Device with power source connection for treating respiratory disorders

Abstract

The present invention relates to devices with power source connections for treating respiratory disorders. Respiratory devices, such as ventilators, for use in treating respiratory disorders and for preventing respiratory disorders are configured to be powered from a number of different power sources including an internal battery, an external battery, an alternating current power source, or a direct current power source. The device can be electrically connected to a plurality of external batteries in a string, and power from each external battery is used in turn along the string. A controller of the respiratory device is configured to detect the connection of the different power sources, and control the use of the different power sources using a power priority scheme. The controller can determine an estimate of the total available battery capacity from all electrically connected batteries, and display the total battery capacity on a user interface display of the device.

Description

[0001] This patent application is a divisional application of the patent application filed on October 30, 2014, with national application number 201480059531.6 and title "Device with Power Source Connection for Treating Respiratory Disorders". Technical Field

[0002] This technology relates to one or more of the diagnosis, treatment, and improvement of respiratory disorders, as well as processes for preventing respiratory disorders. Specifically, this technology relates to medical devices and the use of medical devices for treating and preventing respiratory disorders. Background Technology

[0003] The body's respiratory system facilitates gas exchange. The nose and mouth form the entrances into the patient's airways.

[0004] The airways consist of a series of branching tubes, which become narrower, shorter, and more numerous as they extend deeper into the lungs. The primary function of the lungs is gas exchange, allowing oxygen to move from the air into the venous blood and carbon dioxide to escape. The trachea divides into the right main bronchus and the left main bronchus, which further subdivide into terminal bronchioles. The bronchi form the airway and do not participate in gas exchange. Further subdivisions of the airways lead to respiratory bronchioles, which eventually result in alveoli. The honeycomb-like regions of the lungs are where gas exchange occurs and are called respiratory zones. See West's *Respiratory Physiology—The Essentials*.

[0005] There is a series of respiratory problems.

[0006] Obstructive sleep apnea (OSA), a form of sleep-disordered breathing (SDB), is characterized by closure or obstruction of the upper airway during sleep. This is due to a combination of abnormal small upper airways and normal damage to muscle tone in the tongue region, soft palate, and posterior oropharyngeal wall during sleep. This condition causes affected patients to stop breathing for a duration typically between 30 and 120 seconds—sometimes 200 to 300 times per night. This often leads to excessive daytime sleepiness and can also cause cardiovascular disease and brain damage. Although affected individuals may not be aware of the problem, the syndrome is a common condition, especially among middle-aged obese men. See U.S. Patent US 4,944,310 (Sullivan).

[0007] Cheyne-Stokes respiration (CSR) is a disorder of a patient's respiratory controller, characterized by rhythmic alternations of rising and falling ventilation, resulting in repeated deoxygenation and reoxygenation of arterial blood. The repeated hypoxia makes CSR potentially harmful. In some patients, CSR is associated with repetitive awakenings from sleep, which can lead to severe sleep disturbances, increased sympathetic activity, and increased afterload. See US Patent 6,532,959 (Berthon-Jones).

[0008] Obesity hyperventilation syndrome (OHS) is defined as a combination of severe obesity and waking chronic hypercapnia in the absence of other known causes of hypoventilation. Symptoms include dyspnea, morning headache, and daytime sleepiness.

[0009] Chronic obstructive pulmonary disease (COPD) encompasses any group of lower airway diseases that share certain common characteristics. These include increased airflow resistance, prolonged expiratory phase of breathing, and impaired lung elasticity. Examples of COPD include emphysema and chronic bronchitis. COPD is caused by chronic smoking (a major risk factor), occupational exposure, air pollution, and genetic factors. Symptoms include exertional dyspnea, chronic cough, and sputum production.

[0010] Neuromuscular disease (NMD) is a broad concept encompassing many diseases and disorders that can impair muscle function directly through intrinsic myopathy or indirectly through neuropathology. Some NMD patients are characterized by progressive muscle damage leading to loss of mobility, wheelchair use, dysphagia, respiratory muscle weakness, and ultimately death from respiratory failure. Neuromuscular diseases can be classified as rapidly progressive or slowly progressive: (i) rapidly progressive diseases: characterized by muscle damage that worsens within months and leads to death within years (e.g., amyotrophic lateral sclerosis (ALS) and Duchenne muscular dystrophy (DMD) in adolescents); (ii) variable or slowly progressive diseases: characterized by muscle damage that worsens over many years and only slightly shortens life expectancy (e.g., limb girdle, facioscapulohumeral, and myotonic dystrophy). Symptoms of respiratory failure in NMD include: increased general weakness, dysphagia, shortness of breath at exertion and rest, fatigue, somnolence, morning headache, and difficulty concentrating and experiencing mood swings.

[0011] Chest wall disorders are a group of chest deformities that result in inefficient coupling between the respiratory muscles and the chest. These disorders are typically characterized by restrictive defects and the potential for chronic respiratory failure. Scoliosis and / or kyphosis can lead to severe respiratory failure. Symptoms of respiratory failure include: exertional dyspnea, angioedema, orthopnea, recurrent lung infections, morning headache, fatigue, poor sleep quality, and loss of appetite.

[0012] In addition, healthy individuals can use systems and devices to prevent respiratory problems.

[0013] 1.1 System

[0014] One known product for treating sleep-disordered breathing is the ResMed S9 Sleep Therapy System. This includes a ventilator such as the ResMed Stellar for adults. TM Series and pediatric ventilators can provide invasive and non-invasive non-dependent ventilatory support to some patients to treat conditions such as, but not limited to, NMD, OHS and COPD.

[0015] ResMed Elisée TM 150 ventilator and ResMed VS III TM Ventilators can provide invasive and non-invasive dependent ventilation support suitable for adult or pediatric patients to treat a range of conditions. These ventilators use single-limb or dual-limb circuits to provide volume ventilation and pressure ventilation modes.

[0016] 1.2 Treatment methods

[0017] Nasal continuous positive airway pressure (CPAP) has been used to treat obstructive sleep apnea (OSA). It is assumed that CPAP acts as a pneumatic splint and can prevent upper airway obstruction by pushing the soft palate and tongue forward and away from the posterior oropharyngeal wall.

[0018] Invasive ventilation (NIV) provides mechanical ventilation through the upper airway to assist patients in achieving a full breath and / or maintaining adequate oxygen levels. This ventilation is provided via a face mask or nasal interface. NIV has been used to treat OHS, COPD, MD, and chest wall diseases. Non-invasive ventilation (IV) provides ventilation support to patients who are unable to breathe effectively using a tracheostomy tube or endotracheal tube.

[0019] The ventilator also controls the timing and pressure of the breaths pumped to the patient and monitors the patient's breathing. Methods of patient control and monitoring typically include volume switching and pressure switching. Volume switching methods can include, among others, pressure-regulated volume control (PRVC), tidal volume (VV), and volume-controlled continuous forced ventilation (VC-CMV) techniques. Pressure switching methods can involve, among others, auxiliary control systems (AC), synchronized intermittent mandatory ventilation (SIMV), controlled mechanical ventilation (CMV), pressure support ventilation (PSV), continuous positive airway pressure (CPAP), or positive end-expiratory pressure (PEEP) techniques.

[0020] 1.3 Patient Interface

[0021] The use of patient interfaces such as nasal masks, full-face masks, or nasal pillows facilitates the application of supplying positive pressure air to the patient's airway inlet. Several patient interface devices are known; however, some have one or more of the following characteristics: excessive protrusion, aesthetic impairment, poor fit, difficulty in use for extended periods, or particular discomfort when the patient is unfamiliar with the system. For the original applications of patient interface devices, masks designed solely for pilots as part of personal protective equipment or for administering anesthetics may be tolerable; however, it is still undesirable to wear them uncomfortably for extended periods, such as during sleep or throughout the day.

[0022] Tracheostomy tubes or endotracheal tubes are other forms of patient interfaces that can be used for invasive ventilation.

[0023] 1.4 Apparatus

[0024] A positive airway pressure (PAP) device, such as an electric motor-driven fan, can supply air at positive pressure to the patient's airway. The fan outlet is connected to the patient interface as described above via a flexible delivery duct.

[0025] A ventilator typically includes an airflow generator, an inlet filter, a patient interface, an air delivery duct connecting the airflow generator to the patient interface, various sensors, and a microprocessor-based controller. The patient interface may include a face mask, nasal prong, or tracheostomy tube or endotracheal tube as described above. The airflow generator may include a servo-controlled motor, a volute forming the fan, and an impeller. In some cases, a brake on the motor can rapidly reduce the fan speed to overcome the inertia of the motor and impeller. Despite inertia, braking allows the fan to quickly reach lower pressure conditions, time-synchronized with exhalation. In some cases, as an option for controlling motor speed, the airflow generator may also include a valve capable of venting the generated air to the atmosphere as a means of changing the pressure delivered to the patient. Among other things, sensors, such as pressure sensors, measure motor speed, mass flow rate, and outlet pressure. The device may optionally include a humidifier and / or a heating element in the path of the air delivery line. The controller may include data storage capacity with or without integrated data retrieval and display capabilities.

[0026] 1.5 Humidifier

[0027] Breathing equipment typically has the ability to modify the humidity of the breathable gas to reduce dryness of the patient's airway and consequently, patient discomfort and related complications. A humidifier can be located between the airflow generator, PAP device, or ventilator and the patient interface, or in front of the airflow generator, PAP device, or ventilator. Using a humidifier produces humidified gas that minimizes dryness of the nasal mucosa and improves patient airway comfort. Except in cool climates, warm air applied to or around the patient interface on the face is generally more comfortable than cold air.

[0028] Humidity refers to the amount of water vapor present in the air. It is typically measured in two ways:

[0029] (1) Absolute humidity (AH) is the actual water content recorded per unit volume by weight – usually in grams per cubic meter (g / cm³). 3 (mg / L) or milligrams per liter.

[0030] (2) Relative humidity (RH) is the percentage of the actual water vapor content of a gas relative to its capacity to carry water at any given temperature.

[0031] The capacity of air to retain water vapor increases with increasing air temperature. This means that for air with a stable AH (Area of ​​Humidity), the RH (Relative Humidity) will decrease as the air temperature rises. Conversely, for water-saturated air (100% RH), excess water will condense if the temperature decreases. The air humans breathe is typically naturally heated and humidified through the airways to achieve a temperature of 37°C and 100% humidity. At this temperature, the AH humidity is 44 mg / L.

[0032] Respiratory humidifiers can be used in various forms, and can be standalone devices coupled to a respiratory apparatus via an air delivery tube, integrated into the respiratory apparatus, or configured to be directly coupled to the relevant respiratory equipment. While passive humidifiers can provide some relief, heated humidifiers are generally required to provide sufficient humidity and temperature to make the patient comfortable. Humidifiers typically include a water reservoir or tank with a capacity of several hundred milliliters (ml), a heating element for heating the water in the reservoir, controls for varying the humidification level, a gas inlet for receiving gas from a gas generator or device, and an outlet suitable for connecting to an air delivery tube that delivers humidified gas to the patient interface.

[0033] Heated aisle humidification is a common form of humidification used with PAP (Particle-Assisted Aeration) units. In this system, the heating element may be contained within a heating plate located below and in thermal contact with the water tank. Therefore, heat is primarily transferred from the heating plate to the water reservoir via conduction. Airflow from the PAP unit, airflow generator, or ventilator passes through the heated water in the tank, generating water vapor that is absorbed by the airflow. (ResMed H4i) TM and H5i TM The humidifier is an example of this heated channel humidification system used in conjunction with the ResMed S8 and S9CPAP systems, respectively.

[0034] Other humidification systems can also be used, such as bubble or diffuser humidifiers, jet humidifiers, or wicking humidifiers.

[0035] By using CounterStream TM ResMed HumiCare technology TM The D900 humidifier offers another form of humidification, from CounterStream. TM The technology directs airflow in a first direction onto a large surface area while simultaneously supplying heated water to that large surface area in a second, opposite direction. (ResMed HumiCare) TM The D900 humidifier can be used with some invasive and non-invasive ventilation systems.

[0036] 1.6 Air Circuit

[0037] Air circuits may include, for example Figure 1 The diagram shows a single-limb circuit or air delivery conduit. A single-limb circuit can be used with an intentionally leaky vent. The vent can be configured as a separate component, such as an anti-asphyxiation valve, fitted into the air delivery conduit, or it can be integrated as part of the patient interface. The air delivery conduit connects to the outlet of a device such as a ventilator or humidifier. In this single-limb circuit arrangement, inhaled air or gas is delivered from the device through the air delivery conduit to the patient interface, and exhaled air is expelled through the vent. The ventilator provides positive pressure at the vent to ensure complete expulsion of the patient's exhaled air.

[0038] In another arrangement, a single-limb line can be used with a proximal pneumatic valve. The proximal pneumatic valve is located near the patient interface end of the air delivery tubing. The other end of the air delivery tubing connects to the outlet of a device such as a ventilator or humidifier. A small tubing also connects between the device and the proximal pneumatic valve to provide a pressure control line. The device applies a control pressure to the proximal pneumatic valve to control the opening and closing of its exhaust port. During inhalation, the valve is fully closed, directing all airflow to the patient interface. During exhalation, the valve is appropriately controlled to allow the patient to exhale air from the exhaust port but at a specified back pressure (called positive end-expiratory pressure (PEEP)). The ventilator also continues to output a bias flow to ensure accurate control of PEEP and to compensate for any unintentional leakage at the patient interface. The pressure at the patient interface can be monitored using a pressure sensing line connected to a proximal pressure sensor within the ventilator.

[0039] In another arrangement, a dual-limb circuit can be used. A dual-limb circuit consists of two tubes: an inspiratory tube that delivers air from the ventilator to the patient during inspiration; and an expiratory tube that delivers exhaled air from the patient to the ventilator's expiratory port and then out through the exhaust port. Geometrically, the two tubes can be arranged side-by-side or coaxially. The airflow between the expiratory and exhaust ports can be regulated by a pneumatic valve located inside the ventilator.

[0040] During inspiration, the valve is fully closed, directing all airflow to the patient. During expiration, the valve is appropriately controlled to allow the patient to exhale through the exhaust port while maintaining the specified PEEP pressure. The ventilator also continues to output a bias flow to ensure accurate PEEP control and compensate for any unintentional leaks at the patient interface. During inspiration, the patient's pressure is monitored via a proximal pressure sensor connected to the ventilator's expiratory line; and during expiration, the patient's pressure is monitored via an output pressure sensor connected to the inspiratory line.

[0041] Heated single- or double-limb air delivery lines can also be used to prevent rain washing effects within the air delivery lines. Summary of the Invention

[0042] The purpose of this technology is to provide a medical device for use in the diagnosis, improvement, treatment or prevention of respiratory disorders that has one or more of the following characteristics: improved comfort, cost, efficiency, ease of use and manufacturability.

[0043] The first aspect of this technology relates to devices used in the diagnosis, improvement, treatment, or prevention of respiratory disorders.

[0044] Another aspect of this technology relates to methods used in the diagnosis, improvement, treatment, or prevention of respiratory disorders.

[0045] One form of this technology includes a device for treating respiratory disorders that is electrically connected to a plurality of external batteries connected in series.

[0046] Another aspect of this technology is a ventilator capable of being electrically connected to multiple external batteries connected in series.

[0047] Another aspect of this technology is a method for determining an estimate of the available battery capacity from two or more battery power sources electrically connected to a breathing device. For example, battery capacity may include remaining battery runtime or remaining battery charge.

[0048] Another aspect of this technology includes a device for treating respiratory disorders, the device comprising a housing, a user interface display, a pressure source for providing pressurized gas, a controller configured to control the pressure source, an electrical connection configured to receive an electrical connection for providing power to the device, and a plurality of external batteries electrically connected in series to the power connection.

[0049] The device's controller can be configured to detect the connection of multiple external batteries and control the power supply to the device. Furthermore, among the multiple external batteries used to supply power to the device during use, one can be a power supply external battery, and each of the multiple external batteries can be used sequentially as a power source, with the external battery closest to the power source being the first external battery to be used as a power source. Each of the multiple external batteries can be connected to adjacent external batteries using cables. The external battery closest to the ventilator can be the last external battery to be used. The series of external batteries can be recharged in reverse order, such that the external battery closest to the ventilator is recharged first.

[0050] In another arrangement, external batteries can be connected in series as a power source, with the external battery closest to the ventilator being the first external battery to be used. External batteries can also be recharged in series, with the last external battery closest to the ventilator being recharged.

[0051] Some aspects of the device may also include an internal battery, which is configured to be housed within a housing and, in use, serves as a power source after all power from the plurality of external batteries has been depleted.

[0052] Some aspects of the device may also include an AC power supply, which can be connected in series to multiple external batteries, and in use, when the AC power supply is connected, the AC power supply acts as a power source.

[0053] Some aspects of the device may also include a direct current (DC) power supply, which can be connected in series to multiple external batteries and, in use, serves as a power source when the DC power supply is connected.

[0054] In some aspects, when a power capacity request is received from the controller, each of the multiple external batteries is able to determine an estimate of its own remaining capacity. The remaining capacity of the external batteries can be used to determine an estimate of the total remaining operating time or state of charge of the external batteries. The total remaining operating time of the external batteries can be determined as a function of the remaining operating time of the power supply to the external batteries.

