the canister. Spring baffle 139 may apply force to gas separation adsorbent in the canister while also assisting in preventing gas separation adsorbent from entering the exit apertures. Use of a spring baffle 139 may keep the gas separation adsorbent compact while also allowing for expansion (e.g., thermal expansion). Keeping the gas separation adsorbent compact may prevent the gas separation adsorbent from breaking during movement of the oxygen concentrator 100.
In some implementations, filter 129 may be placed into respective canister receiving portions of housing components 310 and 510 facing the inlet of the respective canisters. The filter 129 removes particles from the feed gas stream entering the canisters.
In some implementations, pressurized air from the compression system 200 may enter air inlet 306. Air inlet 306 is coupled to inlet conduit 330. Air enters housing component 310 through inlet 306 and travels through inlet conduit 330, and then to valve seats 322 and 324.
In an implementation, pressurized air is sent into one of canisters 302 or 304 while the other canister is being vented. For example, during use, inlet valve 122 is opened while inlet valve 124 is closed. Pressurized air from compression system 200 is forced into canister 302, while being inhibited from entering canister 304 by inlet valve 124. During pressurization of canister 302, outlet valve 132 is closed and outlet valve 134 is opened. Similar to the inlet valves, outlet valves 132 and 134 are operated out of phase with each other. Valve seat 322 includes an opening 323 that passes through housing component 310 into canister 302. Similarly valve seat 324 includes an opening 375 that passes through housing component 310 into canister 304. Air from inlet conduit 330 passes through openings 323 or 375 if the respective valves 122 and 124 are open, and enters the respective canisters 302 and 304.
Check valves 142 and 144 (see
Oxygen enriched air from either canister travels through conduit 342 or 344 and enters conduit 346 formed in housing component 310. Conduit 346 includes openings that couple the conduit to conduit 342, conduit 344 and accumulator 106. Thus, oxygen enriched air, produced in canister 302 or 304, travels to conduit 346 and passes into accumulator 106. As illustrated in
After some time, the gas separation adsorbent will become saturated with nitrogen and will be unable to separate significant amounts of nitrogen from incoming air. When the gas separation adsorbent in a canister reaches this saturation point, the inflow of compressed air is stopped and the canister is vented to desorb nitrogen from the adsorbent. Canister 302 is vented by closing inlet valve 122 and opening outlet valve 132. Outlet valve 132 releases the exhaust gas from canister 302 into the volume defined by the end of housing component 310. Foam material may cover the end of housing component 310 to reduce the sound made by release of gases from the canisters. Similarly, canister 304 is vented by closing inlet valve 124 and opening outlet valve 134. Outlet valve 134 releases the exhaust gas from canister 304 into the volume defined by the end of housing component 310.
While canister 302 is being vented, canister 304 is pressurized to produce oxygen enriched air in the same manner described above. Pressurization of canister 304 is achieved by closing outlet valve 134 and opening inlet valve 124. The oxygen enriched air exits canister 304 through check valve 144.
In an exemplary implementation, a portion of the oxygen enriched air may be transferred from canister 302 to canister 304 when canister 304 is being vented of nitrogen. Transfer of oxygen enriched air from canister 302 to canister 304 during venting of canister 304 helps to desorb nitrogen from the adsorbent by lowering the partial pressure of nitrogen adjacent the adsorbent. The flow of oxygen enriched air also helps to purge desorbed nitrogen (and other gases) from the canister. Flow of oxygen enriched air between the canisters is controlled using flow restrictors and valves, as depicted in
Oxygen enriched air in accumulator 106 passes through supply valve 160 into expansion chamber 162 which is formed in housing component 510. An opening (not shown) in housing component 510 couples accumulator 106 to supply valve 160. In an implementation, expansion chamber 162 may include one or more devices configured to estimate an oxygen purity (fractional oxygen concentration, typically expressed as a percentage) of the gas passing through the chamber.
An outlet system, coupled to one or more of the canisters, includes one or more conduits for providing oxygen enriched air to a user. In an implementation, oxygen enriched air produced in either of canisters 302 and 304 is collected in accumulator 106 through check valves 142 and 144, respectively, as depicted schematically in
Turning to
Oxygen enriched air in accumulator 106 passes through supply valve 160 into expansion chamber 162 as depicted in
The fluid dynamics of the outlet pathway, coupled with the programmed actuations of supply valve 160, may result in a bolus of oxygen being provided at the correct time and with an amplitude profile that assures rapid delivery into the user's lungs without excessive waste.
Expansion chamber 162 may include one or more oxygen sensors adapted to determine an oxygen concentration of gas passing through the chamber. In an implementation, the oxygen concentration of gas passing through expansion chamber 162 is estimated using an oxygen sensor 165. An oxygen sensor is a device configured to measure oxygen concentration in a gas. Examples of oxygen sensors include, but are not limited to, ultrasonic oxygen sensors, electrical oxygen sensors, chemical oxygen sensors, and optical oxygen sensors. In one implementation, oxygen sensor 165 is an ultrasonic oxygen sensor that includes an ultrasonic emitter 166 and an ultrasonic receiver 168. In some implementations, ultrasonic emitter 166 may include multiple ultrasonic emitters and ultrasonic receiver 168 may include multiple ultrasonic receivers. In implementations having multiple emitters/receivers, the multiple ultrasonic emitters and multiple ultrasonic receivers may be axially aligned (e.g., across the gas flow path which may be perpendicular to the axial alignment).
In use, an ultrasonic sound wave from emitter 166 may be directed through oxygen enriched air disposed in chamber 162 to receiver 168. The ultrasonic oxygen sensor 165 may be configured to detect the speed of sound through the oxygen enriched air to determine the composition of the oxygen enriched air. The speed of sound is different in nitrogen and oxygen, and in a mixture of the two gases, the speed of sound through the mixture may be an intermediate value proportional to the relative amounts of each gas in the mixture. In use, the sound at the receiver 168 is slightly out of phase with the sound sent from emitter 166. This phase shift is due to the relatively slow velocity of sound through a gas medium as compared with the relatively fast speed of the electronic pulse through wire. The phase shift, then, is proportional to the distance between the emitter and the receiver and inversely proportional to the speed of sound through the expansion chamber 162. The density of the gas in the chamber affects the speed of sound through the expansion chamber and the density is proportional to the ratio of oxygen to nitrogen in the expansion chamber. Therefore, the phase shift can be used to measure the concentration of oxygen in the expansion chamber. In this manner the relative concentration of oxygen in the accumulator may be estimated as a function of one or more properties of a detected sound wave traveling through the accumulator.
In some implementations, multiple emitters 166 and receivers 168 may be used. The readings from the emitters 166 and receivers 168 may be averaged to reduce errors that may be inherent in turbulent flow systems. In some implementations, the presence of other gases may also be detected by measuring the transit time and comparing the measured transit time to predetermined transit times for other gases and/or mixtures of gases.
The sensitivity of the ultrasonic oxygen sensor system may be increased by increasing the distance between the emitter 166 and receiver 168, for example to allow several sound wave cycles to occur between emitter 166 and the receiver 168. In some implementations, if at least two sound cycles are present, the influence of structural changes of the transducer may be reduced by measuring the phase shift relative to a fixed reference at two points in time. If the earlier phase shift is subtracted from the later phase shift, the shift caused by thermal expansion of expansion chamber 162 may be reduced or cancelled. The shift caused by a change of the distance between the emitter 166 and receiver 168 may be approximately the same at the measuring intervals, whereas a change owing to a change in oxygen concentration may be cumulative. In some implementations, the shift measured at a later time may be multiplied by the number of intervening cycles and compared to the shift between two adjacent cycles. Further details regarding sensing of oxygen in the expansion chamber may be found, for example, in U.S. patent application Ser. No. 12/163,549, entitled “Oxygen Concentrator Apparatus and Method”, which published as U.S. Publication No. 2009/0065007 A1 on Mar. 12, 2009 and is incorporated herein by reference.
Flow rate sensor 185 may be used to determine the flow rate of gas flowing through the outlet system. Flow rate sensors that may be used include, but are not limited to: diaphragm/bellows flow meters; rotary flow meters (e.g., Hall effect flow meters); turbine flow meters; orifice flow meters; and ultrasonic flow meters. Flow rate sensor 185 may be coupled to controller 400. The rate of gas flowing through the outlet system may be an indication of the breathing volume of the user. Changes in the flow rate of gas flowing through the outlet system may also be used to determine a breathing rate of the user. Controller 400 may generate a control signal or trigger signal to control actuation of supply valve 160. Such control of actuation of the supply valve may be based on the breathing rate and/or breathing volume of the user, as estimated by flow rate sensor 185.
