Aerodynamic system, method and device for removing debris from a hollow organ

Abstract

This invention pertains to a system, a method and a device for outwards clearing of debris and secretions within the main airways of the lungs and for preventing their aspiration into the lungs, while dynamically assisting the exhalation of air during the expiratory phase of ventilation. The device comprises an endotracheal tube comprising a hollow conduit in communication with a gas source that is synchronized with a subject's respiration. The device may be actuated during the inhalation phase, and / or the exhalation phase of the respiratory cycle. The endotracheal tube is stably placed in a main airway of the lung. The endotracheal tube comprises a circular jet emitting member that has at least one aperture pointing generally towards the airway opening. When pressurized gas flows through the hollow conduit and into the jet emitting member,jets of gas are emitted generally in the direction of the airway opening. These jets push debris and secretions outward while entraining exhaled air by the Venturi effect and thereby assisting exhalation and reducing intra-thoracic pressure.

Description

[0001] AERODYNAMIC SYSTEM, METHOD AND DEVICE FOR REMOVING DEBRIS FROM A HOLLOW ORGAN

[0002] FIELD OF THE INVENTION

[0003] The invention is in the field of applied aerodynamics for medical applications, and more specifically in the field of aerodynamics for removing debris and secretions from hollow organs such as airways.

[0004] BACKGROUND OF THE INVENTION

[0005] Intubated and ventilated patients are frequently inflicted with a lung infection known as Ventilator-Associated Pneumonia (VAP). VAP increases the morbidity and mortality of ventilated Intensive Care Unit (ICU) patients, increases the length of stay in the ICU and dramatically increases the cost of treatment (Ventilator-associated pneumonia in adults: a narrative review; Laurent Papazian et al. Intensive Care Med. 2020; 46(5): 888-906.). VAP is caused by a variety of bacteria that enter the lungs during intubation or later either through the tube or around the cuff, between the cuff and the tracheal wall. The intubated patient is incapable of coughing and removing secretions and debris from the airways. As such, suctioning of the airways is needed to remove the secretions. Unfortunately, VAP infection leads to increase in secretions necessitating even more frequent suctioning which is associated with many adverse effects (Airway Clearance Techniques: The Right Choice for the Right Patient, Stefano Belli et al. Front Med (Lausanne), 2021; 8: 544826; and Airway Management and Ventilator-Associated Events; Amanda M. Dexter and J. Brady Scott, Respiratory Care, August 2019, 64 (8) 986-993). The literature mentioned above outlines both the need for suctioning and the risks associated therewith.

[0006] The introduction of a suction catheter via the endotracheal tube into the airways is required to remove secretions from the airways, but at the same time it pushes secretions that line the inner surface of the endotracheal tube into the airways, which causes further contamination and infection. Airways suctioning in intensive care, whether as a closed or open system has not changed in the last 50+ years and likewise the rates of Ventilator Associated Pneumonia (VAP) and Events (VAE) have essentially remained stable. Clearly a new approach is needed.

[0007] US5544648 relates to a device for creating sub-atmospheric pressure near the carina of a patient. The device includes a channel or perforation oriented distally, which generates a reverse Venturi effect during exhalation. This device is used for removing carbon dioxide from the lungs.

[0008] US 20140246015 discloses cleaning device, system and method for use with an endotracheal or tracheostomy tube, a ventilator, a fluid source and a suction source. The device cleans or prevents biofilm on the inner surface of the tube by delivering fluid into the tube, wiping the interior with an expandable wiping element moved longitudinally, and suctioning material out of the tube.

[0009] US 20210068861 discloses an accessory device that may be used in combination with a thrombectomy catheter. The accessory device may be configured to deflect a distal portion of the thrombectomy catheter and / or disrupt a lesion in a vessel.

[0010] The present invention provides a novel approach utilizing outward pointing aerodynamic jets as means for removing secretions and debris.

[0011] SUMMARY OF THE INVENTION

[0012] The present invention pertains to a device, and a system comprising an elongated tube extending between a distal end and a proximal end, the tube comprising jet emitting member comprising a ring or a sleeve that encircles a portion of the elongated tube from the peripheral outer wall and / or inner wall thereof. The device comprises a conduit extending along a length of the elongated tube and being in communication with the jet emitting member. The conduit is configured to convey gas from a compressed fluid source and into the jet emitting member. The jet emitting member comprises at least one aperture, optionally, a plurality of apertures facing the proximal end of the elongated tube and forming at least one jet emitting the gas in the proximal direction of the device when the gas fills the jet emitting member.

[0013] The herein invention may be used in tubular hollow organs, such as the trachea.

[0014] In an aspect of the invention, the device is configured as a ventilation device used in an ICU. In such configurations the elongated tube may be an endotracheal tube or a tracheostomy configured to be inserted into the trachea of a subject, and the conduit is configured to provide gas into the jet emitting member of the device. The apertures of the jet emitting member may face an opposite direction of the lung to generate jets emitted essentially in the expiratory direction.

[0015] The current approach used to clear the airways may include utilizing a suction catheter that is inserted into the trachea, optionally via an endotracheal tube and suctions secretions and debris. The advantages of utilizing the herein device with the outward pointing jets over outright suctioning through a suction catheter for clearing the airways are significant. The most important one is that suctioning can collapse a lung segment. This is particularly concerning because, in many intensive care units, the practice is to ventilate the patient with 100% oxygen prior to suctioning. As such, when the suctioning is activated and an airway leading to a lung segment collapses, the oxygen-filled alveolar zone of the lung segment loses its continuity with the air. Over a few minutes, the 02 is taken up by the blood in the capillaries traversing this lung segment, leading to further collapse and atelectasis. Re-opening of the lung region may require high pressure and time due to the adhesive forces that hold the collapsed airways together. This creates fertile ground for bacterial growth and the onset of pneumonia. The outward directed jets of the herein device generate only a limited degree of negative pressure through the Venturi effect, insufficient to cause airway collapse and / or atelectasis. Advantageously, the jet(s) can break down debris and mounds of secretions and push the fragmented elements outwards in a similar way to that of coughing that carries with it secretions.