[0055] In some embodiments, multiple external batteries include an upstream external battery and a downstream external battery, wherein the upstream external battery is electrically connected to a power source connection, and the downstream external battery is electrically connected to the upstream external battery in a series. The upstream external battery can be connected to the power source connection using a cable. Furthermore, one or more additional external batteries can be electrically connected between the downstream external battery and the upstream external battery.

[0056] In some aspects, the upstream external battery is configured to send a determined estimate of its remaining capacity to the downstream external battery. Each of one or more additional external batteries can be configured to send the determined estimate of its remaining capacity along the string to the downstream external battery. The downstream external battery can be configured to determine the total remaining capacity or state of charge from all external batteries electrically connected in the string. The downstream external battery can be configured to determine the total remaining operating time from all external batteries electrically connected in the string as a function of the remaining operating time of the upstream external battery used to supply power to operate the device.

[0057] In some aspects, upon receiving a remaining capacity request from the controller, the internal battery can determine an estimate of its remaining capacity. This remaining capacity can be used to determine an estimate of the remaining runtime of the internal battery. The remaining runtime can be determined as a function of the remaining runtime of the internal battery when it is used to provide power to operate the device, or when one of a plurality of external batteries is used to power the device.

[0058] In some aspects, the controller can be configured to calculate an estimate of the total remaining battery capacity or total state of charge of multiple external and internal batteries. The controller can also be configured to calculate an estimate of the total remaining battery runtime of multiple external and internal batteries. In some forms, the user interface display can be configured to display the estimate of the total remaining battery capacity, the total remaining battery charge, and / or the estimate of the total remaining battery runtime.

[0059] In some respects, the equipment may be a ventilator.

[0060] One aspect of this technology includes a method for determining an estimate of the total available battery capacity from two or more battery power sources electrically connected to a breathing device, the breathing device including a controller configured to perform the following methods: requesting an estimate of the available capacity from a first battery power source to provide a first battery capacity level, requesting an estimate of the available capacity from a second battery power source to provide a second battery capacity level, and combining the first battery capacity level and the second battery capacity level to determine an estimate of the total available battery capacity.

[0061] In some respects, the total available battery capacity is an estimate of the total remaining capacity from the first battery power source and the second battery power source, or an estimate of the total remaining charge, or an estimate of the total state of charge.

[0062] In some aspects, the first battery power source is at least one external battery electrically connected to the breathing apparatus, and the second battery power source is an internal battery located within the breathing apparatus. The first battery power source may include a plurality of external batteries connected in series, each of the plurality of external batteries including an input port and an output port configured to receive a cable therebetween. The plurality of external batteries may include a downstream external battery, the output port of which is electrically coupled to the breathing apparatus via a cable, and the input port of which is electrically coupled to the output port of a second external battery among the plurality of external batteries via a cable. Furthermore, each of the plurality of external batteries may be electrically coupled to an adjacent external battery via a cable connecting the input port of one external battery to the output port of an adjacent external battery. The method may also include each external battery providing an estimate of its available capacity and transmitting the available capacity upstream of the external battery via a cable along the series. The method may also include displaying the total available battery capacity on a user interface display of the breathing apparatus.

[0063] Another aspect of this technology is a breathing device with improved power efficiency.

[0064] Another aspect of this technology is a breathing device for supplying breathable gas to a patient with continuous cyclic breathing, each cycle including an inhalation phase and an exhalation phase. The breathing device includes: a fan including a motor configured to accelerate to achieve an inspiratory pressure provided during the inhalation phase and decelerate to achieve an expiratory pressure provided during the exhalation phase; a first power source arranged to supply power to operate the motor of the fan; and an energy storage unit configured to store energy generated by the motor when the motor decelerates.

[0065] Specifically, when the voltage in the energy storage unit exceeds a first threshold, the power supply from the first power source to the motor is turned off, and the motor is powered by the energy in the energy storage unit. When the voltage in the energy storage unit drops below a second threshold, the power supply from the first power source to the motor is turned on.

[0066] In some aspects, the energy storage unit includes at least one capacitor or supercapacitor. In some aspects, the breathing device also includes a regulator switch that monitors the voltage of the energy storage unit and switches the power supply from the first power source to the motor on and off.

[0067] Of course, aspects can form sub-aspects of this technology. In addition, aspects and / or sub-aspects can be combined in different ways and also constitute other aspects or sub-aspects of this technology.

[0068] The features of this technology will become more apparent from the information contained in the detailed description, abstract, drawings and claims. Attached Figure Description

[0069] The technology is illustrated in the accompanying drawings by way of example rather than limitation, wherein the same reference numerals denote similar elements, in the drawings:

[0070] 3.1 Treatment System

[0071] Figure 1 A system according to the present technology is shown. A patient 1000 wearing a patient interface 3000 receives positive pressure air from a device or ventilator 4000. The air from the device is humidified in a humidifier 5000 and delivered to the patient 1000 along an air line 4170. In another arrangement (not shown), the humidifier may be located upstream or in front of the device or ventilator 4000.

[0072] 3.2 Treatment methods

[0073] 3.2.1 Respiratory System

[0074] Figure 2aThis diagram shows an overview of the human respiratory system, which includes the nasal cavity and oral cavity, larynx, vocal cords, esophagus, trachea, bronchi, lungs, alveolar sacs, heart, and diaphragm.

[0075] Figure 2b This diagram illustrates the human upper airway, which includes the nasal cavity, nasal bones, lateral nasal cartilages, larger alar cartilages, nostrils, upper lip, lower lip, larynx, hard palate, soft palate, oropharynx, tongue, epiglottis, vocal cords, esophagus, and trachea.

[0076] 3.3 Patient Interface

[0077] Figure 3 An exemplary patient interface of one form according to the present technology is shown.

[0078] 3.4 Ventilation Unit

[0079] Figure 4a A perspective view of one form of ventilator device according to the present technology is shown.

[0080] Figure 4b Show Figure 4a A front view of the ventilation unit in the image.

[0081] Figure 4c Show Figure 4a Rear view of the ventilation unit.

[0082] Figure 4d Show Figure 4a Bottom view of the ventilation unit in the middle.

[0083] Figure 4e A schematic diagram showing the arrangement of internal components in a ventilator according to one aspect of the present technology is provided.

[0084] Figure 4f A schematic diagram of the interior of a pneumatic block according to one aspect of the present technology is shown.

[0085] Figure 4g A schematic diagram of the pneumatic circuitry of one form of the device according to the present technology is shown. The upstream and downstream directions are indicated.

[0086] Figure 4h A schematic diagram of the electrical components of an apparatus according to one aspect of the present technology is shown.

[0087] Figure 4i A schematic diagram of an algorithm implemented in an apparatus according to one aspect of the present technology is shown. In this diagram, solid arrows indicate the actual flow of information, for example, via electronic signals.

[0088] Figure 4j A schematic diagram of the electrical arrangement of a ventilator equipped with AC power according to one aspect of the present technology is shown.

[0089] Figure 4k A schematic diagram is shown of a power arrangement for recharging an external battery of a ventilator that is provided with AC power independent of the ventilator, according to one aspect of the present technology.

[0090] Figure 4l A schematic diagram of the power arrangement of a ventilator powered by an external battery, according to one aspect of the present technology, is shown.

[0091] Figure 4m A schematic diagram of the power arrangement of a ventilator equipped with DC power according to one aspect of the present technology is shown.

[0092] Figure 4n A schematic diagram of a power regeneration circuit according to one aspect of the present technology is shown.

[0093] Figure 4o A schematic diagram of a power regeneration circuit including a boost regulator is shown according to another aspect of the present technology.

[0094] Figure 4p A schematic diagram of the HAC control system is shown.

[0095] 3.5 Humidifier

[0096] Figure 5 A schematic diagram of a humidifier according to one aspect of the present technology is shown.

[0097] 3.6 Respiratory waveform

[0098] Figure 6 This diagram illustrates a typical breathing waveform during sleep. The horizontal axis represents time, and the vertical axis represents respiratory flow. While parameter values ​​can vary, typical breathing can be approximated by the following: tidal volume, Vt, 0.5 liters; inspiratory time, Ti, 1.6 seconds; peak inspiratory flow rate, Q. 峰值 0.4 liters / second; Exhalation time, Te, 2.4 seconds; Peak expiratory flow rate, Q peak -0.5 liters / second. Total respiratory duration, Ttot, is approximately 4 seconds. Humans typically breathe at a rate of approximately 15 breaths per minute (BPM), with a ventilation rate, Vent, of approximately 7.5 liters / minute. The common duty cycle, Ti to Ttot, is approximately 40%. Detailed Implementation

[0099] Before providing a further detailed description of this technology, it should be understood that this technology is not limited to the specific embodiments that may vary as described herein. It should also be understood that the terminology used in this disclosure is for the purpose of describing the specific embodiments discussed herein and is not intended to be limiting.

[0100] 4.1 Treatment System

[0101] In one form, the technology includes a device for treating respiratory disorders. The device may include an airflow generator or fan for supplying pressurized breathing gas, such as air, to a patient 1000 via an air delivery tube 4170 leading to a patient interface 3000.

[0102] 4.2 Treatment methods

[0103] In one form, the technology includes a method for treating respiratory distress, comprising the step of applying positive pressure to the inlet of the airway of a patient 1000. Another form of the technology includes a method for treating respiratory distress, comprising the step of applying positive pressure to provide invasive ventilation to an intubated patient. Yet another form of the technology provides a method for treating respiratory distress, comprising the step of providing a pressure-switching or volume-switching treatment method.

[0104] 4.3 Patient Interface 3000

[0105] According to one aspect of the present technology, the non-invasive patient interface 3000 includes the following functional aspects: a hermetically formed structure 3100, a pressurization chamber 3200, a positioning and stabilizing structure 3300, and a connection port 3600 for connection to an air line 4170.

[0106] In one form of this technology, the sealing molding structure 3100 provides a sealing molding surface and may additionally provide a cushioning function. The sealing molding structure 3100 according to this technology may be made of a soft, flexible, elastic material such as silicone.

[0107] In one form, the sealing shaping portion of the non-invasive patient interface 3000 includes a pair of nasal suctions or a pair of nasal pillows, each nasal suction or nasal pillow being constructed and arranged to form a seal to the corresponding nostril of the patient's nose.

[0108] In one form, the non-invasive patient interface 3000 includes a sealing form used on the upper lip region (i.e., the upper lip) of the patient's face to form a seal.

[0109] In one form, the non-invasive patient interface 3000 includes a sealing molding portion used on the chin area of ​​the patient's face to form a seal.

[0110] In some forms, functional aspects can be provided by one or more physical components. In some forms, a single physical component can provide one or more functional aspects. In use, the sealing-forming structure 3100 is arranged around the inlet of the patient's airway to facilitate the supply of air to the airway at positive pressure. Preferably, the pressurization chamber 3200 has a periphery shaped to complement the surface contour of the face in the area where a normal person forms a seal during use. In use, the boundary edges of the pressurization chamber 3200 are positioned close to the adjacent surface of the face. Actual contact with the face is provided by the sealing-forming structure 3100. Preferably, the sealing-forming structure 3100 extends around the entire periphery of the pressurization chamber 3200 during use.

[0111] Preferably, the sealing molding portion 3100 of the patient interface 3000 of this technology is held in a sealed position during use by a positioning and stabilizing structure 3300, such as a headgear.

[0112] In one embodiment, the patient interface 3000 includes a vent 3400, configured and arranged to flush out exhaled carbon dioxide. According to this technology, the vent 3400 includes a plurality of holes, for example, about 20 holes to about 80 holes, or about 40 holes to about 60 holes, or about 45 holes to about 55 holes. Preferably, the vent 3400 is located in a pressurization chamber 3200. In one embodiment, the patient interface 3000 may further include at least one decoupling structure 3500, such as a swivel or ball and slot. The vent 3400 may be located in the decoupling structure 3500. A connection port 3600 enables connection to an air line 4170.

[0113] The patient interface 3000 may also include a forehead support 3700. The patient interface may also include an anti-asphyxiation valve.

[0114] In one embodiment of this technology, the patient interface 3000 includes one or more ports that allow access to a volume within the pressurization chamber 3200. In one embodiment, this allows a clinician to supply supplemental oxygen. In one embodiment, this allows for direct measurement of properties of the gas within the pressurization chamber 3200, such as pressure.

[0115] 4.4 Device 4000

[0116] One form of ventilator device 4000 according to the present technology is shown. Figures 4a to 4eThe ventilator 4000 includes a housing 4012, an expiratory inlet port 4014, and an inspiratory outlet port 4016. Ports 4014 and 4016 are connected to a tube (not shown) that can be inserted into a patient's trachea, to a face or nasal mask that can be fitted over the patient's nose or mouth or both, or otherwise attached to the patient to assist breathing. The housing of the ventilator may be portable and includes a handle 4018 for carrying the ventilator. The housing may have an upper housing 4020, a base frame 4021, and a lower housing 4022 coupled together to form the outer surface of the ventilator. However, it should be understood that the housing may have other configurations, such as including only two components having an upper housing and a lower housing, or may have more than three components. The ventilator may include aspects of a ventilator or a ventilator as described in co-pending U.S. Patent Application No. 13 / 624,167, filed September 21, 2012, the contents of which are incorporated herein by reference.

[0117] The base frame 4021 can provide a structural skeleton for the ventilator assembly. The base frame 4021 can be configured to receive the inlet filter assembly 4036 and the inlet seal 4038, which are described in detail below. The inlet seal 4038 is also configured to be coupled to the inlet of the pneumatic block module 4056. Preferably, the inlet seal 4038 is formed of a flexible material such as silicone, and the inlet seal can be molded onto the inlet of the pneumatic block module 4056.

[0118] The base frame 4021 may also include a pneumatic block seat, wherein the pneumatic block module 4056 is located in the pneumatic block seat to facilitate the alignment and assembly of the pneumatic block module 4056 within the housing. The base frame 4021 may also include a portion of a handle 4018.

[0119] The rear of the base frame 4021 may include interfaces for various connections and switches on the rear panel. For example, interfaces for electrical connectors 4049, switches 4051, data connections 4047, and oxygen connections 4046.

[0120] The base frame 4021 may also provide interfaces for positioning and holding components of the ventilator 4000, such as the cooling fan 4068, the PCB 4086, and the components of the exhalation section 4031 positioned adjacent to the exhalation inlet port 4014 (see [link]). Figure 4e ).

[0121] The expiratory section 4031 of the ventilator 4000 is configured to allow insertion of an expiratory interface module to receive the patient's exhaled air via the expiratory inlet port 4014. Different expiratory interface modules may include an expiratory valve and an expiratory adapter.

[0122] See also Figures 4a to 4eThe ventilator 4000 may include a battery compartment that positions and interfaces with a removable internal battery 4450. A removable battery cover 4052 is provided on the outer bottom surface of the lower housing 4022 to allow access for inserting or removing the battery. A heat dissipation grid 4044, a removable exhalation cap 4048, and an oxygen sensor cap 4054 are also provided on the outer bottom surface, as shown below. Figure 4d As shown. The lower housing 4022 may also include anti-slip feet or gripping surfaces on the outer bottom surface, or one or more anti-slip or gripping feet 4053, such as thermoplastic polyurethane (TPU) feet, to prevent the ventilator 4000 from slipping off smooth surfaces. The anti-slip or gripping feet 4053 may also raise the ventilator 4000 to prevent decomposed water from accumulating in a pool below the bottom surface of the ventilator. A portion of the handle 4018 is also located within the lower housing 4022.

[0123] like Figure 4a As shown, the upper housing 4020 provides the top surface of the ventilator 4000 and is configured to receive a user interface display device 4024. The housing may include a computer or processor that drives the user interface display device 4024, such as a liquid crystal display (LCD) adapted to receive touch input from a computer. The display device may be flush with the top surface of the housing for easy visibility when the ventilator is in use. An alarm indicator light bar 4026, such as a light-emitting diode (LED) light bar, and a button 4028 for disabling audio or visual alarms may be adjacent to the display. However, it should be understood that other known user interface systems such as screens, buttons, dials, keys, or combinations thereof may be used. The base frame 4021, lower housing 4022, and upper housing 4020 are coupled together to assemble the complete ventilator housing 4012. Although any other known fasteners may be used, fasteners such as screws may be used to assemble the housing 4012. The base frame 4021 is assembled between the upper housing 4020 and the lower housing 4022.

[0124] like Figure 4d As shown, the rear portion of housing 4012 may include a filter assembly 4036. Air pumped into the patient's lungs is drawn into an air inlet associated with the filter assembly. The air passes through a permeable filter membrane in the filter and enters an air passage that directs airflow to the patient.

[0125] The rear of the housing may include a data connection 4047 for communicating with digital devices such as computer networks, alarm systems, pulse oximeters (e.g., SpO2), and digital recording media. A power connection 4049 and an on / off switch 4051 may also be located at the rear of the housing. The input grid 4044-I is provided with an air inlet for cooling components and allowing dissipation of heat generated by the operation of internal components (e.g., blower motors and CPUs). The flow of hot air through the internal components can be driven by a cooling fan 4068 within the housing, which may be adjacent to the hot air output grid 4044-O (shown in…). Figure 4d (At the bottom of the housing). In addition, an oxygen (O2) inlet port 4046 can be located at the rear of the housing, which allows coupling with an oxygen source.