In some implementations, ultrasonic oxygen sensor 165 and, for example, flow rate sensor 185 may provide a measurement of an actual amount of oxygen being provided. For example, flow rate sensor 185 may measure a volume of gas (based on flow rate) provided and ultrasonic oxygen sensor 165 may provide the concentration of oxygen of the gas provided. These two measurements together may be used by controller 400 to determine an approximation of the actual amount of oxygen provided to the user.
Oxygen enriched air passes through flow rate sensor 185 to filter 187. Filter 187 removes bacteria, dust, granule particles, etc. prior to providing the oxygen enriched air to the user. The filtered oxygen enriched air passes through filter 187 to connector 190. Connector 190 may be a “Y” connector coupling the outlet of filter 187 to pressure sensor 194 and delivery conduit 192. Pressure sensor 194 may be used to monitor the pressure of the gas passing through delivery conduit 192 to the user. In some implementations, pressure sensor 194 is configured to generate a signal that is proportional to the amount of positive or negative pressure applied to a sensing surface. Changes in pressure, sensed by pressure sensor 194, may be used to determine a breathing rate of a user, as well as to detect the onset of inhalation (also referred to as the trigger instant) as described below. Controller 400 may control actuation of supply valve 160 based on the breathing rate and/or onset of inhalation of the user. In an implementation, controller 400 may control actuation of supply valve 160 based on information provided by either or both of the flow rate sensor 185 and the pressure sensor 194.
Oxygen enriched air may be provided to a user through delivery conduit 192. In an implementation, delivery conduit 192 may be a silicone tube. Delivery conduit 192 may be coupled to a user using an airway delivery device 196, as depicted in
In an alternate implementation, a mouthpiece may be used to provide oxygen enriched air to the user. As shown in
Mouthpiece 198 is removably positionable in a user's mouth. In one implementation, mouthpiece 198 is removably couplable to one or more teeth in a user's mouth. During use, oxygen enriched air is directed into the user's mouth via the mouthpiece. Mouthpiece 198 may be a night guard mouthpiece which is molded to conform to the user's teeth. Alternatively, mouthpiece may be a mandibular repositioning device. In an implementation, at least a majority of the mouthpiece is positioned in a user's mouth during use.
During use, oxygen enriched air may be directed to mouthpiece 198 when a change in pressure is detected proximate to the mouthpiece. In one implementation, mouthpiece 198 may be coupled to a pressure sensor 194. When a user inhales air through the user's mouth, pressure sensor 194 may detect a drop in pressure proximate to the mouthpiece. Controller 400 of oxygen concentrator 100 may control release of a bolus of oxygen enriched air to the user at the onset of inhalation.
During typical breathing of an individual, inhalation may occur through the nose, through the mouth or through both the nose and the mouth. Furthermore, breathing may change from one passageway to another depending on a variety of factors. For example, during more active activities, a user may switch from breathing through their nose to breathing through their mouth, or breathing through their mouth and nose. A system that relies on a single mode of delivery (either nasal or oral), may not function properly if breathing through the monitored pathway is stopped. For example, if a nasal cannula is used to provide oxygen enriched air to the user, an inhalation sensor (e.g., a pressure sensor or flow rate sensor) is coupled to the nasal cannula to determine the onset of inhalation. If the user stops breathing through their nose, and switches to breathing through their mouth, the oxygen concentrator 100 may not know when to provide the oxygen enriched air since there is no feedback from the nasal cannula. Under such circumstances, oxygen concentrator 100 may increase the flow rate and/or increase the frequency of providing oxygen enriched air until the inhalation sensor detects an inhalation by the user. If the user switches between breathing modes often, the default mode of providing oxygen enriched air may cause the oxygen concentrator 100 to work harder, limiting the portable usage time of the system.
In an implementation, mouthpiece 198 is used in combination with nasal cannula airway delivery device 196 to provide oxygen enriched air to a user, as depicted in
Operation of oxygen concentrator 100 may be performed automatically using an internal controller 400 coupled to various components of the oxygen concentrator 100, as described herein. Controller 400 includes one or more processors 410 and internal memory 420, as depicted in
In some implementations, controller 400 includes processor 410 that includes, for example, one or more field programmable gate arrays (FPGAs), microcontrollers, etc. included on a circuit board disposed in oxygen concentrator 100. Processor 410 is configured to execute programming instructions stored in memory 420. In some implementations, programming instructions may be built into processor 410 such that a memory external to the processor 410 may not be separately accessed (e.g., the memory 420 may be internal to the processor 410).
Processor 410 may be coupled to various components of oxygen concentrator 100, including, but not limited to compression system 200, one or more of the valves used to control fluid flow through the system (e.g., valves 122, 124, 132, 134, 152, 154, 160), oxygen sensor 165, pressure sensor 194, flow rate sensor 185, temperature sensors (not shown), fan 172, and any other component that may be electrically controlled. In some implementations, a separate processor (and/or memory) may be coupled to one or more of the components.
Controller 400 is configured (e.g., programmed by program instructions) to operate oxygen concentrator 100 and is further configured to monitor the oxygen concentrator 100 such as for malfunction states or other process information. For example, in one implementation, controller 400 is programmed to trigger an alarm if the system is operating and no breathing is detected by the user for a predetermined amount of time. For example, if controller 400 does not detect a breath for a period of 75 seconds, an alarm LED may be lit and/or an audible alarm may be sounded. If the user has truly stopped breathing, for example, during a sleep apnea episode, the alarm may be sufficient to awaken the user, causing the user to resume breathing. The action of breathing may be sufficient for controller 400 to reset this alarm function. Alternatively, if the system is accidentally left on when delivery conduit 192 is removed from the user, the alarm may serve as a reminder for the user to turn oxygen concentrator 100 off.
Controller 400 is further coupled to oxygen sensor 165, and may be programmed for continuous or periodic monitoring of the oxygen concentration of the oxygen enriched air passing through expansion chamber 162. A minimum oxygen concentration threshold may be programmed into controller 400, such that the controller lights an LED visual alarm and/or an audible alarm to warn the user of the low concentration of oxygen.
Controller 400 is also coupled to internal power supply 180 and may be configured to monitor the level of charge of the internal power supply. A minimum voltage and/or current threshold may be programmed into controller 400, such that the controller lights an LED visual alarm and/or an audible alarm to warn the user of low power condition. The alarms may be activated intermittently and at an increasing frequency as the battery approaches zero usable charge.
The server 460 may also be in wireless communication with the portable computing device 480 using a wireless communication protocol such as GSM. A processor of the smartphone 480 may execute a program 482 known as an “app” to control the interaction of the smartphone 480 with the user 1000, the oxygen concentrator 100, and/or the server 460. The server 460 may have access to a database 466 that stores operational data about the oxygen concentrator 100 and user 1000.
The server 460 includes an analysis engine 462 that may execute methods of operating and monitoring the oxygen concentrator 100 as further described below. The server 460 may also be in communication via the network 470 with other devices such as a personal computing device (e.g., a workstation) 464 via a wired or wireless connection. A processor of the personal computing device 464 may execute a “client” program to control the interaction of the personal computing device 464 with the server 460. One example of a client program is a browser.
In a further implementation, the server 460 may be configured to host a portal system. The portal system may receive, from the portable computing device 480 or directly from the oxygen concentrator 100, data relating to the operation of the oxygen concentrator 100. As described above, the personal computing device 464 may execute a client program such as a browser to allow a user of the personal computing device 464 (such as a representative of a home medical equipment provider) to access the operational data of the oxygen concentrator 100, and other oxygen concentrators in the connected respiratory therapy system 450, via the portal system hosted by the server 460. In this fashion, such a portal system may be utilised by an HME to manage a population of users of oxygen concentrators, e.g., the oxygen concentrator 100, in the connected respiratory therapy system 450. The portal system may provide actionable insights into user or device condition for the population of oxygen concentrators and their users based on the operational data received by the portal system. Such insights may be based on rules that are applied to the operational data.