[0016] Thus, an aspect of the invention pertains to a device for clearing hollow tubular organs from debris, particles and / or secretions, the device comprising an elongated hollow tube extending between a distal end and a proximal end, the tube comprising a jet emitting member that encircles at least a portion of the elongated tube from the peripheral outer wall and / or inner wall thereof, wherein the device comprising a conduit being in communication with the jet emitting member configured to convey gas from a compressed gas source and into the jet emitting member, wherein the jet emitting member comprises at least one aperture facing the proximal end of the elongated tube and forming at least one jet emitting the gas in the proximal direction of the device when the gas fills the jet emitting member.

[0017] In another aspect, the invention provides a system for clearing hollow tubular organs from debris, particles and / or secretions, the system comprising a gas source for accommodating compressed gas, an elongated hollow tube comprising a jet emitting member that encircles a portion of the tube from the peripheral outer wall and / or inner wall thereof, a conduit being in communication with the jet emitting member to convey the gas from the gas source and into the jet emitting member, wherein the jet emitting member comprising at least one aperture facing the proximal end of the elongated tube and forming at least one jet emitting gas in the proximal direction of the device, when the gas fills the jet emitting member.

[0018] In another aspect, the invention provides a device for clearing hollow tubular organs from debris, particles and / or secretions, the device comprising a gas source configured to accommodate compressed gas; an elongated tube extending between a distal end and a proximal end; a jet emitting member connected to said elongated tube; a conduit in fluid communication with said jet emitting member configured to convey said gas from said gas source and into said jet emitting member, wherein said jet emitting member comprising at least one aperture positioned to direct gas flow toward the proximal end of said elongated tube and configured to form at least one jet emitting gas in a proximal direction of said device, when said gas fills said jet emitting member.

[0019] In one or more embodiments, the elongated tube is hollow. In one or more embodiments, the device is a ventilation device and the elongated tube is an endotracheal tube configured to be inserted into the trachea of a subject to provide a passageway for ventilation gases between a ventilator and the patient’s lungs, and wherein the conduit is configured to provide gas into the jet emitting member in a direction of the lung airways, and wherein the aperture is positioned in an opposite direction relative to the lung to generate at least one jet emitted essentially in an expiratory direction, away from lungs of the subject.

[0020] In one or more embodiments, the elongated tube is opened at its distal end. In one or more embodiments, the elongated tube is opened at its proximal end.

[0021] In one or more embodiments, the gas is a respirable gas.

[0022] In one or more embodiments, the jet emitting member is made from a flexible material. In one or more embodiments, the jet emitting member is made from a rigid material. In one or more embodiments, the jet emitting member is made from an elastic material. In one or more embodiments, the jet emitting member is inflatable and moveable between an inflated state and a deflated state.

[0023] In one or more embodiments, the jet emitting member is configured as a circular ring that encircles at least a portion of the elongated tube from its exterior surface. In one or more embodiments, the jet emitting member is configured as a sleeve. In one or more embodiments, the jet emitting member is configured as an inner bulge surrounding an inner surface of the elongated tube. In one or more embodiments, the jet emitting member is configured as an inner horizontal bulge that surrounds an inner periphery of the elongated tube. In one or more embodiments, the jet emitting member is configured as an inner vertical bulge extending along the wall of elongated tube. In one or more embodiments, the jet emitting member is configured as an inner duct disposed within the hollow elongated tube. In one or more embodiments, the jet emitting member is configured as a rotary peripheral element

[0024] In one or more embodiments, the jet has kinetic energy sufficient to entrain additional gas from the surrounding environment and lower the pressure in the airways and lungs. In one or more embodiments, the at least one jet is capable of preventing debris and secretions from entering the lungs and the at least one jet is directed to expel debris and secretions from the airway lumen and walls away from the lungs.

[0025] In one or more embodiments, the device and system further comprise a pressure monitoring and control unit comprising a pressure sensor configured to monitor and adjust the gas pressure within the device and / or its surroundings to maintain a pressure below the harmful levels, within up to about 3000 Pa.

[0026] In one or more embodiments, the elongated tube is configured as a catheter.

[0027] In one or more embodiments, the conduit is embedded within a wall of the elongated tube or positioned as a separate channel that extends along the outer and / or inner wall of the elongated tube.

[0028] In one or more embodiments, the elongated tube is configured as a suction catheter.

[0029] In one or more embodiments, the elongated tube is configured as a bronchial blocker catheter.

[0030] In one or more embodiments, the conduit conveying the gas is configured as a visualization catheter (bronchoscope).

[0031] In one or more embodiments, wherein the jet emitting member is configured as a sleeve connected to elongated tube at a distal end of said sleeve and positioned around a portion of an outer surface of the elongated tube, wherein the conduit comprises at least one conduit aperture that delivers gas through the conduit such that it is emitted to a cavity formed between the sleeve and the elongated tube, wherein said aperture in the form of a peripheral slit is present between the proximal end of the sleeve and the elongated tube, wherein gas delivered through the conduit is emitted to the sleeve through said conduit aperture and is dispersed to form said one or more jet(s) in a proximal direction through the peripheral slit.

[0032] In one or more embodiments, the jet emitting member is disposed to encircle an outer surface of the elongated tube, and the at least one aperture is disposed on a proximal top surface of the jet emitting member.

[0033] In one or more embodiments, the plurality of the apertures are located sequentially along the top proximal surface of the jet emitting member.

[0034] In one or more embodiments, the jet emitting member is disposed internally and surrounds an inner surface of the elongated tube and the at least one aperture is located internally inside the lumen of the tube.

[0035] In one or more embodiments, the gas flows into the jet emitting member in a continuous manner. In one or more embodiments, the gas flows into the jet emitting member in pulses. In one or more embodiments, the jets are emitted from the apertures synchronously with the expiratory phase of a ventilation cycle.

[0036] In one or more embodiments, the jets are emitted from the apertures synchronously with the inspiratory phase of ventilation cycle.

[0037] In one or more embodiments, a distal end of the conduit or elongated tube is connected to a pressure sensor. In one or more embodiments, a proximal end of the conduit is connected to a gas source. In one or more embodiments, a proximal end of the elongated tube is connected to a ventilation system. In one or more embodiments, the device further comprises an alarm, wherein when the pressure detected by the pressure sensor exceeds a pressure value ranging between 2000 and 3000 Pa, an alarm signal is triggered.

[0038] In one or more embodiments, when the measured pressure exceeds a pressure value of 3000 - 5000 Pa an instantaneous flow of the gas is halted.