[0126] Figure 4d The bottom of the ventilator 4000 is shown. A removable exhalation cap 4048, serving as an external hatch, provides access to and protects the housing section or the compartment of the exhalation section. Removing the exhalation cap 4048 provides access to any inserted exhalation gas routing module and the exhalation inlet port 4014. Exhalation gas routing modules such as exhalation valves or exhalation adapters can also be easily removed and replaced. The exhalation cap 4048 can be secured to the housing by a latch 4050 that can be turned with a finger to reduce excessive manipulation. Optionally, in some embodiments, the latch may help to lock the latch to prevent it from being released. An optional latch release button 4050R can be operated to unlock the exhalation cap. The release button 4050R can be pressed to unlock the exhalation cap 4048. Those skilled in the art will understand that the exhalation cap 4048 can also be removably secured and coupled to the housing in other ways. The bottom of the ventilator housing may also have a removable battery cover 4052 for a replaceable internal battery and an oxygen sensor cover 4054 that can be removed to access the oxygen sensor 4047.

[0127] Figure 4e The internal components of a ventilator 4000 according to one aspect of the present technology are shown. The ventilator 4000 may include some or all of the following components: inlet filter 4034, inlet seal 4038, inlet silencer 4039, oxygen supply path 4043, pneumatic block module 4056, inhalation section 4033, safety valve 4085, exhalation section 4031, PCB and control components 4086, cooling fan 4068, and internal battery 4450.

[0128] A pneumatic block module 4056 is arranged within the ventilator such that the air passage of the pneumatic block module 4056 is aligned with the filter assembly 4036 at the air inlet 4034, the intake / exhaust port 4016, and the oxygen supply path 4043. Arrows indicate the paths of the airflow 4035 and the oxygen flow 4045 through the ventilator 4000, respectively. The airflow 4035 enters via the air inlet 4034 and travels through the filter assembly 4036 and the inlet seal 4038 to the inlet silencer 4039 of the pneumatic block module 4056. Optionally, an oxygen source can be attached at the oxygen inlet port 4046, and the oxygen flow 4045 is directed through the oxygen supply path 4043 and the oxygen seal to the pneumatic block module 4056, where the oxygen flow 4045 combines with the intake airflow 4035 within the inlet silencer 4039. Within the pneumatic block module 4056, the airflow 4035 is pressurized by the main fan 4104 (see...). Figure 4f The pressurized air flow 4035 / pressurized oxygen flow 4045 is directed out of the pneumatic block module 4056 via the outlet silencer 4084 and enters the inhalation section 4033 through the main seal 4040, and is then output from the inhalation outlet port 4016 and delivered to the patient interface (not shown) via an air delivery conduit (not shown).

[0129] An oxygen sensor 4064, located in the oxygen sensor compartment of the inhalation section 4033, measures the amount of oxygen delivered to the patient. The oxygen sensor 4064 can be mounted in the housing 4012 for easy replacement and adjacent to the inhalation / outhalation ports 4016. The oxygen sensor detects the oxygen level in the air pumped to the patient. Data from the oxygen sensor can be used to trigger an alarm related to oxygen concentration and to provide data to a microprocessor for displaying the oxygen concentration on a user interface. The amount of oxygen supplied can be controlled by adjusting the oxygen supplied to the patient and the known volume of air. However, the oxygen sensor can also optionally be used to regulate the amount of supplemental oxygen supplied through the oxygen inlet port 4046.

[0130] The oxygen sensor cover 4054 on the bottom of the housing. Figure 4d (As shown) is removable to provide access to an oxygen sensor contained within the oxygen sensor compartment of the housing. The oxygen sensor is mounted in a base within the housing and adjacent to the inspiratory / outflow port 4016. The oxygen sensor detects a portion of the airflow through the inspiratory / outflow port 4016. The sensor generates a data signal indicating the oxygen level in the gas. The data is transmitted to a data connection that transmits the data to a processor. The processor analyzes the data to determine the amount of supplemental oxygen to be added to the air pumped to the patient.

[0131] The oxygen source can be a low-pressure oxygen supply or a high-pressure oxygen supply. For a high-pressure oxygen supply, an oxygen regulator (not shown) can be located within the oxygen supply path 4043 to reduce the pressure from the high-pressure oxygen source before the oxygen enters the inlet silencer 4039. The oxygen inlet port 4046 can be adapted to couple to several different oxygen connection adapters so that different types of oxygen connectors can be used for different jurisdictions, including but not limited to male or female diameter index safety systems (DISS), sleeve index systems (SIS), the National Institute of Standards and Technology (NIST), and the French Association for Standardization (AFNOR).

[0132] In another configuration (not shown), a high-pressure oxygen source may be located downstream of the main fan 4104, such as within an exhaust silencer 4084, where it is mixed with a pressurized air source. In some examples, the high-pressure oxygen may be used to provide a pressure source for the gas flowing to the patient. In some arrangements, low-pressure oxygen may optionally be supplied to the air line 4170 or the patient interface 3000.

[0133] Although the pneumatic block module 4056 is schematically shown as a rectangular shape, it should be understood that the pneumatic block module 4056 can have any shape that includes a seat that conforms to the housing and minimizes the possibility that the pneumatic block module 4056 may be improperly inserted into the housing.

[0134] The main printed circuit board (PCB) 4086 can be assembled and mounted to the base 4021 and positioned between the base frame 4021 and the lower housing 4022. Electronic components on the main circuit board may include a processor, electrical connectors for transmitting data signals, such as electrical signals, from the pneumatic block module 4056, and a data connector for a fan supplying pressurized air to the intake and exhaust ports 4016. In this regard, the electrical connectors provide power and signal paths between the electronic components on the PCB in the pneumatic block module 4056 and the electronic components on the main PCB in the housing. The electronic components on the main circuit board may also include data and power connectors for any sensor, such as the oxygen sensor 4064. The electronic components in the housing can control the generation of images on the display device, the generation of sound signals from the speaker 4061, such as those used to create an audible alarm, the detection of signals from the pressure and oxygen sensors, and the control of the fan's rotational speed. The ventilator 400 may optionally include a clock connected to the PCB 4086.

[0135] The base frame 4021 may include multiple mounts or compartments configured to receive different components of the ventilator 4000, such as a pneumatic block mount that may conform to the perimeter of the pneumatic block module 4056, a filter seat and / or compartment for the inlet filter assembly 4036, and other mounts for the low-pressure oxygen connection assembly, cooling fan 4068, and deformable seals. The base frame 4021 may also include embedded or integrated air passages and ports that can be molded within the base frame structure for conveying air between base frame sections or compartments. For example, air may be directed at a known pressure from the pneumatic block module to the PEEP air supply through passages in the base frame.

[0136] Figure 4f This is a schematic diagram of the internal components of the pneumatic block module 4056. The pneumatic block module 4056 includes a main fan 4104 with a volute assembly 4108, an inlet check valve assembly 4114, an optional oxygen inlet port 4144, a positive end-expiratory pressure (PEEP) fan 4124, an outlet silencer 4084, a safety valve 4085, a pressure sensor 4128, a flow sensor 4130 and a flow meter 4132, and a PEEP pressure sensor 4142. The volute assembly 4108 forms the main air passage and performs some of the key functions of the pneumatic block module 4056.

[0137] The pneumatic block module 4056 may include an electric valve 4116 and a flow control electric valve 4120 configured to communicate with and control the check valve assembly 4114. A PEEP electric valve 4136 is configured to communicate with a PEEP blower 4124 to control the pressure supplied by the blower 4124 to the exhalation section 4031. A PEEP pressure line is coupled between the PEEP supply port in the exhalation section 4031 and the PEEP exhalation valve to provide a PEEP pressure source. A PEEP pressure sensor 4142 senses the PEEP pressure.

[0138] Figure 4g A schematic arrangement of another form of device 4000 is shown. The pneumatic path of device 4000 preferably includes an inlet filter 4034, an inlet silencer 4039, a controllable source pressure device 4140 (preferably a main fan 4104) capable of supplying air at positive pressure, and an outlet silencer 4084. One or more sensors or sensors 4270, such as pressure sensor 4128 and flow sensor 4130, are included in the pneumatic path.

[0139] The preferred pneumatic block 4056 includes a portion of the pneumatic path located within the outer housing 4012.

[0140] Device 4000 preferably includes a power supply 4210, one or more input devices 4220, a central controller 4230, a pneumatic controller 4240, a treatment device 4245, one or more protection circuits 4250, a storage device 4260, a sensor 4270, a data communication interface 4280, and one or more output devices 4290. Electrical components 4200 may be mounted on a single printed circuit board assembly (PCBA). In another form, device 4000 may include more than one PCBA.

[0141] The central controller 4230 of the device 4000 is programmed to execute one or more algorithm module groups 4300 during use, preferably including a preprocessing sensor signal module 4310, a treatment tool module 4320, a pressure control module 4330, and more preferably including a fault status module 4340. 4.4.1 Mechanical & Pneumatic Components of the Device

[0142] 4.4.1.1 One or more air filters 4110

[0143] One form of device according to the present technology may include one or more air filters 4110.

[0144] In one configuration, the inlet filter 4034 is located at the beginning of the pneumatic path upstream of the fan 4104. See also Figure 4g .

[0145] In one configuration, an exhaust filter 4150, such as an antibacterial filter, is located between the outlet of the pneumatic block 4056 and the patient interface 3000. See also Figure 4g .

[0146] 4.4.1.2 One or more silencers 4120

[0147] In one embodiment of this technology, the inlet silencer 4039 is located upstream of the aerodynamic path of the fan 4104. See also Figure 4g .

[0148] In one embodiment of this technology, the exhaust silencer 4084 is located in the pneumatic path between the fan 4104 and the patient interface 3000. See also Figure 4g .

[0149] 4.4.1.3 Pressure Device 4140

[0150] In a preferred embodiment of this technology, the pressure device 4140 for generating a positive pressure airflow is a controllable main fan 4104. For example, the main fan may include a brushless DC motor 4404a having one or more impellers housed in a volute. Preferably, the fan is capable of delivering air at a rate, for example, between about 10 liters / minute and about 120 liters / minute, to achieve a positive pressure supply of about 60 cmH2O, ranging from about 3 cmH2O to about 40 cmH2O, or otherwise.

[0151] The pressure device 4140 is under the control of the pneumatic controller 4240.

[0152] 4.4.1.4 One or more sensors 4270

[0153] In one form of this technology, one or more sensors or sensor 4270 are located upstream of pressure device 4140. One or more sensors 4270 are constructed and arranged to measure the properties of the air at that point in the pneumatic path.

[0154] In one form of this technology, one or more sensors 4270 are located downstream of the pressure device 4140 and upstream of the air line 4170. One or more sensors 4270 are constructed and configured to measure the properties of the air at that point in the pneumatic path.

[0155] In one form of this technology, one or more sensors 4270 are positioned close to the patient interface 3000. The one or more sensors 4270 may include, for example, a pressure sensor, a flow sensor, a velocity sensor, or an oxygen sensor.

[0156] 4.4.1.5 Anti-overflow valve 4160

[0157] In one embodiment of this technology, an anti-backflow valve is located between an optional humidifier 5000 and the device 4000. The anti-backflow valve is constructed and arranged to reduce the risk of water flowing upstream from the humidifier 5000 to, for example, the motor 4104.

[0158] 4.4.1.6 Air Line 4170

[0159] An air delivery line 4170 according to one aspect of the present technology is constructed and arranged such that air or breathable gas can flow between an outlet of device 4000, such as an inspiratory / exhaust port 4016, and a patient interface 3000. The air delivery line 4170 may include a single-limb line or a dual-limb line. A dual-limb line includes an expiratory conduit for delivering exhaled air from the patient back to the ventilator and out through an exhaust port. The exhaust port may include a filter, such as an antibacterial filter.

[0160] 4.4.1.7 Oxygen Delivery 4180

[0161] In one form of this technology, supplemental oxygen 4180 is delivered to a point in the pneumatic path.

[0162] In one form of this technology, supplemental oxygen 4180 is delivered upstream of pneumatic block 4056.

[0163] In one form of this technology, supplemental oxygen 4180 is delivered to air line 4170.

[0164] In one embodiment of this technology, supplemental oxygen 4180 is delivered to the patient interface 3000. 4.4.2 Electrical components of the device 4200

[0165] 4.4.2.1 Power Supply 4210

[0166] Power supply 4210 supplies power to other components of the basic device 4000—input device 4220, central controller 4230, treatment device 4245, and output device 4290.

[0167] In one form of this technology, the power supply 4210 may include an internal power supply such as an internal battery 4450 that may be removably located within the outer housing 4012 of the device 4000 (see [link to relevant documentation]). Figure 4j The internal battery 4450 can be a lithium-ion battery and can be configured to provide 4 to 12 hours of use time, such as up to 4, 5, 6, 7, or 8 hours of continuous use. The internal battery 4450 can provide a voltage of 10 to 18 volts direct current (DC) power, such as a DC power range of 12 to 16.8 volts, and has a power output of 90 to 100 watts (W) per hour (hr), such as approximately 95 watts per hour.

[0168] In another form of this technology, the power supply 4210 may alternatively or additionally include one or more external power supplies, such as external batteries 4410, 4420 (see [link to relevant documentation]), configured to be connected via wires to a power source connected to the device 4000. Figures 4j to 4m Multiple external batteries can be connected in series to the device or ventilator 4000, for example, two, three, four or more external batteries can be connected in series to the device 4000. External batteries 4410, 4420 can be connected to the device or ventilator 4000 and connected to each other via cables such as DC cables or power lines 4462. Figures 4l to 4m A downstream external battery 4410 and an upstream external battery 4420 connected in series with the ventilator 4000 are shown. It should be understood that an additional external battery (not shown) may be connected in series between the downstream external battery 4410 and the upstream external battery 4420 to extend the available external battery power.

[0169] Each external battery includes an input port and an output port to allow cables for transmitting power and signals to be connected along the string. Each of the external batteries 4410 and 4420 can be identical or different, meaning they can each provide the same or different power. The external batteries can provide power for 2 to 12 hours of use, such as up to 4, 5, 6, 7, or 8 hours of continuous use. The external batteries 4410 and 4420 can provide direct current (DC) power from 10 to 30 volts, such as in the range of 24 to 26 volts, and have a power output from 90 to 100 watts (W) per hour (hr), such as approximately 95 watts per hour, 96 watts per hour, and 97 watts per hour.

[0170] In another arrangement, the power supply 4210 enables connection to an alternating current (AC) power source (see reference 4430) via an AC power supply unit (PSU). Figure 4j The AC PSU 4430 can be a switch-mode power supply with a universal input range of 80 volts to 270 volts or 100 volts to 240 volts. The AC PSU 4430 can provide an output power of 60 watts to 100 watts (W), approximately 90 W, and a power supply of approximately 24 volts DC. The AC PSU 4430 is suitable for use in aircraft. The AC PSU 4430 can be directly connected to the power source of the ventilator or device 4000 (i.e., without an external battery connected to the ventilator 4000, not shown), or connected in series upstream of a battery or external battery 4410, 4420 electrically connected to the ventilator 4000, such as... Figure 4j As shown.

[0171] exist Figure 4m In another arrangement shown, power supply 4210 allows connection to DC main power supply 4460 via DC main power line 4462. The DC main power supply can provide approximately 12 volts to 24 volts of power. DC main power line 4462 can be electrically connected between the power source connection of the ventilator or device 4000 and the DC main power supply 4460 without any intermediate external battery (not shown). Additionally, as... Figure 4mAs shown, one or more of the upstream external battery 4420 and the downstream external battery 4410 may also be connected in series between the ventilator 4000 and the DC main power supply. In one arrangement, if the external batteries 4410 and 4420 are connected, they are not charged via the DC power supply when the device is in use. However, alternatively, the DC main power supply may charge the external batteries 4410 and 4420 according to the power usage requirements of the device 4000 and the available power supplied by the DC main power supply 4460. The internal battery 4450 may also be present in the ventilator 4000 and may optionally be charged via the DC main power supply 4460.

[0172] It should be understood that the power capacity ranges described above are merely exemplary and that the AC PSU 4430, internal battery 4450, and external batteries 4410 and 4420 may have different power capacities and outputs than those described above. The power management of the device 4000 will be described in more detail below.

[0173] 4.4.2.1.1 One or more input devices 4220

[0174] Input device 4220 includes buttons, switches, or dials to enable a person to interact with device 4000. The buttons, switches, or dials can be physical or software devices accessible via a touchscreen. In one form, the buttons, switches, or dials can be physically connected to an external housing 4012, or in another form, the buttons, switches, or dials can wirelessly communicate with a receiver electrically connected to a central controller 4230.

[0175] In one form, the input device 4220 can be constructed and arranged to enable a person to select values ​​and / or menu options.