Further functions that may be implemented with or by the controller 400 are described in detail in other sections of this disclosure. For example, the controller 400 of the oxygen concentrator 100 may implement compressor control to regulate pressure in the system. Thus, the oxygen concentrator 100 may be equipped with a pressure sensor such as the pressure sensor 107 in the accumulator 106 downstream of the canisters 302 and 304. The controller 400 in the oxygen concentrator 100 can control adjusting of the speed of the compressor 210 using signals from the pressure sensor as well as a motor speed sensor such as in one or more modes. In this regard, the controller 400 may implement dual control modes, designated a coarse pressure regulation mode and a fine pressure regulation mode. The coarse pressure regulation mode may be implemented for changing between the different flow rate settings (or “flow settings”) of the oxygen concentrator 100 and for starting/initial activation. The fine pressure regulation mode may then take over upon completion of each operation of the coarse pressure regulation mode.
In the coarse pressure regulation mode, the motor speed is set/controlled to ramp up or down depending the prior state of operations. During the ramping, the controller 400 uses the measurements from the pressure sensor to generate an estimated pressure upstream of the sensor, in the canisters. In some implementations, the estimated pressure is used in a test to terminate the ramp, e.g., when the estimated pressure reaches a predetermined target pressure value, created at manufacturing time, that is associated with the selected flow rate setting of the oxygen concentrator 100. The pressure estimate may be calculated by performing a regression (e.g., linear) using data from the pressure sensor whereby the controller 400 determines regression parameters (e.g., slope and intercept parameters of a line) from the sensor signal samples. The pressure estimate is calculated with the regression parameters and a known system response delay.
In the fine pressure regulation mode, the motor speed is controlled to regulate the pressure of the system to the target pressure value using the signal from the pressure sensor. Upon completion of the coarse pressure regulation mode, the motor speed ramping is stopped and a base motor speed is set equal to the current motor speed. Any further changes to the motor speed are implemented by a fine pressure controller such as a PID (proportional, integral, derivative) controller. During the fine pressure regulation mode, the target pressure is compared with a qualified pressure estimate to generate a first error signal that is applied to the fine pressure controller to produce a speed adjustment. By summing the speed adjustment to the base motor speed, a speed set point for the motor may be obtained. The speed set point is used for control of the motor speed using a motor controller (e.g., a PID controller).
The qualified pressure estimate for the fine pressure controller is computed using regression. In this regard, samples from the pressure signal may be applied to a best fit algorithm (e.g., linear regression) to determine regression parameters (e.g., slope and intercept of a line) of the data from the pressure signal during an adsorption phase of the PSA cycle. If the slope is positive, these parameters (slope and intercept rather than pressure samples from the pressure sensor) may then be applied with the particular time of the given adsorption phase of the PSA cycle to determine a peak value of the regression line from the linear regression. If the slope is negative, the intercept parameter may be taken as the peak value. The peak values from the regression information may be then applied to a running average buffer that maintains an average of the most recent peak values (e.g., six or more). The average peak value may then serve as the qualified pressure estimate for the fine pressure controller. Versions of such processes are discussed in more detail in U.S. Provisional No. 62/904,858, entitled “Methods and Apparatus for Control of Oxygen Concentrator,” filed on Sep. 24, 2019, the entire disclosure of which is incorporated herein by reference.
Additionally, the controller 400 of the oxygen concentrator 100 may be configured to implement supply valve control to regulate bolus size (volume) in the system, which may optionally be implemented without use of a flow rate sensor of the oxygen concentrator 100. For example, the oxygen concentrator 100 may be equipped with a pressure sensor, such as the pressure sensor 107 in the accumulator 106 downstream of the canisters, and regulate bolus size, generated by the oxygen concentrator 100, as a function of pressure. Such regulation of bolus size may be a function of accumulator pressure.
Control panel 600 serves as an interface between a user and controller 400 to allow the user to initiate predetermined operation modes of the oxygen concentrator 100 and to monitor the status of the system.
In some implementations, control panel 600 may include buttons to activate various operation modes for the oxygen concentrator 100. For example, control panel may include power button 610, flow rate setting buttons 620 to 626, active mode button 630, sleep mode button 635, altitude button 640, and a battery check button 650. In some implementations, one or more of the buttons may have a respective LED that may illuminate when the respective button is pressed, and may power off when the respective button is pressed again. Power button 610 may power the system on or off. If the power button 610 is activated to turn the system off, controller 400 may initiate a shutdown sequence to place the system in a shutdown state (e.g., a state in which both canisters are pressurized).
Flow rate setting buttons 620, 622, 624, and 626 allow a flow rate of oxygen enriched air to be selected (e.g., 0.2 LPM by button 620, 0.4 LPM by button 622, 0.6 LPM by button 624, and 0.8 LPM by button 626). In other implementations, the number of flow rate settings may be increased or decreased. After a flow rate setting is selected, oxygen concentrator 100 will then control operations to achieve production of the oxygen enriched air according to the selected flow rate setting.
Altitude button 640 may be activated when a user is going to be in a location at a higher elevation than the oxygen concentrator 100 is regularly used by the user.
Battery check button 650 initiates a battery check routine in the oxygen concentrator 100 which results in a relative battery power remaining LED 655 being illuminated on control panel 600.
A user may have a low breathing rate or depth if relatively inactive (e.g., asleep, sitting, etc.) as estimated by comparing the detected breathing rate or depth to a threshold. The user may have a high breathing rate or depth if relatively active (e.g., walking, exercising, etc.). An active/sleep mode may be estimated automatically from the detected breathing rate or depth, and/or the user may manually indicate an active mode or a sleep mode by pressing button 630 for active mode or button 635 for sleep mode respectively. In some implementations, the oxygen concentrator 100 defaults to active mode.
The methods of operating and monitoring oxygen concentrator 100 described below may be executed by the one or more processors, such as the one or more processors 410 of the controller 400, configured by program instructions, such as including, as previously described, the one or more functions and/or associated data corresponding thereto, stored in a memory such as the memory 420 of oxygen concentrator 100. Alternatively, some or all of the steps of the described methods may be similarly executed by one or more processors of an external computing device, such as the server 460, forming part of the connected respiratory therapy system 450, as described above. In this latter implementation, the processors 410 may be configured by program instructions stored in the memory 420 of oxygen concentrator 100 to transmit to the external computing device the measurements and parameters necessary for the performance of those steps that are to be carried out at the external computing device.
In order to minimize weight, size, and power consumption, oxygen concentrator 100 may deliver oxygen enriched air to the user as series of pulses. In such a pulsed oxygen delivery (POD) or demand mode of operation, controller 400 may regulate the size of the one or more released pulses or boluses to achieve delivery of the oxygen enriched air according to the selected flow rate setting. In order to maximize the effect of the delivered oxygen enriched air, controller 400 may be further programmed to synchronize the release of each bolus of the oxygen enriched air with the user's inhalations. Releasing a bolus of oxygen enriched air to the user as the user inhales may reduce wastage of oxygen by not releasing oxygen, for example, when the user is exhaling. The flow rate settings on the control panel 600 may correspond to minute volumes (bolus volume multiplied by breathing rate per minute) of delivered oxygen, e.g., 0.2 LPM, 0.4 LPM, 0.6 LPM, 0.8 LPM, 1 LPM, 1.1 LPM.
Oxygen enriched air produced by oxygen concentrator 100 is stored in accumulator 106 and, in a POD mode of operation, released to the user as the user inhales. The amount of oxygen enriched air provided by oxygen concentrator 100 is controlled, in part, by supply valve 160. In an implementation, supply valve 160 is opened for a sufficient amount of time to provide the appropriate amount of oxygen enriched air, as estimated by controller 400, to the user. In order to minimize the wastage of oxygen, the oxygen enriched air may be released as a bolus soon after the onset of a user's inhalation is detected. For example, the bolus of oxygen enriched air may be released in the first few milliseconds of a user's inhalation.
In some implementations, an inhalation sensor, such as a pressure sensor 194, may be used to detect the onset of inhalation by the user (a process referred to as “triggering”). For example, the onset of the user's inhalation may be detected by using pressure sensor 194. In use, delivery conduit 192 is coupled to the user's nose and/or mouth through the nasal airway delivery device 196 and/or mouthpiece 198. The pressure in delivery conduit 192 is therefore representative of the user's airway pressure and hence indicative of user respiration. At the onset of an inhalation, the user begins to draw air into their body through the nose and/or mouth. As the air is drawn in, a negative pressure is generated at the end of delivery conduit 192, due, in part, to the venturi action of the air being drawn across the end of delivery conduit 192. Controller 400 analyzes the pressure signal from the pressure sensor 194 to detect a drop in pressure indicating the onset of inhalation. Upon detection of the onset of inhalation, supply valve 160 is opened to release a bolus of oxygen enriched air from the accumulator 106.