[0039] In one or more embodiments, the number of jets is between 1 and 8. In one or more embodiments, the number of jets is between 3 and 8. In one or more embodiments, the number of jets is up to two. In one or more embodiments, the number of jets is greater than 8. In one or more embodiments, the number of jets is 1.

[0040] In one or more embodiments, the jet emitting member is configured as a sleeve positioned about an inner or outer surface of the tube.

[0041] In one or more embodiments, the jet emitting member is configured as a protruding ring positioned on an inner or outer surface of the tube.

[0042] In one or more embodiments, the elongated tube comprises an inflatable cuff that, when inflated, holds the tube steadily within the tubular organ.

[0043] In one or more embodiments, wherein the elongated tube comprises an inflatable cuff that is moveable between an inflated configuration and a deflated configuration, the inflatable cuff positioned near the distal end of the elongated tube and the jet emitting member is positioned proximally to the inflatable cuff, wherein the inflated configuration holds the tube steadily within the tubular organ.

[0044] In one or more embodiments, the cuff is inflated and deflated intermittently, optionally in synchronization with pulses of the pressurized gas emitted from the jet emitting member. In one or more embodiments, the cuff is inflated and deflated intermittently, optionally in synchronization with the respiratory cycle.

[0045] In one or more embodiments, the gas source provides an intermittent flow of the pressurized gas, each period of flow lasting between 0.2 to 10 seconds and each interval between flow pulses lasting between 0.2 to 20 seconds. In one or more embodiments, the intermittent flow of the pressurized gas is synchronized with a specific phase of a ventilation cycle, the specific phase being at least one of an expiratory phase, an inspiratory phase, or a portion thereof.

[0046] In one or more embodiments, the jets have a flow velocity between 1 to 100 m / s.

[0047] In one or more embodiments, the at least one aperture comprises between 5 and 25 apertures arranged in a circle on the jet emitting member.

[0048] In one or more embodiments, each of the at least one aperture has a diameter between 0.2 mm to 2 mm.

[0049] In one or more embodiments, the pressure of the pressurized gas entering the tube or conduit is between 200 to 4000 millibars.

[0050] In one or more embodiments, the flowrate of the pressurized gas entering the tube or conduit is between 50 to 500 milliliters per second.

[0051] Another aspect of the invention pertains to a respiratory clearing device, comprising: an elongated tube extending between a distal end and a proximal end, the elongated tube comprising a lumen configured for respiratory gas delivery; an inflatable cuff positioned near the distal end of the elongated tube and configured to synchronize with respiratory cycles, the inflatable cuff moveable between an inflated configuration during an inhalation phase and a deflated configuration during an exhalation phase; one or more cuff apertures extending from the lumen of the elongated tube to the inflatable cuff, the cuff apertures configured to inflate the inflatable cuff when respiratory gas flows within the lumen; a jet emitting member positioned proximally to the inflatable cuff and configured to create at least one jet toward a proximal direction; a conduit in fluid communication with the jet emitting member and configured to convey gas to the jet emitting member; and at least one aperture in the jet emitting member oriented to direct gas flow toward the proximal end of the elongated tube and configured to form at least one jet when gas fills the jet emitting member.

[0052] In one or more embodiment, wherein during the inhalation phase, the inflatable cuff expands through gas flow via the cuff apertures to create a seal that blocks an airway distal to the cuff position, and wherein during the exhalation phase, the inflatable cuff deflates to allow natural expiratory flow around the elongated tube. In one or more embodiment, wherein the deflated cuff configuration enables exhaled gas to flow around an exterior of the elongated tube, creating additional flow pathways that may enhance clearing effectiveness through coordinated interaction between natural expiratory flow and directed jet streams.

[0053] In one or more embodiment, wherein the inflated cuff configuration enables clearing effectiveness during the inhalation phase and avoids collision between inhaled air and jet streams flowing in the opposite / proximal direction to the inhaled air (distal direction).

[0054] In one or more embodiments, wherein the at least one jet may operate during both inhalation and exhalation phases to provide continuous clearing pathways throughout an entire respiratory cycle.

[0055] In yet another aspect, the invention provides a method for clearing debris and secretions from a hollow organ, comprising: providing an elongated tube extending between a distal end and a proximal end, the elongated tube comprising a jet emitting member and a conduit in fluid communication with the jet emitting member and a gas source, the jet emitting member comprising at least one aperture pointing generally towards an opening of the hollow organ; flowing a pressurized gas through the conduit and into the jet emitting member; and emitting at least one jet from the at least one aperture in a direction of the opening of the hollow organ, the at least one jet entraining fluid to assist fluid movement and push debris and secretions outward.

[0056] In yet another aspect, the invention provides a method of injecting jets of compressed respirable gas inside a lung airway in the outward direction, the method comprising providing a ventilation device comprising an endotracheal tube extending between a distal end and a proximal end, the endotracheal tube comprising a jet emitting member and a conduit in fluid communication with the jet emitting member and a gas source comprising pressurized gas, wherein said jet emitting member comprises at least one aperture facing a proximal end of the endotracheal tube; inserting the endotracheal tube into a trachea of a subject in need thereof; connecting the conduit of said endotracheal tube to the gas source; and flowing a pressurized gas through said conduit and into said jet emitting member; and forming at least one jet emitting said gas in the proximal direction of said device when said gas fills said jet emitting member.

[0057] In yet another aspect, the invention provides a method for outwards clearing of debris and secretions from a lung airway, comprising providing an elongated tube extending between a distal end and a proximal end, the elongated tube comprising a jet emitting member, and a conduit in a fluid communication with said jet emitting member and a gas source, the jet emitting member comprising at least one aperture pointing generally towards an opening of the lung airway; flowing a pressurized gas through the conduit and into said jet emitting member; and emitting at least one jet from the at least one aperture in a direction of the opening of the lung airway, the jet entraining exhaled air to assist exhalation, and push debris and secretions outward.

[0058] In yet another aspect, the invention provides a method of injecting jets of compressed respirable gas inside a lung airway in the outward direction, the method comprising providing a ventilation device comprising an endotracheal tube; inserting the endotracheal tube into a trachea of a subject in need thereof; connecting a conduit of the endotracheal tube to a gas source wherein the jets emitting member comprises at least one aperture facing a proximal end of the endotracheal tube; filling using the conduit the peripheral jets emitting member of the endotracheal tube with a gas; and forming at least one jet emitting the gas in the proximal direction of the device when the gas fills the jets emitting member.