[0176] 4.4.2.1.2 Central Controller 4230

[0177] In one form of this technology, the central controller or processor 4230 is a dedicated electronic circuit configured to receive one or more input signals from the input device 4220 and to provide one or more output signals to the output device 4290 and / or the treatment device controller 4245.

[0178] In one form, the central controller 4230 is a dedicated application integrated circuit. In another form, the central controller 4230 includes discrete electronic components.

[0179] The processor 4230 is configured to receive one or more input signals from one or more sensors 4270 and one or more input devices 4220.

[0180] The processor 4230 is configured to provide one or more output signals to one or more of the output device 4290, the pneumatic controller 4240, the data communication interface 4280, and the humidifier controller 5250.

[0181] In some forms of this technology, processor 4230 or more such processors are configured to execute one or more methods described herein, such as one or more algorithms 4300 represented as computer programs stored in a non-transitory computer-readable storage medium such as memory 4260. As previously discussed, in some cases, one or more such processors may be integrated with device 4000. However, in some forms of this technology, for example, to execute any of the methods described herein without directly controlling the supply of respiratory therapy, one or more processors may be executed separately according to the pressure generating component of device 4000. For example, such processors may execute any of the methods described herein to determine control settings for ventilators or other respiratory-related events by analyzing stored data from any of the sensors described herein.

[0182] 4.4.2.1.3 Treatment device 4245

[0183] In one form of this technology, the treatment device 4245 is configured to provide treatment to a patient under the control of a central controller 4230.

[0184] 4.4.2.1.4 Output device 4290

[0185] The output device 4290 according to this technology can take one or more forms of visual output, audio output, and tactile output. Visual output can be a liquid crystal display (LCD) or a light-emitting diode (LED) display. Audio output can be a speaker or an audio transmitter.

[0186] 4.4.2.1.5 Clock 4232

[0187] Preferably, the device 4000 includes a clock 4232 connected to the processor 4230.

[0188] 4.4.2.1.6 Pneumatic Controller 4240

[0189] In one form of this technology, the pneumatic controller 4240 is a pressure control module 4330 that forms part of an algorithm 4300 executed by the processor 4230.

[0190] In one form of this technology, the pneumatic controller 4240 is a dedicated motor control integrated circuit.

[0191] In one form of this technology, the pneumatic controller 4240 is a pneumatic block processor 4630.

[0192] 4.4.2.1.7 Protect line 4250

[0193] Preferably, the device 4000 according to the present technology includes one or more protection lines 4250.

[0194] According to this technology, one form of protection circuit 4250 is a pneumatic block safety circuit 4632.

[0195] According to this technology, one form of protection circuit 4250 is an electrical protection circuit.

[0196] According to this technology, one form of protection circuit 4250 is a temperature or pressure safety circuit.

[0197] According to this technology, one form of protection circuit 4250 is an alarm controller. The alarm controller can be, for example, a hardware alarm controller 4610, described in more detail below.

[0198] 4.4.2.1.8 Storage 4260

[0199] According to one embodiment of the present technology, device 4000 includes memory 4260, preferably non-volatile memory. In some embodiments, memory 4260 may include battery-powered static RAM. In some embodiments, memory 4260 may include volatile RAM.

[0200] Preferably, the memory 4260 is located on the PCBA. The memory 4260 may be in the form of EEPROM or NAND flash memory.

[0201] Alternatively or alternatively, the device 4000 includes a removable storage device 4260, such as a memory card made according to the Secure Digital (SD) standard.

[0202] In one form of the present technology, the memory 4260 is used as a non-transitory computer-readable storage medium on which computer program instructions representing one or more methods such as one or more algorithms 4300 described herein are stored.

[0203] 4.4.2.1.9 Sensor 4270

[0204] Sensors can be located inside or outside the device. For example, external sensors can be located on or form part of an air delivery line, such as a patient interface. External sensors can be in the form of non-contact sensors that send or transmit data to the device, such as Doppler radar motion sensors.

[0205] 4.4.2.1.9.1 Traffic volume 4272

[0206] The flow sensor 4272 according to this technology can be based on a differential pressure sensor, such as the SDP600 series differential pressure sensor from SENSIRION or the Zephyr sensor from HONEYWELL. TM Flow sensor. Differential pressure sensor is in fluid communication with the pneumatic circuit, and each differential pressure sensor is connected to a corresponding first and second point in the flow limiting element.

[0207] In use, the processor 4230 receives a signal representing the total flow rate Qt from the flow sensor 4272.

[0208] 4.4.2.1.9.2 Pressure 4274

[0209] The pressure sensor 4274 according to this technology is positioned in fluid communication with a pneumatic circuit. An example of a suitable pressure sensor is the sensor from the Honeywell ASDX series. Another suitable pressure sensor is the sensor from the General Electric NPA series. Another alternative suitable pressure sensor is the Honeywell TruStability. TM Pressure sensor series.

[0210] In use, the processor 4230 receives signals from the pressure sensor 4274. In one embodiment, the signals from the pressure sensor 4274 are filtered before being received by the processor 4230.

[0211] 4.4.2.1.9.3 Motor speed 4276

[0212] In one form of this technology, a motor speed signal 4276 is generated. Preferably, the motor speed signal 4276 is provided by a pneumatic controller 4240. For example, the motor speed can be generated by a speed sensor such as a Hall effect sensor.

[0213] 4.4.2.1.10 Data Communication System 4280

[0214] In a preferred embodiment of this technology, a data communication interface 4280 is provided and connected to a processor 4230. Preferably, the data communication interface 4280 can be connected to a remote external communication network 4282. Preferably, the data communication interface 4280 can be connected to a local external communication network 4284. Preferably, the remote external communication network 4282 can be connected to a remote external device 4286. Preferably, the local external communication network 4284 can be connected to a local external device 4288.

[0215] In one configuration, the data communication interface 4280 is part of the processor 4230. In another configuration, the data communication interface 4280 is an integrated circuit independent of the processor 4230.

[0216] In one embodiment, the remote external communication network 4282 is the Internet. The data communication interface 4280 can be connected to the Internet using wired communication (e.g., via Ethernet or fiber optic) or wireless protocols.

[0217] In one form, the local external communication network 4284 uses one or more communication standards, such as Bluetooth or consumer infrared protocols.

[0218] In one form, the remote external device 4286 is one or more computers, such as a cluster of networked computers. In another form, the remote external device 4286 may be a virtual computer rather than a physical computer. In either case, such a remote external device 4286 may be accessed by an appropriately authorized person, such as a clinician.

[0219] Preferably, the local external device 4288 is a personal computer, mobile phone, tablet computer, or remote control.

[0220] 4.4.2.1.11 Includes an optional display and an output device for the alarm 4290.

[0221] The output device 4290 according to this technology can take the form of one or more of a visual unit, an audio unit, and a tactile unit. The visual display can be a liquid crystal display (LCD) or a light-emitting diode (LED) display 4298. The audio display can be a buzzer 4296.

[0222] 4.4.2.1.11.1 Display Driver 4292

[0223] Display driver 4292 receives characters, symbols, or images intended to be displayed on display 4294 as input and converts them into commands to make display 4294 display those characters, symbols, or images.

[0224] 4.4.2.1.11.2 Monitor 4294

[0225] The display 4294 is configured to visually display characters, symbols, or images in response to commands received from the display driver 4292.

[0226] 4.4.3 Device Algorithm 4300

[0227] 4.4.3.1 Preprocessing Module 4310

[0228] like Figure 4iAs shown, the preprocessing module 4310 according to the present technology receives raw data from a sensor, such as a flow sensor or a pressure sensor, as input, and preferably performs one or more processing steps to calculate one or more output values ​​that will be used as input to another module, such as the treatment tool module 4320.

[0229] In one form of this technology, the output values ​​include the interface or mask pressure Pm, the breathing flow rate Qr, and the leakage flow rate Ql.

[0230] In different forms of this technology, the preprocessing module 4310 includes one or more of the following algorithms: pressure compensation 4312, ventilation 4314, leakage flow 4316, breathing flow 4318, and interference detection 4319.

[0231] 4.4.3.1.1 Pressure Compensation 4312

[0232] In one embodiment of this technology, the pressure compensation algorithm 4312 receives a signal indicating the pressure in the pneumatic path near the outlet of the pneumatic block as input. The pressure compensation algorithm 4312 estimates the pressure drop in the air line 4170 and sets the estimated pressure Pm in the patient interface 3000 as output.

[0233] 4.4.3.1.2 Ventilation volume 4314

[0234] In one form of this technology, the ventilation calculation algorithm 4314 receives an estimated pressure Pm in the patient interface 3000 as input and estimates the ventilation volume Qv of the air from the air vent 3400 in the patient interface 3000.

[0235] 4.4.3.1.3 Leakage flow rate: 4316

[0236] In one form of this technology, the leakage flow algorithm 4316 receives the total flow rate Qt and the ventilation rate Qv as inputs, and sets the leakage flow rate Ql as output by calculating the average of Qt to Qv over a period of time long enough to include several respiratory cycles, such as about 10 seconds.

[0237] In one form, the leakage flow algorithm 4316 receives the total flow rate Qt, ventilation volume Qv, and estimated pressure Pm from the patient interface 3000 as input, and sets the leakage flow rate Ql as output by calculating the leakage conductivity and determining that the leakage flow rate Ql is a function of the leakage conductivity and pressure Pm. Preferably, the calculated leakage conductivity is the quotient of the non-ventilation volumes Qt to Qv under low-pass filtering and the square root of the pressure Pm under low-pass filtering, wherein the value of the low-pass filtering time constant is a value long enough to include a period of time such as about 10 seconds.

[0238] 4.4.3.1.4 Respiratory flow rate 4318

[0239] In one form of this technology, the respiratory flow algorithm 4318 receives total flow rate Qt, tidal volume Qv, and leakage flow rate Ql as inputs, and estimates the respiratory flow rate Qr of the air supplied to the patient by subtracting the tidal volume Qv and leakage flow rate Ql from the total flow rate Qt.

[0240] 4.4.3.2 Treatment Tool Module 4320

[0241] In one form of this technology, the treatment tool module 4320 receives one or more of the pressure Pm and the breathing flow rate Qr of the air supplied to the patient from the patient interface 3000 as inputs, and sets one or more treatment parameters as outputs.

[0242] In one form of this technique, the treatment parameter is the treatment pressure Pt.

[0243] In one form of this technique, the treatment parameters are one or more of the level of pressure support and the target ventilation.

[0244] 4.4.3.2.1 Stage Determination 4321

[0245] In one form of this technology, the stage determination algorithm 4321 receives a signal indicating respiratory flow Qr as input and sets the stage of the patient's respiratory cycle 1000 as output.

[0246] In one form, the stage output is a discrete variable with either an inhalation value or an exhalation value.

[0247] In one form, the stage output is a discrete variable with one of the following values: inhalation value, mid-inspiratory pause value, and exhalation value.

[0248] In one form, the stage output is continuously variable, for example, from 0 to 1, or from 0 to 2Pi.

[0249] In one form, when the respiratory flow rate Qr has a positive value exceeding a positive threshold, the stage output is determined to have discrete values ​​for inhalation. In another form, when the respiratory flow rate Qr has a negative value less than a negative threshold, the stage is determined to have discrete values ​​for exhalation.

[0250] 4.4.3.2.2 Waveform Determination 4322

[0251] In one form of this technology, the control module 4330 controls the treatment device 4245 to set a substantially constant positive airway pressure throughout the patient's respiratory cycle.

[0252] In one embodiment of this technology, the control module 4330 controls the treatment device 4245 to set positive airway pressure according to a predetermined waveform of pressure stages. In one embodiment, the waveform remains at a substantially constant level for all values ​​of the stages. In another embodiment, the waveform is a square wave with values ​​higher than some stages and levels lower than others.

[0253] In one form of this technology, the waveform determination algorithm 4322 receives a value indicating the current patient ventilation (Vent) as input and sets the waveform of the pressure pair phase as output.

[0254] 4.4.3.2.3 Determination of ventilation volume 4323

[0255] In one form of this technology, the ventilation determination algorithm 4323 receives respiratory flow Qr as input and determines a measurement indicating the patient's tidal volume Vent.

[0256] In one form, the ventilation determination algorithm 4323 determines the current value of the patient ventilation Vent as half the absolute value of the low-pass filtered respiratory flow Qr.

[0257] 4.4.3.2.4 Determination of Inspiratory Flow Limit 4324

[0258] In one form of this technology, the processor executes one or more algorithms for detecting inspiratory flow limitations.

[0259] In one form, algorithm 4324 receives the respiratory flow signal Qr as input and sets a measure of the degree to which the inspiratory portion of the breath exhibits inspiratory flow restriction as output.

[0260] In one form of this technique, the inspiratory phase of each breath is identified using a zero-crossing detector. An interpolator inserts points (e.g., 65) at uniform intervals representing time points along the inspiratory flow-time curve for each breath. The curve described by the points is then scaled using a scaler to have unit length (duration / cycle) and unit area, thereby removing the effects of variations in respiratory rate and depth. The scaled breath is then compared in a comparator to a pre-stored template representing normal, unobstructed breathing. Similar to... Figure 6The diagram shows the inspiratory phase of a breath. When determined by the test element, breaths that deviate more than a specific threshold (typically 1 scaling unit) at any point during inspiration, such as those caused by coughing, sighing, swallowing, and hiccups, are discarded according to this template. For the data not discarded, for the aforementioned several inspiratory events, the processor 4230 calculates a moving average of the first such scaled point. For the same inspiratory event, the above steps are repeated for the second such point, and so on. Thus, for example, the processor 4230 generates sixty-five scaled data points, and these sixty-five scaled data points represent the moving average of the aforementioned several inspiratory events, such as three inspiratory events. The moving average of the continuously updated values ​​of (e.g., 65) points is referred to below as the "scaled flow," designated as Qs(t). Alternatively, a single inspiratory event can be used without using a moving average.

[0261] Based on the scaling flow rate, two shape factors related to determining partial obstruction can be calculated.

[0262] The shape factor 1 is the ratio of the average of the intermediate (e.g., 32) scaled flow points to the average of the overall (e.g., 65) scaled flow points. A ratio greater than one (unity) indicates normal breathing. A ratio of one or less indicates obstructed breathing. A ratio of approximately 1.17 serves as a threshold between partial obstruction and unobstructed breathing, and corresponds to the degree of obstruction that allows for sufficient oxygenation for a normal user.

[0263] The shape factor 2 is calculated as the RMS deviation per unit scaled flow rate, taking the middle (e.g., 32) points. Approximately 0.2 units of RMS deviation is considered normal. Zero RMS deviation is considered complete flow restriction during breathing. The closer the RMS deviation is to zero, the more flow restriction occurs during breathing.

[0264] Shape factor 1 and shape factor 2 can be used interchangeably or in combination. In other forms of this technique, the number of sampling points, breaths, and intermediate points may differ from those described above. Furthermore, the thresholds may differ from those described.

[0265] The above method is exemplary, and it should be understood that other methods for determining inspiratory flow limits may also be used.

[0266] 4.4.3.2.5 Determination of Apnea and Hypopnea 4325

[0267] In one form of this technology, processor 4230 executes one or more algorithms for determining the presence of apnea and / or hypoventilation.

[0268] Preferably, one or more algorithms receive a respiratory flow signal Qr as input and set a flag indicating that apnea or hypopnea has been detected as output.

[0269] In one form, apnea can be said to have been detected when a function of respiratory flow Qr falls below a flow threshold within a predetermined time period. This function can be determined by peak flow, relatively short-term average flow, or an intermediate flow between relatively short-term average and peak flow, such as RMS flow. The flow threshold can be a flow rate measured over a relatively long period.

[0270] In one form, hypoventilation can be said to be detected when a function of respiratory flow Qr falls below a second flow threshold within a predetermined time period. This function can be determined by peak flow, relatively short-term average flow, or an intermediate flow between relatively short-term average and peak flow, such as RMS flow. The second flow threshold can be a relatively long-term measured flow. The second flow threshold is greater than the flow threshold used to detect apnea.

[0271] The methods described above are exemplary, and it should be understood that other methods may also be used to determine when apnea and / or hypoventilation occurs.

[0272] 4.4.3.2.6 Determining Snoring 4326

[0273] In one form of this technology, processor 4230 executes one or more algorithms for detecting snoring.

[0274] In one form, the snoring algorithm 4326 receives a respiratory flow signal Qr as input and sets a metric value for the degree of snoring as output.

[0275] Preferably, algorithm 4326 includes the step of determining that the intensity of the flow signal is in the range of 30 Hz to 300 Hz. More preferably, algorithm 4326 includes the step of filtering the respiratory flow signal Qr to reduce background noise, such as the sound of airflow from the fan in the system.

[0276] The above methods are exemplary, and it should be understood that other methods can also be used to determine snoring. 4.4.3.2.7 Determination of Airway Patency 4327

[0277] In one form of this technology, processor 4230 executes one or more algorithms for determining airway patency.

[0278] In one form, the airway patency algorithm 4327 receives the respiratory flow signal Qr as input and determines the signal power within a frequency range of approximately 0.75 Hz to approximately 3 Hz. A peak within this frequency range indicates airway opening. The absence of a peak indicates airway closure.