In some implementations, pressure sensor 194 may be used to determine the onset of exhalation by the user. A positive change or rise in the pressure in delivery conduit 192 indicates an exhalation by the user. Controller 400 may analyze the pressure signal from pressure sensor 194 to detect a rise in pressure indicating the onset of exhalation. In some implementations, when a positive pressure change is sensed, supply valve 160 is closed until the next onset of inhalation is detected. In other implementations, when a positive pressure change is sensed, supply valve 160 may be closed after a predetermined interval known as the bolus duration.
By measuring the intervals between adjacent onsets of inhalation, the user's breathing rate may be estimated. By measuring the intervals between onsets of inhalation and the subsequent onsets of exhalation, the user's inspiratory time may be estimated. In some implementations, the user's breathing rate and/or inspiratory time may be used to adjust the bolus duration. In some implementations, if the user's activity level (e.g., the user's breathing rate) exceeds a predetermined threshold, controller 400 may implement an alarm (e.g., visual and/or audio) to warn the user that the current breathing rate is exceeding the delivery capacity of oxygen concentrator 100. For example, the threshold may be set at 40 breaths per minute (BPM).
In other implementations, the pressure sensor 194 may be positioned at different locations. For example, pressure sensor 194 may be located in a sensing conduit that is in pneumatic communication with the user's airway, but separate from the delivery conduit 192. In such implementations the pressure signal from the pressure sensor 194 is still representative of the user's airway pressure. As another example, pressure sensor 194 may be placed in nasal cannula airway delivery device 196. In such implementations, a signal from pressure sensor 194 may be provided to controller 400 via one or more electrical conduits or one or more wireless transmitters, receivers, and/or transceivers. In some implementations, the sensitivity of the pressure sensor 194 may be affected by the physical distance of the pressure sensor 194 from the user, especially if the pressure sensor 194 is located in oxygen concentrator 100 and the pressure difference is detected through delivery conduit 192 coupling the oxygen concentrator 100 to the user. Placement of pressure sensor 194 in nasal cannula airway delivery device 196 may improve its sensitivity.
In some implementations, the sensitivity of the triggering process is governed by a trigger threshold. In such implementations, the signal from the pressure sensor 194 is compared with a trigger threshold to determine whether a significant drop in pressure has taken place, thereby indicating onset of inhalation. Adjusting the trigger threshold alters the sensitivity of the triggering process. In some implementations, the trigger threshold is set to give the triggering process a higher sensitivity when the oxygen concentrator 100 is in sleep mode (e.g., as estimated automatically or as requested by the user via the sleep mode button 635) compared to when the oxygen concentrator 100 is in active mode (e.g., as estimated automatically or as requested by the user via the active mode button 630).
In some implementations, if the oxygen concentrator 100 is in active mode and an onset of inhalation has not been detected for a predetermined interval, e.g., 8 seconds, the oxygen concentrator 100 changes to sleep mode, which increases the trigger sensitivity as described above. If onset of inhalation is not detected for a further predetermined interval (e.g., 8 seconds), the oxygen concentrator 100 enters “auto-pulse” mode. In auto-pulse mode, the controller 400 controls actuation of the supply valve 160 so as to deliver boluses at regular, predetermined auto-pulse intervals, e.g., 4 seconds. The oxygen concentrator 100 exits auto-pulse mode once onset of inhalation is detected by the triggering process or the oxygen concentrator 100 is powered off.
Adjustment module 710 may be configured to receive, for example, a measured pressure signal (e.g., a signal generated by pressure sensor 194), a valve control signal (e.g., a signal generated by controller 400 to control supply valve 160), and/or a measured temperature signal (e.g., a signal generated by a temperature sensor in oxygen concentrator 100). Adjustment module 710 may be configured to adjust the measured pressure signal so that it more accurately represents the user's airway pressure. For example, adjustment module 710 may use the valve control signal to remove the pressure pulse(s) or pressure effect(s) that is/are contained in the measured pressure signal as a consequence of each release of a bolus of oxygen enriched air. As another example, adjustment module 710 may use the measured temperature signal to compensate for variations in temperature by removing any offset drift (e.g., thermal or other) in the measured pressure signal that may be caused by those variations (e.g., pressure sensor 194 may be temperature sensitive). As yet another example, adjustment module 710 may perform noise reduction filtering on the measured pressure signal. The output of adjustment module 710 is an adjusted pressure signal as a function of time.
Threshold module 720 may be configured to monitor the adjusted pressure signal from adjustment module 710 and repeatedly determine an appropriate trigger threshold as a function of time. Threshold module 720 may have an activity estimation sub-module configured to generate an activity signal from the adjusted pressure signal. In some implementations, the activity signal may correspond with a breathing parameter, such as a breathing rate of the user. In some implementations, the activity signal may be indicative of other types of activity. For example, a filter (e.g., a high-pass filter, such as a second-order Butterworth high-pass filter) with an appropriate cutoff frequency (e.g., 10 Hz) may be used to generate an activity signal that is indicative of non-respiratory activity.
Threshold module 720 may also have a threshold update sub-module configured to adjust the trigger threshold based on the activity signal from the activity estimation sub-module. For example, the threshold update sub-module may increase the magnitude of the trigger threshold when the activity signal indicates an increase in the user's activity. Similarly, the threshold update sub-module may decrease the magnitude of the trigger threshold when the activity signal indicates a decrease in the user's activity. These adjustments may help compensate for increased noise in the adjusted pressure signal during periods of increased activity of the user.
In some implementations, the threshold update sub-module may analyze fixed-length windows (e.g., time periods of 5 to 15 seconds) of the activity signal. In other implementations, the threshold update sub-module may analyze adjustable-length windows of the activity signal. In such implementations, threshold module 720 may also have a window adjustment sub-module that is configured to adjust the length of the window used by the threshold update sub-module as a function of the activity signal, the adjusted pressure signal, and/or the trigger threshold. For example, the window adjustment sub-module may temporarily shorten the length of the window to allow the trigger threshold to make a quick recovery from a brief isolated episode of increased noise (e.g., from a cough or a cannula bump, whereby the cannula bump may be an agitation caused by physical contact with a part of the cannula). In such implementations, the window adjustment sub-module may adjust the length of the window based on the amount of time that the trigger threshold exceeded a recent moving average of the trigger threshold.
Trigger module 730 may be configured to apply the trigger threshold from threshold module 720 to the adjusted pressure signal from adjustment module 710 to generate a trigger signal (e.g., a digital Boolean signal or a proportional control signal). The trigger signal may be used to synchronize the release of a bolus of oxygen enriched air with the user's inhalation. For example, the trigger signal may be provided to supply valve 160. In some implementations, trigger module 730 may compare the adjusted pressure signal to the trigger threshold to identify an onset of inhalation. In such implementations, trigger module 730 may detect an onset of inhalation when the magnitude of the adjusted pressure signal is greater than the magnitude of the trigger threshold. In some implementations, trigger module 730 may also compare the time since the previously detected onset of inhalation to a blackout period. In some implementations, the blackout period is a period after the detection of onset of inhalation in which the trigger module 730 will not compare the pressure signal to the trigger threshold. In such implementations, trigger module 730 may only detect an onset of inhalation when the time since the previously detected onset of inhalation is greater than the blackout period. In some implementations, trigger module 730 may also only detect an onset of inhalation when an onset of expiration has been detected after the previously detected onset of inhalation.
Monitoring module 740 may be configured to calculate one or more breathing parameters of the user (e.g., the user's breathing rate or inspiratory time) based on the adjusted pressure signal from adjustment module 710 and the trigger signal from trigger module 730. For example, monitoring module 740 may estimate the user's current breathing rate as the reciprocal of either a single recent breath duration or a moving average of two or more recent breath durations. A breath duration may be estimated as the length of time between successive detections of onsets of inhalation. As another example, monitoring module 740 may estimate the user's inspiratory time as the time for which the adjusted pressure has continuously remained below a predetermined threshold (e.g., zero). One or more of the breathing parameters calculated by monitoring module 740 may be provided to trigger module 730. In some implementations, trigger module 730 may adjust the length of the blackout period based on these breathing parameters. For example, trigger module 730 may decrease the length of the blackout period in response to an increase in the user's breathing rate. Similarly, trigger module 730 may increase the length of the blackout period in response to a decrease in the user's breathing rate. One or more of the breathing parameters calculated by monitoring module 740 may also be provided to one or more modules external to system 700 (e.g., a bolus adjustment module or a user data reporting module).