[0059] In another aspect the invention provides a method for outwards clearing of debris and secretions within a lung airway, comprising: providing a hollow tube extending between a distal end and a proximal end, the hollow tube comprising jets emitting member, and a conduit in a fluid communication with the jets emitting member and a gas source, the jet emitting member comprising at least one aperture pointing generally towards an opening of the lung airway; flowing a pressurized gas through the conduit and into the jets emitting member; and emitting jet from the at least one aperture in a direction of the opening of the lung airway, the jets entraining exhaled air to assist exhalation, and push debris and secretions outward.

[0060] In one or more embodiments, wherein the step of flowing a pressurized gas is synchronized with a subject's respiration such that the at least one jet is emitted during an expiratory phase of a ventilation cycle.

[0061] In one or more embodiments, the gas source is synchronized with a subject's respiration.

[0062] In one or more embodiments, the tube is an endotracheal tube, a suction catheter, or a bronchial blocker catheter. In yet another aspect, the invention provides system for clearing hollow tubular organs from debris, particles and secretions, comprising: a gas source configured to accommodate compressed gas; an elongated hollow tube extending between a distal end and a proximal end; a jet emitting member associated with the elongated hollow tube; a conduit in communication with the jets emitting member and configured to convey the gas from the gas source into the jets emitting member; and at least one orifice in the jet emitting member oriented to direct gas flow toward the proximal end of the elongated hollow tube and configured to form at least one jet emitting the gas in a proximal direction when the gas fills the jets emitting member.

[0063] BRIEF DESCRIPTION OF THE DRAWINGS

[0064] Some embodiments of the invention are herein described, by way of example only, with reference to the accompanying drawings. With specific reference now to the drawings in detail, it is stressed that the particulars shown are by way of example and for purposes of illustrative discussion of embodiments of the invention. In this regard, the description taken with the drawings makes apparent to those skilled in the art how embodiments of the invention may be practiced.

[0065] Figure l is a side view of an exemplary device for clearing hollow tubular organs from debris, particles and / or secretions, according to some embodiments of the invention.

[0066] Figure 2 is a longitudinal section of the device of figure 1, according to some embodiments of the invention.

[0067] Figure 3 is another longitudinal section of the device of figure 1, according to some embodiments of the invention.

[0068] Figure 4 is a cross section of the device of figure 1, according to some embodiments of the invention.

[0069] Figure 5A illustrates a longitudinal section of an alternative clearing device with a sleeve configuration, according to some embodiments of the invention.

[0070] Figure 5B illustrates a cross-sectional view of the clearing device of FIG. 5 A through section AA, according to some embodiments of the invention.

[0071] Figure 5C illustrates a cross-sectional view of the clearing device of FIG. 5 A through section BB, according to some embodiments of the invention. Figure 6 is a longitudinal section of another exemplary device comprising an internal peripheral ring comprising internal jets within an elongated tube, according to some embodiments of the invention.

[0072] Figure 7 is a side view of another exemplary device configured as a suction catheter, according to some embodiments of the invention.

[0073] Figure 8A is a longitudinal section of another exemplary device comprising a rotary member, according to some embodiments of the invention.

[0074] Figure 8B is a cross section of the device of figure 8A, according to some embodiments of the invention.

[0075] Figure 8C is a cross section of the device of figure 8A, according to some embodiments of the invention.

[0076] Figure 9A is a side view of a clearing device with a jet emitting member comprising an outer sleeve, according to some embodiments of the invention.

[0077] Figure 9B is a front view of the device of figure 9A, according to some embodiments of the invention.

[0078] Figure 9C is a cut view of the device of figure 9A, according to some embodiments of the disclosure.

[0079] Figure 10 is a flow chart depicting a pressure monitoring and control unit of the herein devices, according to some embodiments of the invention.

[0080] DETAILED DESCRIPTION OF THE INVENTION

[0081] The following description sets forth exemplary aspects of the present disclosure. It should be recognized, however, that such description is not intended as a limitation on the scope of the present disclosure. Rather, the description also encompasses combinations and modifications to those exemplary aspects described herein.

[0082] The present disclosure relates to an aerodynamic system for removing debris from hollow organs, particularly focusing on maintaining airways clear of secretions and debris. The system utilizes pressurized gas jet(s) to create outward flow patterns that assist in clearing unwanted materials from tubular biological structures.

[0083] Conventional approaches for clearing airways in medical settings typically involve mechanical suction methods that may introduce complications such as airway collapse and potential contamination. The disclosed aerodynamic approach provides an alternative method that employs controlled gas flow to generate j et(s) directed away from sensitive organ areas. The jet(s) create aerodynamic effects that may help mobilize and remove accumulated secretions and debris.

[0084] The aerodynamic system operates on principles of fluid dynamics, where pressurized gas is emitted from a jet(s) emitting member. The jets emitting member contain one or more aperture(s) that direct gas flow to create beneficial clearing effects. The gas flow may be continuous or intermittent, depending on the particular application and timing requirements of the medical procedure.

[0085] Flow rates and pressures may be adjusted based on the specific anatomical requirements and the nature of the debris or secretions being addressed.

[0086] Thus, the present invention pertains to a system, a device and a method for outwards deflecting and clearing debris, particles and secretions from a hollow organ, such as a gascontaining duct. It is also intended to help evacuate the duct by creating negative pressure by means of the Venturi mechanism. Suitable organs include airways, blood vessels, gastrointestinal tract, urinary tract, and bile ducts.

[0087] The device and system comprise an elongated tube, a gas conduit, and a fluid source or container configured to accommodate a pressurized gas, such as a compressed gas cylinder or a compressor.

[0088] Gas composition may include various respirable mixtures suitable for medical applications. The gas may include, for example, a respiratory gas comprising pure oxygen or oxy gen-enriched mixtures, or standard medical air (-21% Oxygen, -78% Nitrogen, - 0.93% Argon, and - 0.04% Carbon Dioxide -CO2). The respiratory gas may contain oxygen at various concentrations (e.g., 20% or 30%). The respiratory gas may contain nitrous oxide. The system may also accommodate therapeutic gas combinations that provide additional benefits beyond debris clearing. The gas may contain treatment agents such as lungs therapeutic agents, e.g., 70% helium with 30% oxygen or 80% helium with 20% oxygen, and / or anaesthetic agents.