[0279] In one form, the frequency range in which the peak is sought is the frequency of small forced oscillations under therapeutic pressure Pt. In one implementation, the forced oscillation frequency is 2 Hz and the amplitude is approximately 1 cmH2O.

[0280] In one form, the airway patency algorithm 4327 receives the respiratory flow signal Qr as input and determines whether a cardiac signal is present or absent. The absence of a cardiac signal indicates airway closure.

[0281] 4.4.3.2.8 Determination of Treatment Pressure 4328

[0282] In one form of this technology, processor 4230 executes one or more algorithms 4328 for determining the target therapeutic pressure Pt.

[0283] Preferably, algorithm 4328 receives one of the following as input:

[0284] i. Measurement of respiratory phases;

[0285] ii. Waveform;

[0286] iii. Measurement of ventilation rate;

[0287] iv. Measurement of inspiratory flow limit;

[0288] v. Measurement of the presence of apnea and / or hypoventilation.

[0289] vi. The measurement of the presence of snoring; and

[0290] vii. Measurement of airway patency.

[0291] Pi = stage (time), which can be discrete or continuous.

[0292] Phi = Waveform function (Pi), which can include square waves, sine waves, or other waveforms.

[0293] The integral controller amplitude is given by A = G * Int(Vent - Vtgt) dt. Other controller types, such as P, PI, and PID, can also be used.

[0294] Pt(t)=A*Ф(Pi)+P0.

[0295] The P0 = "DC" component can be constant or a function of one or more measurements or indicators of flow restriction, apnea, hypopnea, patency, and snoring.

[0296] (Note: In the basic CPAP model, A can be zero, in which case the total pressure equation is simplified.)

[0297] Algorithm 4328 determines the therapeutic pressure Pt as a function of one or more measurements or indicators of flow restriction, apnea, hypopnea, patency, and snoring. In one implementation, these measurements are determined based on a single breath, rather than on a set of several previous breaths.

[0298] 4.4.3.3 Control Module 4330

[0299] According to one aspect of the present technology, the control module 4330 receives the target therapeutic pressure Pt as input and controls the therapeutic device 4245 to provide this pressure.

[0300] According to one aspect of the technology, the control module 4330 receives EPAP pressure and IPAP pressure as inputs and controls the treatment device 4245 to provide these corresponding pressures.

[0301] 4.4.3.4 Fault Detection 4340

[0302] In one form of this technology, the processor executes one or more methods for detecting fault conditions. Preferably, the fault conditions detected by one or more methods include at least one of the following:

[0303] • Power failure (no power or insufficient power)

[0304] Sensor fault detection

[0305] • The presence of the component cannot be detected.

[0306] • Operating parameters outside the recommended range (e.g., pressure, flow rate, temperature, PaO2)

[0307] • Test alarm malfunctions to generate detectable alarm signals.

[0308] When detecting fault conditions, the corresponding algorithm indicates the presence of a fault by signaling one or more of the following:

[0309] • Activation of audible alarms, visual alarms & / or motion (such as vibration) alarms

[0310] Sending messages to external devices

[0311] • Event log

[0312] 4.4.3.5 Treatment Device 4245

[0313] In a preferred embodiment of this technology, the treatment device 4245 is under the control of the control module 4330 to provide treatment to the patient 1000.

[0314] 4.5 Humidifier 5000

[0315] 4.5.1 Humidifier

[0316] Optionally, in one form of this technology, a humidifier 5000 is provided, comprising a water reservoir 5110 and a heating plate 5120. The water reservoir is configured to contain a supply of liquid, such as water 5140. The heating plate is arranged to heat at least a portion of the supplied liquid 5140 to generate water vapor absorbed by an airflow passing through the humidifier 5000. The humidifier 5000 may include a temperature sensor 5130 for monitoring the temperature of the heating plate and optionally additional sensors 5160 such as a temperature sensor, a relative humidity sensor, and / or an absolute humidity sensor.

[0317] Optionally, a heated air delivery duct 4172 is used to reduce the rain-washing effect on the air delivery duct between the humidifier 5000 and the patient interface 3000. The heated air delivery duct 4172 can be a single-limb or dual-limb line, with one or both limbs being heated. A heating coil 4174 can be disposed within the heated duct 4174 to heat the airflow as it flows through the air delivery duct 4172. Optionally, the air delivery duct 4172 may also include one or more sensors 4176, such as temperature sensors, flow sensors, humidity sensors, or pressure sensors.

[0318] like Figure 5 As shown, a humidifier can be coupled between device 4000 and patient interface 3000. Alternatively, humidifier 5000 can be attached upstream of device 4000 (not shown). Humidifier 5000 can be a component independent of device 4000 and coupled to device 4000 via air delivery duct 4170 or arranged to be directly connected to device 4000. In another arrangement, humidifier 5000 can be integrally constructed with device 4000 (not shown). Humidifier 5000 is configured to humidify the gas before it is delivered to patient 1000.

[0319] The humidifier can use an additional humidification system such as CounterStream as described in U.S. Patent No. 7,975,687. TM Humidification systems, the entire content of which is incorporated into this article by reference.

[0320] 4.6 Power Management

[0321] 4.6.1 Power Use and Charging Layout

[0322] The device or ventilator 4000 described above includes power supply connections configured to connect to several different power sources: AC power line 4432 connected to AC power 4434 via AC power supply unit (PSU) 4430, connected to one or more external batteries 4410, 4420, and DC power line 4462 connected to DC mains power 4460. The system may include one or more of these different power sources simultaneously coupled to the ventilator 4000. The power sources may be coupled in series to the device 4000 via power supply connections. Typically, the device 4000 may be connected to either the AC PSU 4430 or the DC mains power 4460 at any given time. The ventilator or device 4000 may also include an internal battery 4450 located within the device as described above, which can be used as a power source. In use, typically one of the connected power sources can be used at a time to supply power to the device 4000.

[0323] In some arrangements, for ventilation therapy provided by the device, even if another power source is coupled to the ventilator and used as the primary power source, the internal battery 4450 must be present in the device 4000. The device 4000 can be turned on, but treatment cannot begin without the internal battery 4450. An alarm can signal the absence of the internal battery 4450. The requirement for the internal battery 4450 is to ensure that treatment can continue if the primary or external power supply is interrupted for any reason, such as during a power outage. The presence of the internal battery 4450 provides a safe backup for the device 4000.

[0324] The ventilator 4000's controller can detect the connection of different power sources based on the detection of different voltage ranges along the communication signal. The voltage ranges of the different power sources do not overlap. An AC PSU 4430 can provide a first voltage range, such as 1.3 volts to 1.8 volts; a DC mains power supply 4460 can provide a different second voltage range, such as 0.05 volts to 1.2 volts; and an external battery can provide a third voltage range, such as 2.2 volts to 3 volts. These voltage ranges are merely exemplary and it should be understood that other voltage ranges can be used as long as they do not overlap.

[0325] The device includes a power usage priority scheme to ensure that power is used preferentially according to different power supply sources. AC PSU 4430 has the highest power priority, therefore, if AC PSU 4430 is attached, it is always used as the primary power source. Thus, when AC PSU 4430 is coupled between the main AC power supply and device 4000, regardless of any other form of power supply source coupled to device 4000, AC PSU 4430 has power priority to supply power to device 4000. Figure 4jAs shown, if one or more external batteries and internal batteries 4450 are also connected in series, the power supplied by the AC PSU 4430 can also be used to recharge one or more external batteries 4410, 4420 and / or internal batteries 4450 if needed, while also supplying power to operate the ventilator 4000. However, at any given time, the operation of the ventilator 4000 takes precedence over the use of power, and recharging of any battery is reduced when the ventilator 4000 requires more power. In some arrangements, the AC PSU 4430 can supply power to recharge the battery when the output power required by the ventilator is below a threshold. The threshold can be the maximum power or close to the maximum power that the AC PSU 4430 can provide, such as 90 watts. Therefore, a dynamic power management system is used to control the recharging of the battery.

[0326] There can be a priority for the recharging scheme, such that when AC mains power is used for recharging, the internal battery 4450 has the highest priority and is preferably recharged first. When the internal battery 4450 is substantially fully charged, one or more external batteries can be recharged. Recharging of one or more external batteries can also occur in series, with the downstream external battery 4410, i.e., the external battery closest to the ventilator 4000, being recharged before the next external battery in the series. In this arrangement, each external battery is recharged along the series, and the last or upstream external battery 4420 is the last battery to be recharged.

[0327] Figure 4kAn arrangement is shown in which the AC PSU 4430 is not coupled to the device or ventilator 4000 but is used to recharge external batteries 4410, 4420. In this arrangement, the AC PSU 4430 is connected to the main AC power supply 4434 to supply power to charge one or more external batteries; charging of two external batteries—upstream external battery 4420 and downstream external battery 4410—is shown. However, another external battery can be connected in series between the upstream external battery 4420 and the downstream external battery 4410. In this configuration, the downstream external battery 4410 is not connected to the device or ventilator 4000. In some arrangements, according to the present technology, external batteries are recharged in series along the string, for example, when an external battery is connected to or furthest from the AC PSU 4430, the furthest downstream external battery 4410, i.e., the external battery closest to the device 4000, can be recharged first, and then the next external battery in the string can be recharged. The recharging process continues along the string until all external batteries connected in the string have been recharged, with the last or upstream external battery 4420 being the last to be recharged. It should be understood that recharging can be performed in a different order, for example, the upstream external battery 4420 can be recharged first, with the downstream external battery 4410 being the last to be recharged. In another arrangement, all external batteries can be recharged simultaneously.

[0328] See Figure 4m If the DC main power supply 4460 is coupled to the ventilator 4000, the DC main power supply 4460 has power priority in supplying power to the device 4000, regardless of the presence of an internal battery or the presence or absence of one or more external batteries connected in series. In this arrangement, the internal battery 4450 can also be charged via the DC main power supply 4460 if sufficient power is available for recharging and operation of the device 4000. The power requirement for operation of the device 4000 takes precedence over the recharging of the internal battery 4450. In some arrangements, one or more external batteries 4410, 4420 can be recharged without using the DC main power supply 4460, regardless of the available level of DC power, if one or more external batteries 4410, 4420 are present. In other arrangements, external batteries 4410, 4420 can be charged via DC power if sufficient DC power is available. It should be understood that when the ventilator is connected to the DC main power supply 4460, it is not necessary for one or more external batteries 4410, 4420 to be connected to the ventilator. Preferably, when the ventilator is powered by DC mains power 4460, an internal battery 4450 is present within the ventilator 4000 to provide power backup as described above.

[0329] Figure 4lThe arrangement of one or more external batteries used to operate the ventilator or device 4000 is shown. The external batteries can be connected to the ventilator using cables such as DC power line 4462, and each external battery is connected to an adjacent external battery using a cable such as DC power line. Each external battery may include input and output ports configured to receive cables between adjacent external batteries. The external battery closest to device 4000 (e.g., downstream external battery 4410) is connected to the power source connection of device 4000 via cable such as DC power line 4462. If more than one external battery is connected in series to the ventilator 4000, external battery power usage priority is used to determine which external battery supplies power from. The external battery used to supply power to the ventilator in use can be considered as the power supply external battery.

[0330] In one arrangement, the external battery located furthest from the ventilator 4000 in the string, such as... Figure 4l The power from the upstream external battery 4420 shown is initially used to operate the ventilator 4000 and is the initial power supply to the external battery. When the power from the upstream external battery 4420 is substantially depleted, power is then used from the next external battery in the series, and this external battery is, for example... Figure 4l The downstream external battery 4410 will become the power supply for the external battery to operate the ventilator 4000. If more than two external batteries are connected in series to the ventilator 4000, power from each external battery is used continuously along the string from the furthest or upstream external battery to the nearest or downstream external battery. When all power from all external batteries is substantially depleted, power from the internal battery 4450 is then used to operate the ventilator 4000. In this arrangement, the power in the internal battery 4450 is the last power used, so that a safe backup of power can be provided, especially when connected to the AC mains power 4434 or DC mains power 4460, in case of any power problems.

[0331] In another arrangement, the power usage priority of the external battery can be to first use the power from the external battery closest to the ventilator 4000, i.e., the downstream external battery 4410, then use the power from the next adjacent external battery in the string, and then continue along the string such that the power from the external battery furthest from the ventilator 4000, i.e., the upstream battery 4420, is used last.

[0332] In a preferred aspect of this technology, power usage and recharging are configured such that the internal battery 4450 is the last battery used and the first battery to be recharged.

[0333] 4.6.2 Communication

[0334] In this aspect of the technology, the device or ventilator 4000 is configured to provide an estimate of the available state of charge or total remaining capacity from all coupled battery power sources, namely the internal battery 4450 and / or one or more external batteries 4410, 4420. The device 4000 can set the estimate of the total available capacity as an estimate of the total remaining operating time based on the current power usage of the ventilator.

[0335] Each external battery has an input port and an output port to transmit communication signals or information along the chain to the controller of the ventilator 4000 and to transmit communication signals or information from the controller of the ventilator 4000. Communication signals are transmitted along the chain from the upstream external battery 4410 to the downstream external battery 4410 and back to the ventilator 4000, and in the opposite direction along the chain from the ventilator 4000 to the upstream external battery 4420. If an internal battery 4450 is present, the communication signals can also be configured to communicate through the internal battery 4450; alternatively, the internal battery 4450 can communicate independently with the ventilator controller.

[0336] The batteries currently in use, which power the device, are configured to determine the total remaining available operating time (hours) as a function of the current utilization rate of the ventilator (mA / hour) and the current charge level of the battery (mA). Other batteries, such as external batteries and / or internal batteries, can also determine their own remaining capacity and send this information to the batteries currently powering the system. The batteries currently powering the system are used to determine the current power utilization rate. It should be understood that time and rate can be set in different time units, such as minutes or seconds instead of hours, or in combinations of hours, minutes, and / or seconds.

[0337] For example, when the system from such Figure 4lWhen the upstream external battery 4420 is running, the controller 4230 of the ventilator 4000 can send a remaining runtime request to the upstream external battery 4420. The controller 4230 can also send a battery capacity information request to the internal battery 4450, which is the downstream battery coupled to the ventilator. The internal battery 4450 can then send a request to the downstream external battery 4410, i.e., the external battery closest to the ventilator 4000. The downstream external battery 4410 can then send a battery capacity information request to its adjacent external battery, and continue sending battery capacity information requests along the string of external batteries to the upstream external battery 4420, which is currently supplying power or capable of supplying power. The upstream external battery 4420 provides remaining capacity (RC) information and remaining runtime (RRT) information based on the current power utilization of the ventilator from this upstream external battery 4420. The remaining capacity (RC) information and remaining runtime (RRT) information are then transmitted back to the downstream external battery 4410 along the string. If there are any other external batteries between the upstream external battery 4420 and the downstream external battery 4410 ( Figure 4l (not shown in the image), then the downstream external battery 4410 can also request any other external battery from the upstream external battery 4420 connected in the string between the downstream external battery 4410 and the upstream external battery 4420. Figure 4l The remaining capacity (RC) information (not shown) is used to provide the total remaining capacity of the external battery. In one arrangement, the downstream external battery 4410 can then send information to the internal battery 4450, which also provides information about its own remaining capacity. The internal battery 4450 can determine an estimate of the total remaining runtime (TRRT) or send information to the controller 4230 to determine an estimate of the total remaining runtime (TRRT). In this arrangement, the internal battery 4450 or the controller 4230 estimates the total remaining runtime (TRRT) using the following formula:

[0338]

[0339] There are n batteries in this string, and battery n is, for example, the upstream battery that can supply power to make the ventilator 4000 run when powered by AC or DC power (e.g., Figures 4j to 4m The upstream external battery 4420 in the string, or the battery used to supply power to run the ventilator 4000, TRRT is the total remaining running time of all n batteries in the string, and Bat(n)_RC is the upstream battery with available power (e.g., the battery with the most available power). Figure 4m The remaining capacity of the upstream external battery (4450) in the middle, Bat(n-1)_RC is the battery adjacent to the upstream battery (e.g., Figure 4m The remaining capacity of the downstream external battery 4410, Bat(1)_RC is the most downstream battery (e.g., Figure 4m The remaining capacity of the internal battery (4450) and BatnRRT are the remaining operating time of battery n in hours (and / or minutes and / or seconds). It should be understood that if there are batteries between the downstream external battery n and the upstream external battery, the calculation also includes the remaining capacity of each additional external battery.

[0340] The remaining capacity in the above calculation [1] is preferably the remaining capacity in milliamperes per hour or other absolute units of the actual battery, rather than a percentage of the state of charge. This is because the percentage of the state of charge can vary between batteries and exceeds the battery's lifespan, so that using the percentage of the state of charge (SOC) would introduce errors. For example, 100% SOC of a battery can differ from the actual amount in mAhrs, because %SOC is related to the maximum currently available capacity in the peak that decreases with charge-discharge cycles, for example, the total capacity after 400 cycles may be only 80% of the new package capacity.