Further details regarding adaptive triggering systems may be found, for example, in International Patent Application No. PCT/AU2019/050302, entitled “Methods and Apparatus for Treating a Respiratory Disorder,” which published as International Publication No. WO 2019/191814 A1 on Oct. 10, 2019 and is incorporated herein by reference.
In some implementations, flow rate sensor 185 may be used to determine the onset of inhalation and/or exhalation by the user. For example, in much the same way that controller 400 may analyze a pressure signal from pressure sensor 194 to detect a drop in pressure indicating the onset of inhalation, controller 400 may analyze a flow signal from flow rate sensor 185 to detect a negative flow rate indicating the onset of inhalation. Similarly, controller 400 may also analyze the flow signal from flow rate sensor 185 to detect a positive flow rate indicating the onset of exhalation. Upon detection of the onset of inhalation, supply valve 160 may be opened to release a bolus of oxygen enriched air from accumulator 106. Similarly, upon detection of the onset of exhalation, supply valve 160 may be closed until the next onset of inhalation is detected.
In some implementations, flow rate sensor 185 may be used in combination with pressure sensor 194 to determine the onset of inhalation and/or exhalation by the user. In such implementations, adaptive triggering system 700 of
In some implementations, flow rate sensor 185 may be used without pressure sensor 194 to determine the onset of inhalation and/or exhalation by the user. In such implementations, adaptive triggering system 700 of
In some implementations, oxygen concentrator 100 may initiate an automatic delivery mode when the time since the previously detected onset of inhalation is greater than a predetermined threshold. During the automatic delivery mode, boluses of oxygen enriched air are automatically delivered to the user regardless, for example, of whether or not an onset of inhalation is detected. The automatic delivery mode helps to ensure that the user still receives the prescribed amount of oxygen enriched air. In some implementations, oxygen concentrator 100 may exit the automatic delivery mode and resume a POD mode of operation after a user breath is detected. In some implementations, oxygen concentrator 100 may exit the automatic delivery mode and resume a POD mode of operation after a predetermined time period (e.g., 45 seconds, 1 minute, 2 minutes, 3 minutes, etc.)
In some implementations, the predetermined threshold used to initiate the automatic delivery mode is a fixed value (e.g., a time period of 5 to 15 seconds). In other implementations, the predetermined threshold is repeatedly adjusted. For example, the predetermined threshold may be repeatedly adjusted based on a moving average of two or more recent breath durations. For example, the predetermined threshold may be repeatedly calculated as the product of a scaling constant (e.g., 1.25, 1.5, 2, 2.5, etc.) and the moving average of two or more recent breath durations. As another example, the predetermined threshold may be repeatedly calculated as the sum of a predetermined time period (e.g., 2 seconds, 3 seconds, 4 seconds, etc.) and the moving average of two or more recent breath durations.
In some implementations, the size and/or frequency of the boluses delivered during the automatic delivery mode is fixed. In other implementations, the size and/or frequency of the boluses is repeatedly adjusted. For example, the size and/or frequency of the boluses may be repeatedly adjusted based on a moving average of two or more recent breath durations. As another example, the size of the boluses automatically delivered to the user may correspond with the size of one or more boluses that were previously delivered to the user in response to one or more previously detected onsets of inhalation. Similarly, the rate at which the boluses are automatically delivered to the user may correspond with the rate at which one or more boluses were previously delivered to the user in response to one or more previously detected onsets of inhalation.
As the user of an oxygen concentrator moves, one or more components of the oxygen concentrator may also move. For example, as the user moves, a delivery conduit (e.g., delivery conduit 192) and/or an airway delivery device (e.g., nasal cannula airway delivery device 196 and/or mouthpiece 198) may also move. These movements may affect the measurements of one or more sensors in the oxygen concentrator (e.g., oxygen sensor 165, flow rate sensor 185, pressure sensor 194). For example, movement of delivery conduit 192 of oxygen concentrator 100 may create noise in the oxygen concentration, flow, and/or pressure signals of oxygen sensor 165, flow rate sensor 185, and/or pressure sensor 194, respectively. Therefore, in some implementations, one or more movement sensors may be included in the systems described above to compensate for noise created by movement of the user.
For example, as shown in
A variety of different movement sensors, such as accelerometers, gyroscopes, tilt switches, strain gauges, barometers, or altimeters, can be used with the present technology. For example, in some implementations, movement sensors 802A and/or 802B may be accelerometers configured to measure acceleration in one or more directions (e.g., a 1-axis accelerometer, a 2-axis accelerometer, or a 3-axis accelerometer). As another example, in some implementations, movement sensor 802B may be a strain gauge configured to measure bending of one or more portions of delivery conduit 192. As yet another example, in some implementations, movement sensors 802A and/or 802B may be barometers and/or altimeters configured to measure changes in altitude caused by the user.
Data generated by movement sensors 802A and 802B is received by controller 400. In some implementations, movement sensors 802A and 802B may be communicatively coupled to controller 400 through one or more electrical conduits. In such implementations, movement sensors 802A and 802B may transmit the generated data using standard communications protocols, such as Inter-Integrated Circuit (I2C), Serial Peripheral Interface (SPI), Controller Area Network (CAN), Universal Asynchronous Reception and Transmission (UART), Ethernet, or Universal Serial Bus (USB), or custom communications protocols. In some implementations, movement sensors 802A and 802B may wirelessly transmit the generated data to controller 400 through one or more wireless transmitters, receivers, and/or transceivers. In such implementations, movement sensors 802A and 802B may wirelessly transmit the generated data using standard communications protocols, such as Bluetooth, WiFi, ZigBee, Z-Wave, NEC Infrared (IR), Code Division Multiple Access (CDMA), Global System for Mobile Communications (GSM), or Long-Term Evolution (LTE), or custom communications protocols.
Controller 400 may use the data received from movement sensors 802A and 802B to compensate for noise created by movement of the user. For example, as shown in
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Activity estimation sub-module may be configured to generate an activity signal based on the adjusted pressure signal and/or a measured movement signal (e.g., a signal generated by movement sensor 802A or 802B). For example, in some implementations, activity estimation sub-module may derive a breathing parameter from the adjusted pressure signal (e.g., a breathing rate of the user) and a movement parameter from the measured movement signal (e.g., a number of steps taken per unit of time by the user). Activity estimation sub-module may then combine the breathing parameter and the movement parameter to generate the activity signal. For example, the activity signal may be calculated as a weighted sum of the breathing parameter and the movement parameter. As another example, in some implementations, activity estimation sub-module may generate a non-respiratory signal from the adjusted pressure signal (e.g., using a high-pass filter with an appropriate cutoff frequency). Activity estimation sub-module may then scale the non-respiratory signal based on the measured movement signal. For example, when the measured movement signal indicates a larger amount of movement by the user, a larger scaling factor may be applied to the non-respiratory signal to generate the activity signal. Similarly, when the measured movement signal indicates a smaller amount of movement by the user, a smaller scaling factor may be applied to the non-respiratory signal to generate the activity signal.
Threshold update sub-module may be configured to adjust the trigger threshold based on the activity signal from the activity estimation sub-module and/or a measured movement signal (e.g., a signal generated by movement sensor 802A or 802B). For example, the threshold update sub-module may increase the magnitude of the trigger threshold when the activity signal reliably indicates an increase in the user's activity. Similarly, the threshold update sub-module may decrease the magnitude of the trigger threshold when the activity signal reliably indicates a decrease in the user's activity. The threshold update sub-module may use the measured movement signal to assess the reliability of the activity signal. For example, in implementations where adaptive triggering system 900B is used with the outlet systems of
In some implementations, the threshold update sub-module may analyze fixed-length windows (e.g., time periods of 5 to 15 seconds) of the activity signal. In other implementations, the threshold update sub-module may analyze adjustable-length windows of the activity signal. In such implementations, threshold module 920 may have a window adjustment sub-module that is reconfigured to adjust the length of the window used by the threshold update sub-module as a function of the activity signal, the adjusted pressure signal, the trigger threshold, and/or a measured movement signal (e.g., a signal generated by movement sensor 802A or 802B). For example, the window adjustment sub-module may temporarily shorten the length of the window to allow the trigger threshold to make a quick recovery from a brief isolated episode of increased noise (e.g., from a cough or a cannula bump). In such implementations, the window adjustment sub-module may adjust the length of the window based on the amount of time that the trigger threshold exceeded a recent moving average of the trigger threshold. In some implementations, the window adjustment sub-module may be configured to analyze the measured movement signal to identify episodes of increased noise. For example, an episode of increased noise may be identified by the window adjustment sub-module when a magnitude and/or frequency of the measured movement signal is greater than a predetermined threshold.