[0089] The elongated tube may feature a peripheral jet emitting member configured to accommodate a gas therein and comprising one or more apertures. The gas repeatedly or continuously fills the jet emitting member via a gas conduit. The pressurized gas flows to the jet emitting member comprising one or more aperture, optionally pointing toward the airway opening.

[0090] The one or more apertures may have a conical shape comprising a narrow part facing in or out or may comprise a cylindrical shape. As used herein, the term 'aperture' may refer to any opening, passage, or flow path through which gas can be directed, including but not limited to orifices, such as circular orifices, elongated slits, rectangular slots, oval openings, curved passages, linear cuts, or any combination thereof.

[0091] The device may further comprise a pressure monitoring and control unit comprising one or more controllable valves that modulate the flow of the gas into the jet emitting member or the conduit that conveys the gas to the jet emitting member. Due to a venturi effect caused by the gas flowing from the jet emitting member and through the aperture(s) with constricted diameter, jet(s) of gas is expelled into the outer surrounding allowing to clear the surrounding. The device is configured to be placed inside a duct or an airway such as trachea of a lung.

[0092] The jet flows emitted from one or more apertures may be adjusted to provide a flow velocity which is comparable to the speed of the air during a cough. The flow velocity may be of 1 to 100 meters per second (m / s). The flow velocity may be up to 10, 20, 30, 40, 50, 60, 70, 80, 90, or 100 m / s. Each possibility represents a separate embodiment of the invention. The number of jets may be between 1 and 50 or between 1 and 25. The jets may be arranged in a circle on the side of the jet emitting member facing the entry to the trachea and away from the lung. The number of jets or jet apertures may vary and may include 1 to 50, 1 to 25, 4 to 25, 6 to 25, 8 to 25, 10 to 25, 2 to 22, 2 to 20, 2 to 18, 2 to 16, 2 to 14, 2 to 12, 2 to 10, or 2 to 8, or any number in-between. Each possibility represents a separate embodiment of the invention.

[0093] Each aperture size may be set to be of a diameter of 0.2 to 2 mm, 0.2 to 1 mm, 0.2 to 1.5 mm, or 0.5 to 1.5 mm. Each possibility represents a separate embodiment of the invention.

[0094] The jet gas speed may be controlled by adjusting the flowrate and the pressure of the gas flow. The gas entry pressure may be set to be between 200 and 4000 millibars, 200 to 3000, 500 to 4000, or any value in between. The gas entry pressure may be set to be up to 2,000, 2,500, 3,000, 3,500, or 4,000 millibars. Each possibility represents a separate embodiment of the invention.

[0095] The gas flow rate entering the jet emitting member or gas conduit may be set to be between 50 and 500 milliliters per second (mL / s), 50 to 300, or 100 to 400, or 100 to 500 or any value in between. Each possibility represents a separate embodiment of the invention.

[0096] The system and device may include a pressure sensor that may be located about various locations, such as a location at the proximal side or end of the jet emitting member, distal end of the elongated tube, and / or ring. The pressure sensor may include any suitable sensor type, such as a piezoresistive, capacitive, or MEMS-based sensor. The pressure sensor may be configured to measure absolute, gauge, or differential pressure, and may be integrated within the wall of the tube, disposed in communication with the lumen of the tube, or connected externally via a dedicated tube. A pressure regulator or a servo-controlled mechanism may be used to adjust the pressure of the gas flow. The flow entering the jet emitting member can be continuous or intermittent. Each period of in-flow may last between 0.2 to 10 seconds. Each interval between flow pulses may last between 0.2 to 20 seconds. In an embodiment of the invention, the flow pulses coincide with the respiratory cycle to be activated during a specific phase of the ventilation cycle such as the expiratory phase or the inspiratory phase or portion of each thereof. In an embodiment of the invention, the flow pulses coincide / synchronize with the expiratory phase of the respiratory cycle or ventilation cycle.

[0097] Various shapes and sizes of the jet emitting member are contemplated, including a ring structure that encircles a circumference of the elongated tube, a sleeve positioned around or within a portion of the elongated tube, an inflatable balloon or bladder that expands when filled with gas, a bulge or protrusion extending from a surface of the elongated tube, a collar or band surrounding the elongated tube, a chamber integrated into a wall of the elongated tube, or combinations thereof.

[0098] An embodiment of this invention includes a jet emitting member that is surrounding a tube inserted into the airways, such as an endotracheal tube inserted into the trachea, a suction catheter inserted into the central airways and a bronchial blocker catheter inserted into the left or the right main bronchi during pneumonectomy. The inserted tube may have an inflatable cuff that, when inflated, holds it steadily in the airway. It may also have a cuff that is inflated and deflated intermittently in in-phase or out-of-phase synchronization with the pulses of flow emitted from the jet emitting member. The timing of the flow pulses may also be synchronized with the compressions of the chest during CPR for reviving a patient in cardiac arrest. In yet another embodiment, the gas / jet flow out of the jet emitting member will coincide with the outward flow from the trachea (exhalation phase).

[0099] In yet another embodiment, the jet emitting member with its outward pointing jet(s) is placed around a bronchoscope inserted into the airways for diagnosis or treatment of the patient’s lung. In yet another embodiment, a plurality of such jet(s) emitting member can be positioned around the inserted tube in axial intervals to amplify the entrainment of gas and improve the clearing of secretions.

[0100] In yet another embodiment, the jet emitting member may be internal inside the tube inserted into the airways. Alternatively, the jet may be internal but emerging directly from the inner surface of the tube without a protruding jet emitting member.