[0341] In another arrangement, the internal battery 4450 and the external batteries 4410, 4420 are not directly connected to each other. The ventilator controller sends a signal to the downstream external battery 4410 to request the remaining capacity and / or remaining runtime of a series of external batteries. The determination of the total remaining runtime of the external batteries is independent of the calculation of the total remaining runtime of the internal battery 4450. In this arrangement, the downstream external battery 4410 may perform the above calculation [1] based on the remaining capacity information received from all upstream external batteries in the string to determine the total remaining runtime of all external batteries. In addition, the upstream external battery 4420 may perform the calculation of the total remaining runtime of the external batteries based on the capacity information received from all downstream external batteries in the string [1].

[0342] If the upstream external battery n has been fully discharged to supply power to the next downstream external battery n-1 in the string, then no charging signal is sent from the upstream external battery n to the downstream external battery 4410. In this case, the next external battery n-1 in the string becomes battery n, so battery n and other external batteries downstream of this external battery can only be used in the calculation of the total remaining running time if the remaining charge from the external battery is currently supplying power or is able to supply power.

[0343] The ventilator controller can send independent request signals to the internal battery 4450 regarding its remaining capacity and / or remaining operating time. The internal battery 4450 can be configured to determine its remaining capacity and send this information to the controller.

[0344] In some configurations, the ventilator 4000 controller can be configured to receive information on the total remaining operating time from all battery sources, namely the internal battery as described above and all external batteries.

[0345] In other arrangements, the controller may be configured to receive remaining capacity information from the internal battery 4450 and a series of external batteries 4410, 4420 and perform the calculations described above [1] to determine the total remaining battery runtime. The ventilator controller 4230 may be configured to display an estimate of the total remaining runtime of all battery sources in hours and / or minutes and / or seconds on the ventilator's display 4294 or user interface. The ventilator 4000 may be configured to display the total remaining runtime of each battery source or all external and internal batteries in hours and / or minutes and / or seconds on the display 4292.

[0346] In another aspect of this technology, the ventilator controller can request an estimate of the total remaining capacity from the coupled batteries, whether from external and internal batteries together or individually from external and internal batteries. The ventilator can display the total remaining capacity of the battery source, the external battery, and / or the internal battery in milliamperes per hour (mAh) and / or as a percentage of remaining power, based on the total level that the battery source can provide.

[0347] In one form of this technology, the voltage supply is divided into a first voltage rail and a second voltage rail, provided according to a main voltage rail, such as a 30V rail. The first voltage rail can be configured to supply power to the core ventilation system, i.e., to enable the necessary basic logic circuitry to operate the device 4000. The second voltage rail can be configured to supply power to peripheral lines. Peripheral lines may include power to operate user interfaces such as LCDs or touchscreens, data input / output devices such as USB or Ethernet, or remote interfaces. In this arrangement, failure or shutdown of peripheral lines is unlikely to affect the core ventilation system, thus allowing the core ventilation to continue operating. In one example, the first and second voltage rails may be 5V rails. Alternatively, the first and second voltage rails may provide different voltage supply levels.

[0348] 4.6.3 Power Efficiency

[0349] In another aspect of this technology, the device or ventilator 4000 may include an energy regeneration system coupled to the main fan 4104. In this arrangement, see [reference needed]. Figure 4nWhen the main fan decelerates, such as when cycling from the inspiratory set pressure to the expiratory set pressure, the energy stored in the fan's inertia can be stored in the energy storage unit 4510. The energy storage unit 4510 may include at least one capacitor, a set of capacitors, a supercapacitor, or a battery. The energy storage unit 4510 is positioned in parallel with the input power supply 4210. Energy is regenerated or stored in the energy storage unit 4510 to enable the device or components of the device 4000 to operate for a short period of time during each breathing cycle until the energy in the energy storage unit decays to a set point. For example, the short period of time may be approximately 200 to 500 milliseconds (ms), such as 300 ms. However, the duration depends on the energy recovered from the main fan inertia and system operating current, i.e., the device's setting at the energy regeneration time. An optional diode 4520, indicated by a dashed line, is positioned between the energy storage unit 4510 and the input power supply 4210 depending on whether the input power supply 4210 can tolerate voltage drift from the energy storage unit 4510. In this arrangement, the energy storage unit 4510 is used only to supply power to the main wind turbine and to supply power to the control system 4230.

[0350] In one aspect of this technology, when the energy storage unit 4510 supplies power for operating the ventilator 4000, the regulator switch shuts off power from the input power supply 4210. Shutting off the input power supply increases the system's power efficiency when the device is operated by the energy storage unit.

[0351] like Figure 4o As shown, the boost regulator 4530 is powered by an input power supply, which may include an external input supply 4540 and / or an internal battery 4450. A switch controls whether the power is supplied by the external input supply 4540 or the internal battery 4450. The external input supply 4540 may include any one of AC mains power 4434, DC mains power 4460, or external batteries 4420 and 4410. When the external input supply drops below a first predetermined voltage, for example, about 10.5V, this switching control is performed by the internal circuitry of the battery charger, and the system switches to the internal battery 4450. When the external input supply 4540 recovers and the voltage reaches above the first predetermined voltage or reaches a second predetermined voltage, for example, about 11V, the system switches back to the external input supply 4540.

[0352] During motor deceleration, the motor driver 4105 uses software control to maintain motor commutation but continues to drive the main fan 4104 at low drive levels, such as 10% drive level. As the main fan 4104 decelerates, the energy stored in the inertia and angular momentum of the main fan is converted into a small amount of heat energy in the fan and motor control FETs and stored in the energy storage unit 4510, for example, in 2 x 2700 μF motor capacitors. Therefore, the motor capacitor voltage increases from a first predetermined voltage limit, for example, 30V, to a maximum voltage, for example, 45V. When the output of the boost regulator exceeds a second predetermined voltage limit, for example, 31V, the overvoltage protection circuit of the boost regulator 4530 is activated, shutting down the boost regulator 4530, which in turn shuts down the input power supply 4540, 4450. The system then operates on the energy stored in the energy storage unit 4510, for example, the motor capacitors, until the voltage drops below the first predetermined voltage limit and the boost regulator 4530 is restarted.

[0353] Advantageously, the energy recovered by the inertia of the fan is not immediately converted into heat, thus requiring less heat dissipation. Furthermore, energy recovery refers to the loss incurred when the boost regulator is shut down during a period of system operation by the energy storage unit. Therefore, the heat generated from the boost regulator is reduced under high-drive conditions. Thus, in this aspect of the technology, the heat generated during the main fan deceleration period can be reduced due to the energy stored in the energy storage unit 4510.

[0354] If an internal battery 4450 and external batteries 4410, 4420 are present and used as the power source of the present invention, the increased power efficiency obtained during deceleration by recovering the main fan energy and shutting off the power input supply 4210 improves the efficiency of the internal battery 4450 and external batteries 4410, 4420.

[0355] 4.7 Alarm System

[0356] The device or ventilator 4000 may include an alarm system that provides visual and / or audio signals to warn of situations requiring attention. The ventilator 4000 may include an output device 4290 that provides warning indication of alarm conditions in the form of one or more audible alarms such as buzzers 4296 and / or one or more visual alarms such as one or more LEDs 4298. If multiple buzzers 4296 are present, each buzzer 4296 may produce a different warning sound or a different volume to indicate different types of alarm conditions. If multiple LEDs 4298 are present, each LED 4298 may have a different color or brightness level to indicate different types of alarm conditions.

[0357] Alarm conditions can include various situations affecting the device or treatment, and may include power supply problems (e.g., no internal battery attached, external power supply loss, low battery power, battery failure, etc.), pressure supply problems (e.g., high pressure, high expiratory pressure, low PEEP, high PEEP, low peak inspiratory pressure, etc.), ventilation parameter problems (e.g., high or low tidal volume during expiration or inspiration, low or high minute ventilation during expiration or inspiration, low or high respiratory rate, occurrence of apnea, etc.), blood oxygen saturation problems (e.g., low or high SpO2 levels, low or high pulse rate, etc.), oxygen supply problems (only provided when an oxygen sensor is connected and low or high FiO2 can be monitored), breathing circuit problems (e.g., high leakage, incorrect wiring, disconnected pressure lines, etc.), and system malfunctions including fan failure, sensor failure, battery connectivity failure, software failure, operating condition failure, etc.

[0358] Visual alarms may include illumination or flashing from the alarm strip 4026 on the ventilator 4000 and / or sound from an audio alarm in the ventilator 4000. Alarm messages may be displayed on a user interface. Alarm priorities may be present, such as high-level, medium-level, and low-level alarms, and the alarm intensity may be varied for different priorities. For example, a high-level alarm may have a red flashing light on the alarm strip 4026 and a first predetermined amount of beeping sound from the audio alarm at a first predetermined frequency. A medium-level alarm may have a yellow flashing light on the alarm strip 4026 and a second predetermined amount of beeping sound from the audio alarm at a second predetermined frequency. A low-level alarm may have a fixed light on the alarm strip 4026 and a third predetermined amount of beeping sound from the audio alarm at a third predetermined frequency. The first predetermined amount of beeping sound may be higher than the second predetermined amount of beeping sound, and the second predetermined amount of beeping sound may be higher than the third predetermined amount of beeping sound. Additionally, the first predetermined frequency may be lower than the second predetermined frequency, and the second predetermined frequency may be lower than the third predetermined frequency. However, it should be understood that other alarm priority arrangements may also be used.

[0359] The volume of the audio alarm can be adjusted using the control settings available via the user interface on the device. By pressing the mute button on the user interface, the audio alarm can be temporarily muted for a predetermined time, such as 1 minute, 2 minutes, 3 minutes, 4 minutes, or 5 minutes. If the alarm persists after the predetermined muting time, the audio alarm will sound again.

[0360] Users can manually reset certain types of alarms, such as low-level alarms and non-life-threatening alarms, and disable visual and / or audio alarms. Other alarms cannot be reset unless the alarm condition is corrected. Emergency alarms can be automatically reset via the ventilator when the alarm condition is corrected, or can only be reset via the ventilator after the alarm-causing condition has been corrected.

[0361] In one aspect, the system can be configured to attach a remote alarm 4660, allowing the alarm to be placed in another location of the ventilator 4000, such as another room. The remote alarm 4660 is configured to alert a caregiver of an alarm event. The remote alarm may be battery-powered and connected to the device 4000 via a cable. Optionally, a second remote alarm may be connected to the first remote alarm, allowing the remote alarms to be placed in two different locations.

[0362] In one aspect, the system can be configured to attach a remote controller 4650 that allows a user to operate an alarm as a warning to a nurse or caregiver by pressing a button located on the remote controller 4650. The remote controller can be coupled to the device 4000 via a cable.

[0363] In one aspect of this technology, the alarm system includes a hardware alarm controller (HAC) 4610. The HAC 4610 drives an alarm buzzer 4292 and / or an LED 4294 to provide predetermined alarm modes for different alarm priorities as described above. Figure 4p A schematic diagram of the HAC control system is shown. The HAC monitors the mainboard processor 4620 and the pneumatic block processor 4630. Although Figure 4p The motherboard processor and pneumatic block processor 4630 shown are two different blocks; however, it should be understood that the motherboard processor and pneumatic block processor can exist on a single PCB or on separate PCBs. The pneumatic block processor 4630 and the motherboard processor 4620 can communicate with each other to enable the correct operation of the device and treatment.

[0364] The pneumatic block processor 4630 may also include a pneumatic block safety line 4632, which monitors for hardware errors such as pressure errors, current errors, or temperature errors, as well as software errors, in the ventilator delivery system.

[0365] The alarm monitoring system monitors the mainboard processor 4620 and the pneumatic block processor 4630, and sends rule signals (2), (5), 4622, and 4634 to the HAC to notify the mainboard processor 4620 and the pneumatic block processor 4630 that they are working properly. The pneumatic block safety line 4632 can generate the pneumatic block monitoring signal 4634. If the HAC 4610 does not receive any monitoring signal 4622 or 4634 in time, the HAC triggers an alarm and sends a safety assertion status signal (6) to the pneumatic block processor 4630. The safety assertion status signal (6) puts the system in a safe state. The safe state may include shutting down the main fan 4104 and the PEEP fan 4124, shutting down the oxygen valve drive 4640 if it is present, disabling the PEEP solenoid valve 4136 and activating (enabling) the check valve 4114 and the safety valve 4085 (see Figure 4f ).

[0366] HAC 4610 can also monitor the power supply of the ventilator 4000 via signal 4670 such as VCORE_Good signal, and issue an alarm if a power failure occurs during the operation of the ventilator 4000.

[0367] The HAC can be coupled to an HAC supercapacitor (not shown), which is powered by a charger operated by a first voltage rail configured as described above to operate the core ventilation system. Therefore, the HAC and HAC supercapacitor are considered part of the core ventilation system, i.e., the basic logic circuitry required to operate device 4000. When the system is powered, the HAC supercapacitor can remain fully charged. If a power failure occurs and a total power failure alarm is generated, the HAC supercapacitor is configured to power one or more of the alarms 4290. Preferably, the total power failure alarm is an audible alarm, and the HAC supercapacitor is configured to power one or more of the buzzers 4292. Optionally, the visual alarm is not activated by the HAC supercapacitor to extend the total power failure operation time of the audible alarm.

[0368] Because the motherboard processor 4620 software can be responsible for starting and stopping the alarm based on predefined alarm algorithms designed for each type of alarm situation, the HAC 4610 communicates bidirectionally with the motherboard processor 4620. The motherboard processor 4620 can then signal the HAC 4610 to activate the buzzer 4292 and / or LED 4294. Each alarm algorithm includes input settings such as thresholds or parameters that meet the conditions for activating the alarm. Alarm activation parameters can originate from the pneumatic block processor 4630 or the motherboard processor 4620. In some arrangements, the ventilator 4000 may include an audio pause button 4610 that silences some alarms by pressing an audio pause button 4670, depending on the alarm's priority and type. When the audio pause button 4610 is pressed, a signal is sent to the HAC 4610 to turn off the output devices 4290, namely the buzzer 4292 and / or LED 4294. A signal is also sent to the motherboard processor 4620 to suggest pausing the alarm and to start a timer for pausing the alarm. The alarm will restart after the scheduled time has elapsed and the alarm condition has not been resolved. An audio pause LED may be present and activated when the alarm is paused.

[0369] The remote alarm 4650 communicates with the motherboard processor 4620 to signal the activation of the alarm, i.e., the caregiver alarm. Then, if an alarm report needs to be generated, the motherboard processor 4620 can signal the HAC 4610 to activate the buzzer 4292 and / or the LED.

[0370] The remote alarm 4660 is connected to the HAC 4610 so that any alarms generated by the HAC 4610 are sent to the remote alarm 4660.

[0371] 4.8 Vocabulary

[0372] For the purposes of this technical disclosure, one or more of the following limitations may be applied in certain forms of this technology. Other limitations may be applied in other forms of this technology.

[0373] 4.8.1 General Principles

[0374] Air: In some forms of this technology, the air supplied to the patient may be atmospheric air, and in other forms of this technology, the atmospheric air may be supplemented with oxygen.

[0375] Continuous Positive Airway Pressure (CPAP): CPAP therapy is understood as the application of supplying air or breathable gas at a continuous positive pressure relative to the atmosphere to the inlet of the airway, preferably, substantially constant through the patient's respiratory cycles. In some forms, the pressure at the airway inlet will vary by a few centimeters of water within a single respiratory cycle, for example, higher during inhalation and lower during exhalation. In some forms, the pressure at the airway inlet is slightly higher during exhalation and slightly lower during inhalation. In some forms, the pressure varies between different respiratory cycles of the patient, for example, the pressure increases in response to a detection indicating local upper airway obstruction, and decreases in the absence of such an indication.

[0376] 4.8.2 Apparatus Aspects

[0377] Air line: A conduit or tube constructed and arranged to deliver a supply of air or breathable gas between the device and the patient interface. Specifically, the air line may be fluidly connected to the outlet of the pneumatic block and the patient interface. The air line may be referred to as an air delivery tube. In some cases, separate limbs may be present for inhalation and exhalation. In other cases, a single-limb line is used.

[0378] Fan or airflow generator: A device that delivers airflow at a pressure higher than ambient pressure.

[0379] Controller: A device or part of a device that adjusts its output based on inputs. For example, one type of controller has a variable under control that constitutes a control variable input to the device. The output of the device is a function of the current value of the control variable and the setpoint of the variable. A servo ventilator may include a controller having a ventilation volume as input, a target ventilation volume as a setpoint, and a pressure support level as an output. Other forms of input may be one or more of oxygen saturation (SaO2), partial pressure of carbon dioxide (PCO2), movement, a signal from an electrovascular volume graph, and peak flow. The setpoint of the controller may be one or more of a fixed setpoint, a variable setpoint, or a known setpoint. For example, the setpoint in a ventilator may be a long-term average of the measured ventilation volume of a patient. Another ventilator may have a ventilation setpoint that varies over time. A pressure controller may be configured to control a fan or pump to deliver air at a specific pressure.

[0380] Treatment methods: In the context of this article, treatment methods may be one or more of the following: positive pressure therapy, oxygen therapy, carbon dioxide therapy, dead space control, and medication administration.

[0381] Electric motor: A device for converting electrical energy into rotational motion of a component. In the context of this article, the rotating component is an impeller that rotates in place about a fixed axis to impart an increase in pressure to the air moving along the axis of rotation.