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As noted above, in some implementations, oxygen concentrator 100 may initiate an automatic delivery mode when the time since the previously detected onset of inhalation is greater than a predetermined threshold. During the automatic delivery mode, boluses of oxygen enriched air are automatically delivered to the user regardless, for example, of whether or not an onset of inhalation is detected. In some implementations, the size and/or frequency of the boluses is repeatedly adjusted. For example, one or more breathing parameters calculated by monitoring module 940 may be used to adjust the size and/or frequency of the boluses. As another example, one or more separately calculated breathing parameters may be used to adjust the size and/or frequency of the boluses (e.g., a moving average of two or more recent breath durations). In such implementations, a measured movement signal (e.g., a signal generated by movement sensor 802A or 802B) can be used to increase the accuracy of these calculations. For example, one or more segments of a measured flow signal (e.g., a signal generated by flow rate sensor 185) and/or a measured pressure signal (e.g., a signal generated by pressure sensor 194) may be excluded from the calculation of the breathing parameters when a magnitude and/or frequency of one or more corresponding segments of the measured movement signal are greater than a predetermined threshold.
In some implementations, additional sensors may be incorporated into the systems and methods described above. For example, a measured heart rate signal generated by a heart rate monitor may be used in combination with a measured movement signal (e.g., a signal generated by movement sensor 802A or 802B) to compensate for noise created by movement of the user. In such implementations, the measured heart rate signal may be supplied to any of the modules described above. Increased heart rate may indicate increased movement by the user. Similarly, decreased heart rate may also indicate decreased movement by the user. As a result, adjustment module 910 may, for example, also use the measured heart rate signal to adjust the measured pressure. As another example, activity estimation sub-module of threshold module 920 may derive a heart rate parameter from the measured heart rate signal. Activity estimation sub-module may then combine the heart rate parameter with the breathing parameter and the movement parameter to generate the activity signal. As yet another example, the threshold update sub-module of threshold module 920 may use the measured heart rate signal to assess the reliability of the activity signal. As yet another example, the window adjustment sub-module of threshold module 920 may adjust the length of the window based on a magnitude and/or frequency of the measured heart rate signal. As yet another example, the trigger module 930 may verify an onset of inhalation based on a magnitude and/or frequency of the measured heart rate signal. As yet another example, the monitoring module 940 may exclude one or more segments of the adjusted pressure signal from the calculation of a breathing parameter based on a magnitude and/or frequency of the measured heart rate signal. As yet another example, the measured heart rate signal may be used to adjust the size and/or frequency of the boluses delivered during an automatic delivery mode.
Further details regarding movement compensation may be found, for example, in U.S. Provisional No. 63/000,813, entitled “Breath Detection with Movement Compensation,” filed on Mar. 27, 2020, the entire disclosure of which is incorporated herein by reference.
Hybrid mode therapy (or hybrid mode of delivery) is a breath-synchronized therapy in which there is a non-zero inter-bolus flow of gas to the patient as well as boluses delivered in synchrony with inhalation as in POD mode. Hybrid mode of delivery may comprise bilevel purity, bilevel flow rate, or a combination thereof.
The lower oxygen purity of the inter-bolus flow means less oxygen is wasted than during conventional continuous flow, in which the oxygen purity is constant. This in turn helps to extend battery life, since the compressor does not need to work as hard as during continuous flow to maintain system pressure at the desired value for the current flow rate setting. In addition, portable oxygen concentrators are limited in the volume of oxygen they can produce in a given time due to the design constraints (size, weight, power consumption, adsorbent mass). By conserving oxygen delivery, bilevel purity hybrid mode allows the other design constraints more room for optimization.
The flow source 1101 is connected to the downstream side of the flow restrictor 175 via a secondary flow path comprising the secondary valve 1110 and the flow restrictor 1120. The flow in the secondary flow path is at a lower purity than the oxygen enriched air released by the supply valve 160 to the patient via the primary path. The controller 400 controls the secondary valve 1110 to allow flow along the lower-purity path when a bolus is not being released by the supply valve 160, to prevent flow along the lower-purity path during bolus release. In other words, the secondary valve 1110 is actuated in anti-sync with the supply valve 160, being open when the supply valve 160 is closed and closed when the supply valve 160 is open. In an alternative to the modified outlet system 1100 for implementing bilevel purity hybrid mode, the two two-way valves 160 and 1110 may be replaced by a single three-way valve that is configured to connect the accumulator 106 to either the primary path (when triggered by the onset of inhalation) or the secondary, lower-purity path at all other times. The three-way valve may be either downstream of the flow restrictors 175 and 1120 or upstream of a single flow restrictor which replaces and combines the effects of the flow restrictors 175 and 1120.
In one implementation, the flow source 1101 may be the compressor 210. In such an implementation, the flow restrictor 1120 is chosen such that the flow rate in the lower-purity path is approximately equal to the bolus flow rate in the higher-purity primary path. In some implementations, the flow restrictor 1120 may be omitted altogether, depending on the pressure of the flow source 1101 and the pneumatic impedance of the secondary flow path.
In an alternative implementation, the flow source 1101 may be a secondary compressor that is configured to generate a flow of air at flow rates approximately equal to the bolus flow rates in the higher-purity path. In such an implementation the flow restrictor 1120 may be omitted.
In either such implementation, the oxygen purity in the lower-purity path is approximately that of ambient air (21%).
In yet a further implementation of bilevel purity hybrid mode, the flow source 1101 is a portion of the vented exhaust gas (of oxygen purity typically around the ambient purity of 21%, but may be as high as 35% and as low as 4% depending on the amount of the purge flow) that has been re-routed from the outlet 130 to the lower-purity path. In one such implementation, the flow restrictor 1120 is chosen such that the flow rate in the lower-purity path is approximately equal to the bolus flow rates in the higher-purity primary path.
Another modification to the outlet system of
However, with the differential connection of
Oxygen enriched air may not be delivered in bilevel purity hybrid mode at all times using the modified outlet system 1100. In some implementations, the controller 400 may keep the secondary valve 1110 closed so that the oxygen enriched air is delivered in POD mode via the primary path until a control on the control panel 600 is activated. For example, the control may be activated if the user is experiencing dyspnea or shortness of breath and is in need of reassurance. Once the control is activated, the controller 400 begins to open and close the secondary valve 1110 in anti-sync with the supply valve 160 as described above to implement bilevel purity hybrid mode. This mode may last for a predetermined period or for an indefinite period until the control on the control panel is de-activated. The controller 400 then reverts to delivering oxygen enriched air in POD mode.
The lower flow rate of the inter-bolus flow means less oxygen is wasted than during conventional continuous flow, in which the flow rate is constant over the breathing cycle. This in turn helps to extend battery life, since the compressor does not need to work as hard as during continuous flow to maintain system pressure at the desired value for the current flow rate setting. In addition, portable oxygen concentrators are limited in the volume of oxygen they can produce in a given time due to the design constraints (size, weight, power consumption, adsorbent mass). By conserving oxygen delivery, bilevel flow rate hybrid mode allows the other design constraints more room for optimization.
The controller 400 controls the secondary valve 1310 to allow flow along the lower-flow path when a bolus is not being released by the supply valve 160, to prevent flow along the lower-flow path during bolus release. In other words, the secondary valve 1310 is actuated in anti-sync with the supply valve 160, being open when the supply valve 160 is closed and closed when the supply valve 160 is open.
The modified outlet system 1300 also makes use of the differentially connected pressure sensor 194 with the flow restrictor 1130, as in the modified outlet system 1100, to enable more accurate triggering.
Oxygen enriched air may not be delivered in bilevel flow rate hybrid mode at all times using the modified outlet system 1300. In some implementations, the controller 400 keeps the secondary valve 1310 closed so that the oxygen enriched air is delivered in POD mode via the primary path until a control on the control panel 600 is activated. For example, the control may be activated if the user is experiencing dyspnea or shortness of breath and is in need of reassurance. Once the control is activated, the controller 400 begins to open and close the secondary valve 1310 in anti-sync with the supply valve 160 as described above to implement bilevel flow rate hybrid mode. This mode may last for a predetermined period or for an indefinite period until the control on the control panel is de-activated. The controller 400 then reverts to delivering oxygen enriched air in POD mode.