[0101] Referring to the drawings, FIG. 1 illustrates an exemplary embodiment of a clearing device 10 of the invention. The device 10 comprises an elongated tube 11, which may be an endotracheal tube or a tracheostomy. The elongated tube 11 is configured to be placed within the trachea T of a subject in need thereof. Elongated tube 11 may be made from a flexible plastic tube configured to be inserted through the mouth or nose or a tracheostomy opening into the trachea T to maintain an open airway or facilitate mechanical ventilation including removing of debris, particles, and secretions through aerodynamic mechanisms. Elongated tube 11 may be sized to fit within the trachea T of a subject, and may be formed, for example, from a length of flexible, tissue-compatible plastics, such as polyvinyl chloride or another plastic, silicon rubber, or another sufficiently flexible material. Elongated tube 11 may alternatively be inserted through a stoma (opening) of a subject leading to trachea T in which elongated tube

[0102] 11 is inserted. The device 10 may be configured for being used in procedures performed in critical care settings, such as during surgery or for patients who require assistance with breathing, particularly in the intensive care unit (ICU). Device 10 extends between a distal end 13 and a proximal end (not shown). The device 10 is configured as an elongated endotracheal tube 11 configured for insertion into the trachea T and positioning thereof such that distal end 13 is disposed in the trachea T and the proximal end exits the mouth of a subject (not shown). The proximal end may have a connector that attaches to a breathing circuit connected to a ventilator or anesthesia machine, supplied by a gas source (such as oxygen cylinders, compressed air, or hospital pipeline systems).

[0103] Device 10 may comprise an inflatable cuff 12 extending from or positioned proximate distal end 13. The inflatable cuff 12 may secure the clearing device 10 within the hollow tubular organ by expanding to contact surrounding tissue walls. The positioning of the inflatable cuff

[0104] 12 near the distal end 13 enables effective anchoring without interfering with the primary clearing functions of the clearing device 10. Inflatable cuff 12 can be inflated and deflated utilising an auxiliary cuff inflating tube (not shown).

[0105] Device 10 further includes a jet emitting member 20 which may feature a ring structure which surrounds a position on the periphery of device 10. Ring 20 may be disposed on various peripheral positions along the length of tube 11. For example, the peripheral ring 20 may be positioned to encircle a position on the middle periphery of tube 11. Ring 20 is configured to be filled with gas, such as air or another respirable gas 18. The ring 20 is configured to be filled with the gas 18 via a gas conduit 16 which is in fluid communication with the hollow peripheral ring 20 and a compressed gas source. The gas conduit 16 extends along the elongated tube 11 and provides a dedicated pathway for gas delivery. The gas 18 flows through the gas conduit 16 under controlled pressure and flow rate conditions to ensure appropriate jet formation and clearing effectiveness. The gas 18 then emerges as high-velocity jets 22 through a plurality of apertures, such as orifice 21 facing outwards in a proximal direction of tube 11. The high velocity jets 22 diminish the pressure surrounding them by virtue of a Venturi effect. This reduced pressure entrains gas near the jets and cause it to flow faster outwards. In addition, the outward pointing jets 22 sweep debris and secretions and push them out, preventing them from being aspirated into the lung.

[0106] In an embodiment of the invention, the gas 18 flows into the ring 20 via gas conduit 16 when the cuff 12 is inflated (not shown here).

[0107] The ring 20 may be made from various materials. For example, the ring 20 may be manufactured from rigid or flexible materials. The ring 20 may be manufactured from an elastic material, such that radial compression pushes the gas within the ring 20 out from the ring 20 via the orifices 21. For example, ring 20 may be made from a plastic (e.g., polyurethane), a rubber, or another flexible or elastic material. Ring 20 may be made from a material resistant to gas (e.g., nitrous oxide, oxygen) permeation, such as a crosslinked, polyester polyurethane resin.

[0108] Figure 2 shows a longitudinal section of the endotracheal tube 11 where the orifices 21 are essentially parallel to an elongated axis of the endotracheal tube 11. This drawing shows the peripheral ring 20 with orifice 21 that surrounds the endotracheal tube 11 located in this embodiment just proximal to the cuff 12 of the endotracheal tube 11.

[0109] The device 10 may incorporate internal structural elements that provide mechanical support and enhance operational functionality during medical procedures. The elongated tube 11 may be reinforced with a metal coil 30 that extends along the length of the elongated tube 11 to prevent structural deformation under various operating conditions. The metal coil 30 may be manufactured from stainless steel or other biocompatible metallic materials that provide flexibility while maintaining resistance to kinking, buckling, or collapse. In some cases, the metal coil 30 allows the elongated tube 11 to bend and conform to anatomical pathways without compromising the internal lumen dimensions or interfering with gas flow patterns.

[0110] The metal coil 30 may be embedded within the wall structure of the elongated tube 11 or positioned as a discrete reinforcing layer that maintains the structural integrity of the clearing device 10. In some cases, the metal coil 30 extends from the proximal end toward the distal end 13 of the elongated tube 11, providing consistent structural support throughout the functional length of the clearing device 10. The metal coil 30 may also facilitate smooth insertion and removal of the clearing device 10 by preventing unwanted deformation that could impede movement through anatomical passages.

[0111] The hollow peripheral ring 20 lies in communication with the conduit 16 (not shown in this section) and when pressure and flow of gas 18 is applied, jets 22 of gas 18 are blown out of the ring 20 in the mouth-ward direction (bold arrows) through orifices 21 in the proximal face of the hollow peripheral ring 20. The jets 22 are emitted all around the tube 11 and are sufficiently forceful to sweep away secretions and debris in the airway surface surrounding the tube (not shown) and also entrain the exhaled gas and assist in its evacuation from the lungs.

[0112] The main lumen of the endotracheal tube 11 may end with a diffuser 36 positioned near the distal end 13. The diffuser 36 may direct the flow of the gas out into the airways in multiple directions rather than as a high-velocity concentrated stream. In some cases, the diffuser 36 comprises multiple outlet ports or a specially configured opening that distributes gas flow in a controlled pattern to reduce localized pressure concentrations. In yet another embodiment, the endotracheal tube 11 is reinforced by a metallic coil 30 made from stainless steel or another flexible but not collapsible material. In yet another embodiment, the cuff 12 of the endotracheal tube 11 expands to an inflated configuration 34 that fits snuggly inside the trachea T or a bronchus to occlude it during the inspiratory phase of the ventilation cycle and collapses to the deflated configuration 35 during the expiratory phase of the ventilation cycle. In this configuration the compressed gas 18 supply to the hollow ring 20 and / or the jets 22 is synchronized with the ventilation cycle so that it is active during the exhalation phase, during the inhalation phase, or both. As such the activation of the jets 22 helps evacuate the lungs by entraining the exhaled gas and preventing debris and secretions from entering the lungs when the cuff 12 is deflated.