[0382] Positive airway pressure (PAP) device: A device used to provide air to the airway at positive pressure.

[0383] Sensor: A device used to convert one form of energy or signal into another form of energy or signal. A sensor can be a sensor or detector used to convert mechanical energy (such as motion) into an electrical signal. Examples of sensors include pressure sensors, flow sensors, carbon dioxide (CO2) sensors, oxygen (O2) sensors, force sensors, motion sensors, noise sensors, volumetric chromatographs, and cameras, etc.

[0384] Volute: The casing of a centrifugal pump that receives air pumped by the impeller, slows down the airflow velocity, and increases the pressure. The cross-section of the volute increases in the region facing the discharge port.

[0385] 4.8.3 Respiratory and Circulatory Aspects

[0386] Apnea: Preferably, apnea is defined as the flow rate falling below a predetermined threshold for a period of time, such as 10 seconds. Obstructive apnea is defined as the obstruction of the airway preventing airflow, regardless of the patient's effort. Central apnea is defined as the detection of apnea due to reduced or absent respiratory effort.

[0387] Respiratory rate: The rate at which a patient breathes spontaneously, usually measured in breaths per minute.

[0388] Duty cycle: The ratio of inhalation time Ti to total expiratory time Ttot.

[0389] Effort (breathing): Preferably, breathing effort can be described as the work done by a person who is breathing voluntarily in an attempt to breathe.

[0390] The expiratory phase of the respiratory cycle: the period from the start of expiratory flow to the start of inspiratory flow.

[0391] Flow restriction: Preferably, flow restriction is considered as a state in which an increase in the patient's effort during breathing does not result in a corresponding increase in flow rate. Flow restriction occurring during the inspiratory portion of the respiratory cycle can be described as inspiratory flow restriction. Flow restriction occurring during the expiratory portion of the respiratory cycle can be described as expiratory flow restriction.

[0392] Types of flow-limiting inhalation waveforms:

[0393] (i) Flat: There is a rise followed by a relatively flat section, and then a fall.

[0394] (ii) M-type: has two local peaks, one at the leading edge and one at the trailing edge, and a relatively flat portion between the two peaks.

[0395] (iii) Chair type: has a single local peak at the leading edge, followed by a relatively flat section.

[0396] (iv) Inverted chair type: has a relatively flat section followed by a single local peak at the trailing edge.

[0397] Hypoventilation: Preferably, hypoventilation is considered as a reduction in flow rate but not an interruption of flow rate. In one form, hypoventilation is said to occur when the flow rate decreases below a threshold over a period of time. In one form in adults, any of the following can be considered hypoventilation:

[0398] (i) Within at least 10 seconds, the patient's breathing decreases by 30% plus an associated 4% desaturation; or

[0399] (ii) Within at least 10 seconds, the patient’s breathing decreases (but less than 50%), and there is an associated desaturation or arousal of at least 3%.

[0400] The inspiratory portion of the respiratory cycle: Preferably, the period from the start of inspiratory flow to the start of expiratory flow is considered the inspiratory portion of the respiratory cycle.

[0401] Open (airway): The degree to which the airway is open, or to what extent the airway is open. Patented airways are open. Airway openness can be quantified, for example, by using a patented value of -(1), and a value of zero (0) indicates an airway closure.

[0402] Positive end-expiratory pressure (PEEP): The pressure above atmospheric pressure present in the lungs at the end of expiration.

[0403] Peak flow (Q) 峰值 ): The maximum flow rate during the inspiratory portion of the respiratory flow waveform.

[0404] Respiratory flow, airflow, patient airflow, respiratory flow (Qr): These synonyms can be understood as referring to the device’s estimated respiratory flow rather than the “true respiratory flow” or “true respiratory flow,” which is the patient’s actual respiratory flow, usually expressed in liters per minute.

[0405] Tidal volume (Vt): The amount of air inhaled or exhaled during normal breathing without additional effort.

[0406] (Inhalation) Time (Ti): The duration of the inspiratory portion of the respiratory flow waveform.

[0407] (Exhalation) Time (Te): The duration of the expiratory portion of the respiratory flow waveform.

[0408] (Total) Time (Ttot): The total duration between the start of the inspiratory portion of one respiratory flow waveform and the start of the inspiratory portion of the next respiratory flow waveform.

[0409] Typical recent ventilation: The value of ventilation that tends to cluster around the most recent values ​​over a predetermined time scale; that is, a measure of the central tendency of recent values ​​of ventilation.

[0410] Upper airway obstruction (UAO): This includes both partial and complete upper airway obstruction. This can be associated with a state of flow restriction, where the flow level increases only slightly or even decreases due to the increased pressure differential across the upper airway (Starling resistance behavior).

[0411] Ventilation: A measure of the total amount of gas exchanged through a patient's respiratory system per unit time, including both inspiratory and expiratory flow rates. When expressed as volume per minute, this amount is often referred to as "minute ventilation." Minute ventilation is sometimes simply given as volume and is understood as volume per minute.

[0412] 4.8.4 Device Parameters

[0413] Flow rate: The instantaneous volume (or mass) of air delivered per unit time. Flow rate is measured over a shorter period when flow rate and ventilation volume have the same volume or mass dimension per unit time. Flow rate for the inspiratory portion of a patient's respiratory cycle can be nominally positive, and therefore negative for the expiratory portion. In some cases, the flow rate mentioned is a reference scalar, i.e., a quantity with only amplitude. In other cases, the flow rate mentioned is a reference vector, i.e., a quantity with both amplitude and direction. Flow rate is denoted by the symbol Q. Total flow rate Qt is the flow rate of air leaving the device. Tidal volume Qv is the flow rate of air leaving the vent that allows exhaled gas to be flushed. Leakage flow rate Ql is the flow rate of air unintentionally leaking from the patient interface system. Respiratory flow rate Qr is the flow rate of air received into the patient's respiratory system.

[0414] Leakage: Preferably, the term leakage is considered as the flow of air leaking into the environment. Leakage can be intentional, for example, allowing exhaled carbon dioxide to be flushed away. Leakage can be unintentional, for example, due to an incomplete seal between the mask and the patient's face.

[0415] Pressure: Force per unit area. This can be expressed in quantities including cmH₂O and gf / cm².2 Pressure is measured in hectopascals (HPa). 1 cmH₂O equals 1 g⁻¹ / cm³. 2 And it is approximately 0.98 hPa. In this instruction manual, unless otherwise stated, the unit of pressure is cmH2O. For nasal CPAP treatment of OSA, the treatment pressure mentioned refers to a pressure within the range of approximately 4 cmH2O to 20 cmH2O or approximately 4 cmH2O to 30 cmH2O. The pressure at the patient interface is indicated by the symbol Pm.

[0416] Sound power: The energy emitted per unit time by a sound wave. Sound power is proportional to the product of the square of the sound pressure and the area of ​​the wavefront. Sound power is usually expressed in decibels (SWL), i.e., decibels relative to a reference power, and is generally considered to be 10. -12 watt.

[0417] Sound pressure level: The local deviation from ambient pressure at a given point in time due to the travel of sound waves through a medium. Sound power is usually expressed in decibels (SWL), i.e., relative reference power in decibels, and is generally considered to be 20 × 10⁻⁶. -6 Pascal (Pa) is the threshold of human hearing.

[0418] 4.8.5 Ventilator Terminology

[0419] Adaptive servo ventilator: A ventilator with a variable target ventilation volume rather than a fixed target ventilation volume. The variable target ventilation volume can be determined from some characteristics of the patient, such as the patient's respiratory characteristics.

[0420] Backup rate: The ventilator parameter that establishes the minimum respiratory rate (usually breaths per minute) delivered to the patient by the ventilator unless otherwise triggered.

[0421] Cycle: The end of the inspiratory phase of a ventilator cycle, and can also be referred to as the expiratory trigger to indicate the start of expiration. When a ventilator is delivering breaths to a spontaneously breathing patient, at the end of the inspiratory portion of the respiratory cycle, the ventilator is considered to have cycled to stop delivering breaths.

[0422] EPAP (or EEP): Positive Expiratory Airway Pressure (EPAP) is the pressure or baseline pressure delivered to the patient during expiration, where changes in intra-breath pressure are added to the positive expiratory airway pressure to produce the mask pressure that the ventilator attempts to achieve during expiration.

[0423] IPAP: The required mask pressure that the ventilator attempts to achieve during the inspiratory phase of breathing.

[0424] Pressure support: Indicates the increase in pressure during inspiration by the ventilator compared to the pressure during expiration, and is typically the pressure difference between the maximum value during inspiration and the minimum value during expiration (e.g., PS = IPAP - EPAP). In some cases, pressure support refers to the difference the ventilator intends to achieve rather than the difference it actually achieves.

[0425] Servo ventilator: A ventilator that measures the patient's ventilation with a target ventilation volume and adjusts the level of pressure support to direct the patient's ventilation volume toward the target ventilation volume.

[0426] Spontaneous / Timed (S / T) – A mode of operation for a ventilator or other device that attempts to detect spontaneous breathing in a patient. However, if the device fails to detect breathing within a predetermined period, it will automatically begin delivering breaths.

[0427] Swing: An equivalent term for pressure support.

[0428] Triggering: When a ventilator delivers breathing air to a spontaneously breathing patient, doing so at the beginning of the inspiratory phase of the respiratory cycle through the patient's effort can be considered as being triggered.

[0429] Ventilator: A mechanical device that provides pressure support to a patient to perform some or all of the functions of breathing.

[0430] 4.8.6 Anatomy of the Respiratory System

[0431] Diaphragm: A muscular plate that extends through the bottom of the thoracic cavity. The diaphragm separates the thoracic cavity from the abdominal cavity and contains the heart, lungs, and ribs. As the diaphragm contracts, the volume of the thoracic cavity increases, and air is drawn into the lungs.

[0432] Larynx: The larynx or larynx that houses the vocal cords and connects the lower part of the pharynx (laryngopharynx) to the trachea.

[0433] Lungs: The organs of respiration in the human body. The conduction area of ​​the lungs includes the trachea, bronchi, bronchioles, and terminal bronchioles. The respiratory area includes the respiratory bronchioles, alveolar ducts, and alveoli.

[0434] Nasal cavity: The nasal cavity (or nasal groove) is a large air-filled area located in the middle of the face, behind and above the nose. The nasal cavity is divided into two parts by a vertical fin called the nasal septum. On the sides of the nasal cavity are three horizontal growths called nasal conchae (singular "turbinate bones") or nasal conchae. The nose is located at the front of the nasal cavity, while the back connects to the nasopharynx via the posterior nasal aperture.

[0435] Pharynx: The pharynx is located just below the nasal cavity and above the esophagus and part of the larynx. The pharynx is generally divided into three parts: the nasopharynx (superior pharynx) (the nasal part of the pharynx), the oropharynx (middle pharynx) (the oral part of the pharynx), and the larynx (inferior pharynx).

[0436] 4.8.7 Patient Interface Aspects

[0437] Anti-asphyxiation valve (AAV): A component or sub-assembly of a mask system that reduces the risk of a patient rebreathing excessive CO2 by opening to the atmosphere in a fail-safe manner.

[0438] Headgear: A headgear is understood to refer to a form of positioning and stabilizing structure designed for use with the head. Preferably, a headgear comprises one or more supports, straps, and reinforcements configured for use in respiratory therapy delivery, positioning the patient interface and holding it in proper position on the patient's face. Some of the straps are formed from layers of soft, flexible, elastic materials such as foam and fabric.

[0439] Pressure chamber: A mask pressure chamber is understood as a device portion of a patient interface having a walled enclosure containing air pressurized above atmospheric pressure during use. A shell may form part of the wall of the mask pressure chamber. In one form, the patient's facial area forms a wall of the pressure chamber.

[0440] Sealing: The noun form ("seal") is understood as a structural element or barrier intentionally preventing airflow through the surfaces of two interfaces. The verb form ("seal") is understood as preventing airflow.

[0441] Rotary ring: (noun) a sub-assembly configured to rotate about a common axis, preferably an independently rotating sub-assembly, and preferably a sub-assembly rotating under low torque. In one form, the rotary ring may be configured to rotate through an angle of at least 360 degrees. In another form, the rotary ring may be configured to rotate through an angle of less than 360 degrees. When used in the air delivery duct described herein, the sub-assembly of the component preferably comprises a pair of mating cylindrical ducts. Preferably, little or no airflow leakage from the rotary ring occurs during use.

[0442] Vent: (noun) A structure that allows air to leak intentionally from the inside of a mask or duct into the ambient air at a controlled rate so as to flush out exhaled carbon dioxide (CO2) and supply oxygen (O2).

[0443] 4.9 Other Notes

[0444] This patent document contains a portion of copyrighted material. Because this material appears in patent documents or records of the Patent and Trademark Office, the copyright holder does not object to anyone copying it through the patent document or the patent disclosure, but otherwise reserves all copyright rights.

[0445] Unless the context explicitly states otherwise and a numerical range is specified therein, it should be understood that every intermediate value up to one-tenth of the lower limit, every intermediate value between the upper and lower limits of the range, and any other specified or intermediate value within the specified range are included in this technology. The upper and lower limits of these intermediate ranges, which may be individually included within the intermediate range, are also included in this technology, subject to any specifically excluded limit values ​​within the specified range. When a specified range includes one or both limit values, the range excluding one or both of the included limit values ​​is also included in this technology.

[0446] Furthermore, when one or more values ​​specified herein are used as part of the implementation of this technology, it should be understood that, unless otherwise stated, such values ​​may be approximations and may be used for any suitable valid bit within the range that the actual technical implementation may allow or require.

[0447] Unless otherwise specified, all technical and scientific terms used herein have the same meaning as commonly understood by one of ordinary skill in the art. While any methods and materials similar to or equivalent to those described herein may be used in the practice and testing of this technology, a limited number of exemplary methods and materials are described herein.

[0448] When a particular material is considered to be preferably used for constructing a component, obvious alternative materials with similar properties may be used as substitutes. Furthermore, unless otherwise stated, any and all components described herein are to be understood as capable of being manufactured and, therefore, can be manufactured together or separately.

[0449] It should be noted that, as used herein and in the appended claims, unless the context clearly indicates otherwise, the singular forms “a,” “an,” and “the” include their plural equivalents.

[0450] All publications mentioned herein are incorporated herein by reference and the methods and / or materials that are the subject of those publications are described. The publications discussed herein provide only those prior to the filing date of this application. Nothing herein should be construed as an admission that the present technology has no prior right to these publications due to prior invention. Furthermore, the dates of the publications provided may differ from the actual publication dates, which requires independent verification.

[0451] Furthermore, in the interpretation of the disclosed content, all terms should be interpreted in the broadest reasonable manner consistent with the context. In particular, the terms "comprising" and "including" should be interpreted in a non-exclusive manner as referring to an element, component, or step, indicating that the referenced element, component, or step may be present or used, or that the referenced element, component, or step may be combined with other elements, components, or steps not expressly referenced.

[0452] The headings included in the detailed descriptions are for the reader's convenience only and should not be used to limit the subject matter found throughout the disclosure or claims. These headings should not be construed as interpreting the scope or limitation of the claims.

[0453] Although the techniques described herein with reference to specific embodiments are given, it should be understood that these embodiments are merely illustrative of the principles and applications of the technology. In some cases, terms and symbols may imply specific details that are not required for the practice of the technology. For example, while the terms "first" and "second" may be used, unless otherwise specified, these terms are not intended to indicate any order, but rather to distinguish different elements. Furthermore, although the processing steps in a method may be described or shown sequentially, such order is not required. Those skilled in the art will recognize that such order can be modified and / or aspects of the method can be performed simultaneously or even concurrently.

[0454] Therefore, it should be understood that various modifications can be made to the illustrative embodiments, and other arrangements can be designed without departing from the spirit and scope of the present technology.

[0455] 5 aspects

[0456] Additional and / or optional aspects of the invention are set forth below.

[0457] 1. A device for treating respiratory disorders, comprising:

[0458] case;

[0459] User interface display;

[0460] A pressure source that provides a supply of pressurized gas;

[0461] A controller configured to control the pressure source;

[0462] A power source connection, configured to accept an electrical connection of a power source to provide power to the device; and

[0463] Multiple external batteries are electrically connected in series to the power source.

[0464] 2. The device according to claim 1, wherein the controller is configured to detect the connection of the plurality of external batteries and control the power supply to the device.

[0465] 3. The device according to any one of 1 to 2, wherein, in use, the external battery among the plurality of external batteries used to provide power to the device is a power supply external battery, and each of the plurality of external batteries is used sequentially as the power source, wherein the external battery closest to the power source is the last external battery to be used as the power source.

[0466] 4. The device according to any one of 1 to 3, wherein each of the plurality of external batteries is connected to an adjacent external battery by a cable.

[0467] 5. The device according to any one of 1 to 4 further includes an internal battery configured to be received within the housing, and in use, the internal battery is used as the power source after all power from the plurality of external batteries has been depleted.

[0468] 6. The device according to any one of 1 to 5, wherein an AC power supply is capable of being connected to the plurality of external batteries in the string, and in use, when the AC power supply is connected, the AC power supply is used as the power source.