An alternative modified outlet system for implementing bilevel flow rate hybrid mode does not include the secondary valve 1310. Instead the secondary, lower-flow path through the flow restrictor 1320 is activated as long as the oxygen concentrator 100 itself is activated.
In a further alternative modified outlet system for implementing bilevel flow rate hybrid mode, the two two-way valves 160 and 1310 may be replaced by a single three-way valve that is configured to connect the accumulator 106 to either the primary path (when triggered by the onset of inhalation) or the secondary, lower-flow path at all other times.
One benefit of the bilevel flow rate hybrid delivery mode is that the oxygen enriched air delivered at a low flow rate via the secondary, lower-flow path “pools” within the delivery conduit 192 and is therefore available for inhalation as soon as inhalation begins, even before the opening of the primary path for the release of the bolus.
Intermediate species may be implemented by a combination of the modified outlet systems 1100 and 1300 containing both the secondary lower-purity path and the secondary lower-flow path, each of which are opened in anti-sync with the primary path. The combination of the flows in the two secondary paths makes up the total inter-bolus flow. The respective sizes of the flow restrictors 1120 and 1320 determine the flow rates in the two secondary paths and therefore the inter-bolus purity and flow rate.
The differentially connected pressure sensor 194 may be used with all species of hybrid mode delivery in order to improve the accuracy of triggering.
Further details regarding hybrid mode oxygen delivery may be found, for example, in A.U. Application No. 2020901121, entitled “Methods and Apparatus for Treating a Respiratory Disorder,” filed on Apr. 8, 2020, the entire disclosure of which is incorporated herein by reference.
In some implementations, an oxygen concentrator (e.g., oxygen concentrator 100) may be configured to automatically switch between a plurality of modes of operation based on whether and/or how the oxygen concentrator is being used. For example, a portable oxygen concentrator (POC) may automatically transition from a prescribed mode of operation to a standby mode of operation after a user stops using the POC. Similarly, a POC may automatically transition from a standby mode of operation to a prescribed mode of operation in response to a user interacting with the POC. During a standby mode of operation, a POC may power off or reduce the power provided to one or more components (e.g., pressure sensor 107, valves 122, 124, 132, 134, 152, and/or 154, oxygen sensor 165, fan 172, compression system 200, and/or motor speed transducer 201). For example, during a standby mode of operation, a POC may power off its compression system. As another example, during a standby mode of operation, a POC may provide a lower oxygen purity or a lower flow rate (e.g., corresponding to an inter-bolus period). By minimizing power consumption during a standby mode of operation, the run-time of an internal power source (e.g., Lithium ion batteries) may be increased and the size and weight of the POC may be minimized. Furthermore, the experience of the user may be improved by reducing the number of times the user interacts with the POC. For example, instead of both removing an airway delivery device (e.g., nasal masks, nasal pillows, nasal prongs, nasal cannulas, or mouthpieces) and manually powering off a POC, a user can simply remove the airway delivery device and the POC will automatically enter a standby mode. A reduction in the number of user interactions may be particularly advantageous for less dexterous users.
During a prescribed mode of operation, a POC may be configured to deliver a prescribed therapeutic pressure, volume, and/or concentration of oxygen to a user. As described above, the prescribed therapeutic pressure, volume, and/or concentration of oxygen may be delivered as a continuous flow of oxygen, a series of pulses (see subsection H, entitled “Pulsed Oxygen Delivery,” for more details), or a hybrid of the two (see subsection J, entitled “Hybrid Mode Oxygen Delivery,” for more details). A prescribed mode of operation may include, for example, the active and/or sleep modes described above.
In some implementations, an oxygen concentrator may transition between a prescribed mode of operation and a standby mode of operation based on a number of detected breaths during a predetermined period of time. For example, a POC may automatically transition from a prescribed mode of operation to a standby mode of operation when a number of detected breaths during a predetermined period of time (e.g., thirty seconds, one minute, three minutes, etc.) is less than a predetermined threshold (e.g., one breath, two breaths, five breaths, etc.). Similarly, a POC may automatically transition from a standby mode of operation to a prescribed mode of operation when a number of detected breaths during a predetermined period of time (e.g., five seconds, ten seconds, thirty seconds, one minute, three minutes, etc.) is greater than a predetermined threshold (e.g., one breath, two breaths, five breaths, etc.). In some such implementations, different predetermined periods of time may be used to initiate different modes of operation. For example, the predetermined period of time used to initiate a standby mode of operation (e.g., one minute) may be greater than the predetermined period of time used to initiate a prescribed mode of operation (e.g., five seconds). Furthermore, in some such implementations, different predetermined thresholds may be used to initiate different modes of operation. For example, the predetermined threshold used to initiate a standby mode of operation (e.g., one breath) may be less than the predetermined threshold used to initiate a prescribed mode of operation (e.g., three breaths).
A variety of different systems and methods may be used to detect breaths. For example, as described above, a pressure, flow, and/or movement sensor may be used to detect an onset of inhalation and/or exhalation (e.g., flow rate sensor 185, pressure sensor 194, movement sensor 802A, and/or movement sensor 802B). For example, adaptive triggering systems 700, 900A, 900B, 900C, and/or 900D (see
In some implementations, during a standby mode of operation, a POC may power off or reduce the power provided to one or more components (e.g., pressure sensor 107, valves 122, 124, 132, 134, 152, and/or 154, oxygen sensor 165, fan 172, compression system 200, and/or motor speed transducer 201), but maintain the power provided to the one or more sensors used to detect breaths (e.g., flow rate sensor 185, pressure sensor 194, movement sensor 802A, and/or movement sensor 802B).
In some implementations, an oxygen concentrator may transition between a prescribed mode of operation and a standby mode of operation based on a magnitude and/or duration of one or more detected movements. For example, a POC may automatically transition from a prescribed mode of operation to a standby mode of operation when an estimated average magnitude of one or more detected movements during a predetermined period of time (e.g., thirty seconds, one minute, three minutes, etc.) is less than a predetermined threshold. Similarly, a POC may automatically transition from a standby mode of operation to a prescribed mode of operation when an estimated average magnitude of one or more detected movements during a predetermined period of time (e.g., five seconds, ten seconds, thirty seconds, one minute, three minutes, etc.) is greater than a predetermined threshold. In some such implementations, different predetermined periods of time may be used to initiate different modes of operation. For example, the predetermined period of time used to initiate a standby mode of operation (e.g., one minute) may be greater than the predetermined period of time used to initiate a prescribed mode of operation (e.g., five seconds). Furthermore, in some such implementations, different predetermined thresholds may be used to initiate different modes of operation. For example, the predetermined threshold used to initiate a standby mode of operation may be less than the predetermined threshold used to initiate a prescribed mode of operation.
A variety of different systems and methods may be used to detect movement. For example, a variety of different movement sensors, such as accelerometers, gyroscopes, tilt switches, strain gauges, barometers, or altimeters, can be used with the present technology at a variety of different locations within a POC. For example, in some such implementations, a POC may include either of the outlet systems illustrated in
In some implementations, an oxygen concentrator may transition between a prescribed mode of operation and a standby mode of operation based on (a) on a number of detected breaths during a predetermined period of time and/or (b) a magnitude and/or duration of one or more detected movements. For example, a POC may automatically transition from a prescribed mode of operation to a standby mode of operation when (a) a number of detected breaths during a first predetermined period of time is less than a first predetermined threshold and (b) an estimated average magnitude of one or more detected movements during a second predetermined period of time is less than a second predetermined threshold. Similarly, a POC may automatically transition from a standby mode of operation to a prescribed mode of operation when (a) a number of detected breaths during a first predetermined period of time is greater than a first predetermined threshold and (b) an estimated average magnitude of one or more detected movements during a second predetermined period of time is greater than a second predetermined threshold. Some such implementations may operate more accurately and/or effectively. For example, by relying on two different types of measurements, the risk of a false positive (e.g., incorrectly determining that a user is currently using the POC) and/or a false negative (e.g., incorrectly determining that a user is not currently using the POC) may be reduced. As such, boluses of oxygen enriched air may be delivered when there is a genuine demand from the user and not otherwise.