[0113] Figure 3 shows a longitudinal cut view of a segment of a jet emitting ring 20. The lumen 58 that extends along the endotracheal tube 11 is configured for providing respiratory gas 60 supply to the lungs. The gas supply conduit 16 ends in the gas ring 20 from which the back flow jets 22 are emitted through orifices 21.

[0114] The device 10 may additionally include a pressure monitoring and control unit comprising a pressure monitoring channel 40 that extends along the elongated tube 11 and ends at or proximate the distal end 13 of the tube 11. The pressure monitoring channel 40 may terminate at pressure port 56. Pressure monitoring channel 40 comprises a pressure sensor (not shown) configured to measure and monitor pressure around the distal end 13 of tube 11. In some cases, the pressure port 56 provides a sensing interface that detects pressure variations and transmits pressure information through the pressure monitoring channel 40 to external monitoring equipment. The pressure monitoring channel 40 may function as part of a pressure monitoring and control unit configured to monitor and adjust gas pressure within the clearing device 10 to maintain pressure below 3000 Pascal (Pa), preventing excessive pressure conditions that could cause tissue damage or patient discomfort. Suitable pressure sensors are configured to measure the pressure and convert it into an electrical signal. Exemplary such sensors include piezoelectric sensors, strain gauge sensors, and capacitive sensors. Optionally, the monitoring channel 40 is also configured to measure the level of the CO2 utilizing a capnograph or similar CO2 sensor. When ventilation / respiratory gas 60 is blown into the tube 11, some of the gas 60 exits the tube lumen 58 through cuff aperture(s) 62 to inflate the cuff from its expiratory deflated shape 35 to its inflated shape 34 thereby occluding the airway and preventing the gas from escaping. At the same time, most of the gas is supplied into the airways leading to the lung 52. When the inspiratory pressure is stopped, the elastic cuff 12 collapses from its inflated shape 34 to its deflated shape 35 thereby opening the way for gas 50 to be exhaled between the tube 11 and the walls of the airway (trachea) (not shown in this figure).

[0115] The operational configuration of device 10 enables coordination between respiratory support and debris clearing functions through synchronized gas flow patterns. The gas 18 may flow into the peripheral ring 20 through the conduit 16 in a continuous manner without interruption, providing steady jet formation for consistent debris clearing action. Alternatively, the gas 18 may flow into the peripheral ring 20 in pulses with intermittent delivery, allowing for coordinated timing with respiratory cycles or specific procedural requirements. In some cases, the jets 22 may be emitted from the orifices 21 synchronously with an expiratory phase of a ventilation cycle, directing the jets 22 in an expiratory direction away from the lung 52 to assist natural exhalation processes while clearing accumulated materials.

[0116] When inspiratory pressure from the respiratory gas 60 decreases or stops, the inflatable cuff 12 may contract from the inflated configuration 34 to the deflated configuration 35, creating pathways for exhaled gas 50 to flow between the elongated tube 11 and surrounding anatomical walls. The exhaled gas 50 represents gas that has participated in physiological gas exchange processes within the lung 52 and may carry expelled materials during natural exhalation. The coordination between cuff deflation and jet activation may enhance the clearing effectiveness by allowing the jets 22 to entrain the exhaled gas 50 and assist in directing accumulated secretions and debris away from sensitive anatomical regions. The pressure monitoring channel 40 may continuously monitor these pressure variations to ensure that the coordinated gas flow patterns maintain safe operating parameters throughout the clearing and ventilation processes.

[0117] Figure 4 is a cross section of a portion of device 10 illustrating the lumen 72 of conduit 16 and further comprising a ventilation tube lumen 58 and a lumen 74 of a pressure monitoring channel 40. Suitable diameters (D) of the various elements that fit an adult human subject are shown (DI = 3.0 mm, D2 = 3.5 mm, D3 = 5.0 mm, D4 = 7.2 mm, D5 = D2 = 3.5 mm, D6 = 4.7 mm, D7 = 6.4 mm, D8 = 7.6 mm, and D9 = 4.8 mm). In an exemplary embodiment, the diameter of ventilation tube lumen 58 (D2) is narrow by only 0.5 mm as compared to the diameter of lumen 72 (DI) of conduit 16. Still, various diameters are applicable herein. It should be noted that conduit 16 with ring 20 can be attached to any size endo-tracheal tube or may also be attached to a suction catheter, an airway blocker, a tracheostomy tube, or provided as a standalone independent catheter / tube. A side element extending from the perimeter of the tube outwards 76 but not necessarily encircling the entire circumference of the tube at any position along the tube may be used as an additional platform for emitting the jets 22.

[0118] Figure 5 depicts a schematic illustration of yet another exemplary device 100 for clearing hollow tubular organs from debriss, particles and / or secretions. The clearing device 100 demonstrates an alternative configuration that positions jets emitting components within the internal lumen 158 of the device 100. The clearing device 100 comprises an elongated tube 111 that extends between a distal end and a proximal end, providing a structural framework for internal gas flow management and debris clearing functions. In some cases, the clearing device 100 may be configured for insertion into hollow tubular organs where internal jet formation provides enhanced clearing effectiveness compared to external jet configurations. Device 100 comprises an elongated tube 111 comprising a back-flow jet emitting member in the form of sleeve 120 with apertures, such as orifices 121. Sleeve 120 may be positioned on an inner surface of the elongated tube 111, creating an internal jet emitting member that operates within the confined space of the tubular lumen 158. In some cases, the sleeve 120 functions as an outer bulge surrounding an outer surface of the elongated tube 111, creating a localized expansion that accommodates pressurized gas while maintaining adequate cross-sectional area for primary flow functions.

[0119] Here, orifices 121 are pointing into lumen 158 of tube 111. Orifices 121 are optionally in a tilted orientation, wherein the tilt is pointed towards the airway opening.

[0120] In this configuration, a conduit 116 may optionally be incorporated to the sleeve 120. The conduit 116 may extend along and within the wall 182 of the tube 111 and delivers pressurized gas into the sleeve 120. The upward pointing arrows indicate the jets 122.

[0121] Figure 5B depicts a section AA through the tube 111 wherein the main lumen 158 and the sleeve lumen 172 are shown as integral parts of the tube 111.

[0122] Figure 5C depicts a section BB through the tube 111 wherein the intra-luminal sleeve 120 lines the inner surface of the tube 111.