[0469] 7. The device according to any one of 1 to 5, wherein the DC power supply is capable of being connected to the plurality of external batteries in the string, and in use, when the DC power supply is connected, the DC power supply is used as the power source.

[0470] 8. The device according to any one of 1 to 7, wherein, upon receiving a power capacity request from the controller, each of the plurality of external batteries is able to determine an estimate of its own remaining capacity.

[0471] 9. The device according to 8, wherein the remaining capacity of the external battery is used to determine an estimate of the total remaining operating time of the external battery.

[0472] 10. The device according to claim 9, wherein the total remaining operating time of the external batteries is determined as a function of the remaining capacity of each external battery and the remaining operating time of the power supply external battery.

[0473] 11. The device according to any one of 8 to 10, wherein the plurality of external batteries includes an upstream external battery and a downstream external battery, wherein the downstream external battery is electrically connected to the power source connection, and the upstream external battery is electrically connected to the downstream external battery in the string.

[0474] 12. The device according to 11, wherein the downstream external battery is connected to the power source via a cable.

[0475] 13. The device according to any one of 10 to 11, wherein one or more additional external batteries are electrically connected between the downstream external battery and the upstream external battery.

[0476] 14. The device according to any one of 11 to 13, wherein the upstream external battery is configured to send a determined estimate of the remaining capacity of the upstream external battery to the downstream external battery.

[0477] 15. The device of claim 14, wherein each of the one or more additional external batteries is configured to transmit an estimated value of the determined remaining capacity of the external battery to the downstream external battery along the string.

[0478] 16. The device according to any one of 14 to 15, wherein the downstream external battery is configured to determine the total remaining external battery capacity from all the external batteries electrically connected in the string.

[0479] 17. The device according to any one of 14 to 16, wherein the downstream external battery is configured to determine the total remaining external battery operating time from all the external batteries electrically connected in the string as a function of the remaining operating time of the power supply external battery.

[0480] 18. The device according to any one of 5 and 6 to 17 when referenced in 5, wherein, upon receiving a remaining capacity request from the controller, the internal battery is able to determine an estimate of the remaining capacity of the internal battery.

[0481] 19. The device according to 18, wherein the remaining capacity of the internal battery is used to determine an estimate of the remaining operating time of the internal battery.

[0482] 20. The device of claim 19, wherein the remaining operating time of the internal battery is determined as a function of the remaining operating time of the internal battery when it is used to provide power to operate the device, or the remaining operating time of the power supply of the external battery when one of the plurality of external batteries is used to operate the device.

[0483] 21. The device according to any one of 18 to 20 when referenced in any one of 8 to 17, wherein the controller is configured to calculate an estimate of the total remaining battery capacity of the plurality of external batteries and the internal batteries.

[0484] 22. The device according to any one of 18 to 21 when referenced in any one of 8 to 17, wherein the controller is configured to calculate an estimate of the total remaining battery operating time of the plurality of external batteries and the internal batteries.

[0485] 23. The device according to any one of 21 to 22, wherein the user interface display is configured to display an estimate of the total remaining battery capacity and / or an estimate of the total remaining battery runtime.

[0486] 24. The device according to any one of 1 to 23, wherein the device is a ventilator.

[0487] 25. A method for determining an estimate of the total available battery capacity from two or more battery power sources electrically connected to a breathing apparatus, the breathing apparatus including a controller configured to perform the following method:

[0488] Request an estimate of the available capacity from the first battery power source to provide the first battery capacity;

[0489] Request an estimate of the available capacity from the second battery power source to provide the second battery capacity; and

[0490] The first battery capacity and the second battery capacity are combined to determine an estimate of the total available battery capacity.

[0491] 26. The method according to 25, wherein the total available battery capacity is an estimate of the total state of charge from the first battery power source and the second battery power source.

[0492] 27. The method according to any one of 25 to 26, wherein the first battery power source is at least one external battery electrically connected to the breathing device, and the second battery power source is an internal battery located within the breathing device.

[0493] 28. The method of 27, wherein the first battery power source includes a plurality of external batteries connected in series, each of the plurality of external batteries including an input port and an output port configured to receive a cable therebetween.

[0494] 29. The method according to 28, wherein the plurality of external batteries includes a downstream external battery, the output port of the downstream external battery being electrically coupled to the breathing device via a cable, and the input port of the downstream external battery being electrically coupled to the output port of a second external battery among the plurality of external batteries via a cable.

[0495] 30. The method according to 29, wherein each of the plurality of external batteries is electrically coupled to the adjacent external battery via a cable connecting an input port of one of the plurality of external batteries to an output port of the adjacent external battery.

[0496] 31. The method according to 30, wherein each external battery provides an estimate of its available capacity and transmits the available capacity to the downstream external battery via the cable along the string.

[0497] 32. The method according to any one of 25 to 31, wherein when the first battery power source is a battery used to provide power to the breathing device, the total remaining operating time is calculated as a function of the total available battery capacity and the remaining operating time of the first battery.

[0498] 33. The method according to any one of 25 to 32, further comprising displaying the total available battery capacity on a user interface display of the breathing device.

[0499] 34. A breathing apparatus for supplying a breathable gas to a patient in a continuous cycle of breathing, each cycle comprising an inspiratory phase and an expiratory phase, the breathing apparatus comprising:

[0500] A fan, the fan including a motor, the motor being configured to accelerate to achieve an inspiratory pressure provided during the inspiratory phase and decelerate to achieve an expiratory pressure provided during the expiratory phase;

[0501] A first power source, configured to supply power to operate the motor of the wind turbine; and

[0502] An energy storage unit configured to store energy generated by the motor when the motor decelerates;

[0503] Specifically, when the voltage in the energy storage unit exceeds a first threshold, the power supply from the first power source to the motor is turned off, and the motor is powered by the energy in the energy storage unit. When the voltage in the energy storage unit drops below a second threshold, the power supply from the first power source to the motor is turned on.

[0504] 35. The breathing device according to 34, wherein the energy storage unit comprises at least one capacitor or supercapacitor.

[0505] 36. The breathing device according to any one of 34 to 35 further includes a regulator switch that monitors the voltage of the energy storage unit and switches on and off the power supply from the first power source to the motor.

[0506] Inventive concept

[0507] This invention provides the following inventive concept:

[0508] 1. A device for treating respiratory disorders, comprising:

[0509] case;

[0510] User interface display;

[0511] A pressure source that provides a supply of pressurized gas;

[0512] A controller configured to control the pressure source;

[0513] A power source connection, configured to accept an electrical connection of a power source to provide power to the device; and

[0514] Multiple external batteries are electrically connected in series to the power source.

[0515] 2. The device according to inventive concept 1, wherein the controller is configured to detect the connection of the plurality of external batteries and control the power supply to the device.

[0516] 3. The device according to any one of inventive concepts 1 to 2, wherein, in use, the external battery among the plurality of external batteries used to provide power to the device is a power supply external battery, and each of the plurality of external batteries is used sequentially as the power source, wherein the external battery closest to the power source is the last external battery to be used as the power source.

[0517] 4. The device according to any one of inventive concepts 1 to 3, wherein each of the plurality of external batteries is connected to an adjacent external battery by a cable.

[0518] 5. The device according to any one of inventive concepts 1 to 4 further includes an internal battery configured to be received within the housing, and in use, the internal battery is used as the power source after all power from the plurality of external batteries has been depleted.

[0519] 6. The device according to any one of inventive concepts 1 to 5, wherein an AC power supply is connectable to the plurality of external batteries in the string, and in use, when the AC power supply is connected, the AC power supply is used as the power source, or...

[0520] The DC power supply can be connected to the plurality of external batteries in the string, and in use, when the DC power supply is connected, the DC power supply is used as the power source.

[0521] 7. The device according to any one of inventive concepts 1 to 6, wherein, upon receiving a power capacity request from the controller, each of the plurality of external batteries is able to determine an estimate of its own remaining capacity, preferably wherein the remaining capacity of the external batteries is used to determine an estimate of the total remaining operating time of the external batteries, more preferably wherein the total remaining operating time of the external batteries is determined as a function of the remaining capacity of each external battery and the remaining operating time of the power supply to the external batteries.

[0522] 8. The device according to inventive concept 7, wherein the plurality of external batteries includes an upstream external battery and a downstream external battery, wherein the downstream external battery is electrically connected to the power source connection, and the upstream external battery is electrically connected to the downstream external battery in the string, preferably wherein the downstream external battery is connected to the power source connection by a cable.

[0523] 9. The device according to any one of inventive concepts 7 to 8, wherein one or more additional external batteries are electrically connected between the downstream external battery and the upstream external battery.

[0524] 10. The device according to any one of inventive concepts 8 to 9, wherein the upstream external battery is configured to send a determined estimate of the remaining capacity of the upstream external battery to the downstream external battery.

[0525] 11. The device according to inventive concept 10, wherein each of the one or more additional external batteries is configured to send a determined estimate of the remaining capacity of the external battery to the downstream external battery along the string, and preferably, wherein the downstream external battery is configured to determine the total remaining capacity of the external battery from all the external batteries electrically connected in the string.

[0526] 12. The device according to any one of inventive concepts 10 to 11, wherein the downstream external battery is configured to determine the total remaining external battery operating time from all the external batteries electrically connected in the string as a function of the remaining operating time of the power supply external battery.

[0527] 13. The device according to inventive concept 5 and any one of inventive concepts 6 to 12 when inventive concept 5 is cited, wherein, upon receiving a remaining capacity request from the controller, the internal battery is capable of determining an estimate of the remaining capacity of the internal battery, preferably wherein the remaining capacity of the internal battery is used to determine an estimate of the remaining operating time of the internal battery, more preferably wherein the remaining operating time of the internal battery is determined as a function of the remaining operating time of the internal battery when it is used to provide power to operate the device, or the remaining operating time of the power supply of the external battery when one of the plurality of external batteries is used to operate the device.

[0528] 14. The device according to inventive concept 13 when referring to any one of inventive concepts 7 to 12, wherein the controller is configured to calculate an estimate of the total remaining battery capacity of the plurality of external batteries and the internal batteries.

[0529] 15. The device according to any one of inventive concepts 13 to 14 when referring to any one of inventive concepts 7 to 12, wherein the controller is configured to calculate an estimate of the total remaining battery operating time of the plurality of external batteries and the internal battery, and / or wherein the user interface display is configured to display the estimate of the total remaining battery capacity and / or the estimate of the total remaining battery operating time.

[0530] 16. The device according to any one of inventive concepts 1 to 15, wherein the device is a ventilator.

[0531] 17. A method for determining an estimate of the total available battery capacity from two or more battery power sources electrically connected to a breathing apparatus, the breathing apparatus including a controller configured to perform the following method:

[0532] Request an estimate of the available capacity from the first battery power source to provide the first battery capacity;

[0533] Request an estimate of the available capacity from the second battery power source to provide the second battery capacity; and

[0534] The first battery capacity and the second battery capacity are combined to determine an estimate of the total available battery capacity.

[0535] 18. The method according to inventive concept 17, wherein the total available battery capacity is an estimate of the total state of charge from the first battery power source and the second battery power source.

[0536] 19. The method according to any one of inventive concepts 17 to 18, wherein the first battery power source is at least one external battery electrically connected to the breathing device, and the second battery power source is an internal battery located within the breathing device.

[0537] 20. The method according to inventive concept 19, wherein the first battery power source includes a plurality of external batteries connected in series, each of the plurality of external batteries including an input port and an output port configured to receive a cable therebetween.

[0538] 21. The method according to inventive concept 20, wherein the plurality of external batteries includes a downstream external battery, the output port of which is electrically coupled to the breathing device via a cable, and the input port of which is electrically coupled to the output port of a second external battery among the plurality of external batteries via a cable, and preferably wherein each of the plurality of external batteries is electrically coupled to the adjacent external battery via a cable connecting the input port of one of the external batteries to the output port of the adjacent external battery, and more preferably wherein each external battery provides an estimate of its available capacity and transmits the available capacity to the downstream external battery via the cable along the string.

[0539] 22. The method according to any one of inventive concepts 17 to 21, wherein when the first battery power source is a battery used to provide power to the breathing device, the total remaining operating time is calculated as a function of the total available battery capacity and the remaining operating time of the first battery, and / or the method further includes displaying the total available battery capacity on a user interface display of the breathing device.

Claims

1. A breathing apparatus (4000) for providing a supply of breathable gas to a patient breathing in a continuous cycle, each cycle comprising an inspiration phase and an expiration phase, the breathing apparatus (4000) comprising: a blower (4104) comprising a motor configured to accelerate to reach an inspiration pressure provided during the inspiration phase and to decelerate to reach an expiration pressure provided during the expiration phase; a first power source (4210) arranged to provide a supply of electrical power to operate the motor of the blower (4104); and an energy storage unit (4510) configured to store energy generated by the motor when the motor decelerates; wherein, when a voltage present in the energy storage unit (4510) exceeds a first threshold, the supply of electrical power to the motor from the first power source (4210) is turned off and the motor is energized by the energy in the energy storage unit (4510), and when the voltage in the energy storage unit (4510) falls below a second threshold, the supply of electrical power to the motor from the first power source (4210) is turned on. The energy storage unit (4510) comprises at least one capacitor or supercapacitor.

2. The respiratory device (4000) of claim 1, wherein, The energy storage unit (4510) comprises at least one capacitor, a set of capacitors or supercapacitors, or a battery.

3. The respiratory device (4000) of claim 1, wherein, 4. The breathing apparatus (4000) according to any one of claims 1 to 3, further comprising a control system (4230).

5. The breathing apparatus (4000) according to any one of claims 1 to 3, further comprising a regulator switch that monitors the voltage of the energy storage unit (4510) and turns on and off the supply of electrical power to the motor from the first power source (4210). The regulator switch is a boost regulator (4530).

6. The respiratory device (4000) of claim 5, wherein, The energy storage unit (4510) is positioned in parallel with the first power source (4210).

7. The respiratory device (4000) according to any one of claims 1 to 3, wherein, A diode (4520) is positioned between the energy storage unit (4510) and the first power source (4210).

8. The respiratory device (4000) according to any one of claims 1 to 3, wherein, The first power source (4210) comprises an external input supply (4540) and / or an internal battery (4450).

9. The respiratory device (4000) according to any one of claims 1 to 3, wherein, The external input supply (4540) comprises any one of an AC mains power supply (4434), a DC mains power supply (4460), or an external battery (4420, 4410).

10. The respiratory device (4000) of claim 9, wherein, 11. The breathing apparatus (4000) according to any one of claims 1 to 3, further comprising a motor driver (4105).

12. A method of operating a breathing apparatus (4000) according to any one of claims 1 to 3, 5 to 7, 9 to 11, the method comprising: storing energy generated by a main blower (4104) in an energy storage unit (4510) when the motor decelerates; ​ when a voltage present in the energy storage unit (4510) exceeds the first threshold, turning off power supply to the motor from the first power source (4210) and powering the motor from energy stored in the energy storage unit (4510), when the voltage in the energy storage unit (4510) falls below the second threshold, turning on power supply to the motor from the first power source (4210).

13. The method of claim 12, wherein, when the motor is transitioning from an inhalation pressure cycle to an exhalation pressure cycle, energy generated by the main blower (4104) is stored in the energy storage unit (4510).

14. The method of claim 12 or 13, wherein, The respiratory device (4000) further includes a control system (4230), a diode (4520) is positioned between the energy storage unit (4510) and the first power source (4210), the diode (4520) is used to provide power to the main blower (4104), and the control system (4230) is powered from the first power source (4210).

15. A method of determining an estimate of a total available battery capacity from two or more battery power sources electrically connected to a respiratory device according to any one of claims 1 to 11, the respiratory device further comprising a controller configured to: request an estimate of an available capacity from a first battery power source to provide a first battery capacity; request an estimate of an available capacity from a second battery power source to provide a second battery capacity; and combine the first battery capacity and the second battery capacity to determine an estimate of the total available battery capacity.

16. The method of claim 15, wherein, The total available battery capacity is an estimate of a total state of charge from the first battery power source and the second battery power source.

17. The method of claim 15, wherein, The first battery power source is at least one external battery electrically connected to the respiratory device, and the second battery power source is an internal battery located within the respiratory device.

18. The method of claim 17, wherein, The first battery power source includes a plurality of external batteries connected in series, each of the plurality of external batteries including an input port and an output port configured to receive a cable therebetween.

19. The method of claim 18, wherein, The plurality of external batteries includes a downstream external battery, an output port of the downstream external battery is electrically coupled to the respiratory device via a cable, and an input port of the downstream external battery is electrically coupled to an output port of a second external battery of the plurality of external batteries via a cable.

20. The method of claim 15, wherein, When the first battery power source is a battery used to provide power to the respiratory device, a total remaining run time is calculated as a function of the total available battery capacity and a remaining run time of the first battery, and / or the method further includes displaying the total available battery capacity on a user interface display of the respiratory device.

21. The method of claim 19, wherein, Each of the plurality of external batteries is electrically coupled to an adjacent external battery via a cable connected between an input port of one of the plurality of external batteries and an output port of the adjacent external battery.

22. The method of claim 21, wherein, Each external battery provides an estimate of available capacity and sends the available capacity along the string to the downstream external battery via the cable.

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