As another example, a POC may automatically transition from a prescribed mode of operation to a standby mode of operation when (a) a number of detected breaths during a first predetermined period of time is less than a first predetermined threshold, (b) an estimated average magnitude of one or more detected movements during a second predetermined period of time is less than a second predetermined threshold, or (c) both (i) a number of detected breaths during a third predetermined period of time is less than a third predetermined threshold and (ii) an estimated average magnitude of one or more detected movements during a fourth predetermined period of time is less than a fourth predetermined threshold. Similarly, a POC may automatically transition from a standby mode of operation to a prescribed mode of operation when (a) a number of detected breaths during a first predetermined period of time is greater than a first predetermined threshold, (b) an estimated average magnitude of one or more detected movements during a second predetermined period of time is greater than a second predetermined threshold, or (c) both (i) a number of detected breaths during a third predetermined period of time is greater than a third predetermined threshold and (ii) an estimated average magnitude of one or more detected movements during a fourth predetermined period of time is greater than a fourth predetermined threshold. In some implementations, the first and second predetermined periods of time and thresholds may be selected such that a mode of operation is only changed when the associated measurements (e.g., from flow rate sensor 185, pressure sensor 194, movement sensor 802A, and/or movement sensor 802B) indicate with a higher degree of certainty whether a user is currently using the POC. Similarly, in some implementations, the third and fourth predetermined periods of time and thresholds may be selected such that a mode of operation is changed when the associated measurements indicate with a lesser degree of certainty whether a user is currently using the POC. Some such implementations may operate more accurately and/or effectively. For example, by relying on two different types of measurements, the risk of a false positive (e.g., incorrectly determining that a user is currently using the POC) and/or a false negative (e.g., incorrectly determining that a user is not currently using the POC) may be reduced. As such, boluses of oxygen enriched air may be delivered when there is a genuine demand from the user and not otherwise.
Additional types of sensors may be used instead of or in addition to the pressure, flow, and/or movement sensors described above to determine when a POC transitions between a prescribed mode of operation and a standby mode of operation. For example, a temperature sensor positioned within a delivery conduit (e.g., delivery conduit 192) or an airway delivery device (e.g., nasal cannula airway delivery device 196 and/or mouthpiece 198) may be used to determine or verify whether a user is using the POC. In some such implementations, increased temperature measurements may indicate that a user is currently using the POC, and decreased temperature measurements may indicate that the user is not currently using the POC. As another example, a microphone positioned within a delivery conduit (e.g., delivery conduit 192) or an airway delivery device (e.g., nasal cannula airway delivery device 196 and/or mouthpiece 198) may be used to determine or verify whether a user is using the POC. In some such implementations, increased magnitudes and/or durations of measured sound signals may indicate that a user is currently using the POC, and decreased magnitudes and/or durations of measured sound signals may indicate that the user is not currently using the POC.
In some implementations, one or more devices associated with a user may be used to further verify whether a user is currently using the POC. For example, a mobile device (e.g., a smartphone) or a wearable device (e.g., a smartwatch) may be used to verify whether the user is near the POC. For example, the mobile device and/or wearable device may be configured to communicate with the POC through a short-range wireless communications protocol (e.g., Bluetooth, WiFi, ZigBee, Z-Wave, or NEC Infrared (IR)). The strength of the wireless signals transmitted by the mobile device and/or wearable device may indicate how close the mobile device and/or wearable device are to the POC.
In many of the implementations described above, only two modes of operation were described (i.e., a prescribed mode of operation and a standby mode of operation). However, in other implementations, a POC may be configured to transition between additional modes of operation. In such implementations, a POC may transition between different modes of operation based on any of the types of measurements described above (e.g., pressure, flow, movement, temperature, sound, etc.). Furthermore, in some implementations, a mode of operation may include multiple phases. For example, a standby mode of operation may include a first phase in which a lower oxygen purity or a lower flow rate (e.g., corresponding to an inter-bolus period) is supplied to an airway delivery device and a second phase in which no supplemental oxygen is supplied to the airway delivery device. A POC may automatically transition between these phases after a predetermined amount of time. For example, during a standby mode of operation, a POC may automatically transition from the first phase described above to the second phase described above after a predetermined amount of time.
In some implementations, a POC may include a control panel (e.g., control panel 600) that serves as an interface between a user and a controller (e.g., controller 400) to allow the user to manually switch between different modes of operation. For example, as explained above in reference to
For the purposes of the present technology disclosure, in certain forms of the present technology, one or more of the following definitions may apply. In other forms of the present technology, alternative definitions may apply.
Air: In certain forms of the present technology, air may be taken to mean atmospheric air, consisting of 78% nitrogen (N2), 21% oxygen (O2), and 1% water vapor, carbon dioxide (CO2), argon (Ar), and other trace gases.
Oxygen enriched air: Air with a concentration of oxygen greater than that of atmospheric air (21%), for example at least about 50% oxygen, at least about 60% oxygen, at least about 70% oxygen, at least about 80% oxygen, at least about 87% oxygen, at least about 90% oxygen, at least about 95% oxygen, at least about 98% oxygen, or at least about 99% oxygen. “Oxygen enriched air” is sometimes shortened to “oxygen”.
Medical Oxygen: Medical oxygen is defined as oxygen enriched air with an oxygen concentration of 80% or greater.
Ambient: In certain forms of the present technology, the term ambient will be taken to mean (i) external of the treatment system or patient, and (ii) immediately surrounding the treatment system or patient.
Flow rate: The volume (or mass) of air delivered per unit time. Flow rate may refer to an instantaneous quantity. In some cases, a reference to flow rate will be a reference to a scalar quantity, namely a quantity having magnitude only. In other cases, a reference to flow rate will be a reference to a vector quantity, namely a quantity having both magnitude and direction. Flow rate may be given the symbol Q. ‘Flow rate’ is sometimes shortened to simply ‘flow’ or ‘airflow’.
Flow therapy: Respiratory therapy comprising the delivery of a flow of air to an entrance to the airways at a controlled flow rate referred to as the treatment flow rate that is typically positive throughout the patient's breathing cycle.
Patient: A person, whether or not they are suffering from a respiratory disorder.
Pressure: Force per unit area. Pressure may be expressed in a range of units, including cmH2O, g-f/cm2, pounds per square inch (psi), and hectopascals. 1 cmH2O is equal to 1 g-f/cm2 and is approximately 0.98 hectopascal (1 hectopascal=100 Pa=100 N/m2=1 millibar ˜0.001 atm ˜0.015 psi). In this specification, unless otherwise stated, pressure values are given as gauge pressures (pressures relative to ambient pressure).
The term “coupled” as used herein means either a direct connection or an indirect connection (e.g., one or more intervening connections) between one or more objects or components. The phrase “connected” means a direct connection between objects or components such that the objects or components are connected directly to each other. As used herein the phrase “obtaining” a device means that the device is either purchased or constructed.
In the present disclosure, certain U.S. patents, U.S. patent applications, and other materials (e.g., articles) have been incorporated by reference. The text of such U.S. patents, U.S. patent applications, and other materials is, however, only incorporated by reference to the extent that no conflict exists between such text and the other statements and drawings set forth herein. In the event of such conflict, then any such conflicting text in such incorporated by reference U.S. patents, U.S. patent applications, and other materials is specifically not incorporated by reference in this patent.
Further modifications and alternative implementations of various aspects of the present technology may be apparent to those skilled in the art in view of this description. Accordingly, this description is to be construed as illustrative only and is for the purpose of teaching those skilled in the art the general manner of carrying out the technology. It is to be understood that the forms of the technology shown and described herein are to be taken as implementations. Elements and materials may be substituted for those illustrated and described herein, parts and processes may be reversed, and certain features of the technology may be utilized independently, all as would be apparent to one skilled in the art after having the benefit of this description of the technology. Changes may be made in the elements described herein without departing from the spirit and scope of the technology as described in the appended claims.
| Number | Date | Country | Kind |
|---|---|---|---|
| 2020901121 | Apr 2020 | AU | national |
This application claims priority to U.S. Provisional Application No. 63/000,813, entitled “Breath Detection with Movement Compensation,” filed on Mar. 27, 2020, A.U. Provisional Application No. 2020901121, entitled “Methods and Apparatus for Treating a Respiratory Disorder,” filed on Apr. 8, 2020, and U.S. Provisional Application No. 62/705,492, entitled “Power Management in Portable Oxygen Concentrators,” filed on Jun. 30, 2020, all of which are incorporated herein by reference.
| Filing Document | Filing Date | Country | Kind |
|---|---|---|---|
| PCT/SG2021/050152 | 3/22/2021 | WO |
| Number | Date | Country | |
|---|---|---|---|
| 63000813 | Mar 2020 | US | |
| 62705492 | Jun 2020 | US |