[0123] Figure 6 depicts yet another exemplary device 200 for clearing hollow tubular organs from debriss, particles and / or secretions. Device 200 comprises an elongated tube 211 with a back-flow jet emitting member with peripheral internal facing bulge 220 with a plurality of apertures, such as orifices 221. Here, orifices 221 are pointing into lumen 258 of tube 211. In this configuration internal back-flow jets 222 are blown into the lumen 258 of the tube 211. In this embodiment respirable gas 218 is blown through thin conduit 216 that extends along and optionally within the wall 282 of the tube 211 and establishes communication pathways for gas delivery to the internal bulge 220. The conduit 216 may be embedded within the tube wall 282 or positioned as a discrete channel that provides dedicated gas flow pathways without interfering with the primary lumen functions of the elongated tube 211. The conduit 216 opens up in a bulge 220 to allow the gas 218 to enter the tube 211 as internal jets 222.

[0124] As further shown in FIG. 6, the internal bulge 220 contains orifices 221 that may be positioned to direct gas flow into a tube lumen 258 of the elongated tube 211. The orifices 221 create internal jets 222. In some cases, the orifices 221 may have a conical shape comprising a narrow part facing inward toward the tube lumen 258 or outward toward the internal bulge 220, creating flow characteristics that optimize jet formation and debris entrainment capabilities. The orifices 221 may alternatively comprise a cylindrical shape that provides consistent flow patterns.

[0125] With continued reference to FIG. 6, respirable gas 218 flows through the conduit 216 and enters the internal bulge 220 to enable formation of the internal jets 222 through the orifices 221.

[0126] Figure 7 depicts another exemplary device 300 for clearing hollow tubular organs from debriss, particles and / or secretions. Device 300 is configured as a suction catheter 350. The clearing device 300 enables simultaneous operation of pressurized gas delivery and negative pressure suction to achieve enhanced clearing effectiveness compared to single-function approaches. The device 300 comprises an elongated tube 311 configured to connect to a vacuum source at a proximal end thereof (not shown) creating a negative pressure and flow 138 to draw secretions from the lung airways 136 into the suction catheter 350. Secretions and debris 126 that are not too viscous can be sucked into the catheter 350. At the same time compressed respirable gas 318 is blown into conduit 316 that is in fluid communication with a jet emitting member in the form of an external bulge 320 that surrounds an outer periphery of the elongated tube 31 land functions as a jet emitting member. Hollow bulge 320 is attached to catheter 350 and surrounds an outer periphery thereof. The compressed gas 318 then emerges as jets 322 through orifices 321 positioned on the top surface of bulge 320. In this configuration the orifices 321 are facing outward in the direction of the airway opening. The jets 322 have sufficient pressure and kinetic energy to disengage the secretions 126 from the airway walls and push them out of the lungs.

[0127] The external bulge 320 may be attached to the suction catheter 350 through mechanical connections or integrated manufacturing processes that maintain structural integrity while allowing independent operation of gas delivery and suction systems. In some cases, the external bulge 320 comprises a hollow chamber that accommodates pressurized gas and provides a platform for controlled gas distribution around the perimeter of the suction catheter 350.

[0128] The orifices 321 may be positioned on a top surface of the external bulge 320 and oriented to direct gas flow outward in a direction away from the lungs. The orifices 321 face outward toward anatomical openings and create gas jets 322 that emerge with sufficient pressure and kinetic energy to disengage the secretions 126 from airway walls and push accumulated materials away from the lung airways 136. In some cases, the orifices 321 may be arranged in circular patterns or linear configurations that optimize gas distribution around the perimeter of the suction catheter 350 while maintaining adequate spacing to prevent interference between adjacent gas jets 322.

[0129] Compressed gas 318 flows through a gas conduit 316 that establishes fluid communication between external gas sources and the external bulge 320 of the clearing device 300. The gas conduit 316 may extend along the outer surface of the elongated tube 311 or may be embedded within the wall structure of the suction catheter 350.

[0130] The operational configuration of the clearing device 300 enables simultaneous operation of debris mobilization and active removal functions through coordinated timing of gas delivery and suction activation. The gas jets 322 may operate continuously to provide steady debris clearing action while the negative flow 138 maintains consistent material removal from the lung airways 136. Alternatively, the compressed gas 318 delivery may be synchronized with suction cycles to optimize the interaction between debris mobilization and removal processes. In some cases, the gas jets 322 may be activated during specific phases of suction operation to enhance the effectiveness of material entrainment and transport through the elongated tube 311 toward external collection systems.

[0131] Figures 8A-8C depict yet another exemplary device 500 comprising jets emitting member featuring a rotary member 520. In this configuration, the force of the jets 522 expelled from apertures, as orifices 521 at the top surface of the rotating member 520 facilitate rotation of the rotary member 520 in an opposite / reverse direction of the jets 522 due to the momentum exchange between the jet and the rotating element. The clearing device 500 may be configured to provide continuous or intermittent rotational movement that creates varying flow patterns. In some cases, the clearing device 500 enables enhanced debris mobilization through the combination of pressurized gas delivery and rotational motion that may dislodge adherent materials effectively.

[0132] Rotary member 520 may be positioned around the perimeter of the elongated tuber 511 and configured to rotate during operational procedures. The rotary member 520 functions as a jets emitting member that combines gas flow capabilities with mechanical movement to create dynamic clearing patterns within the anatomical environment. The rotary member 520 may be supported through bearing systems or flexible mounting arrangements that enable smooth rotational movement without compromising the structural integrity of the clearing device 500 or interfering with primary tubular functions.

[0133] As further shown in Figs. 8A-8C, the rotary member 520 contains orifices 521 that may be positioned on a top surface of the rotary member 520 and oriented to direct gas flow in specific patterns that facilitate debris clearing and optionally rotational movement. The orifices 521 create gas jets 522 that emerge from the rotary member 520 with controlled velocity and pressure characteristics that mobilize accumulated materials while generating reactive forces that contribute to the rotational motion of the rotary member 520.

[0134] The gas jets 522 emerge from the orifices 521 with sufficient pressure and kinetic energy to create momentum exchange interactions with the rotary member 520 that facilitate rotational movement in a direction opposite to the gas jets 522 due to conservation of momentum principles.

[0135] With continued reference to Figs. 8A-8C, the operational configuration of the clearing device 500 enables the rotary member 520 to function as a rotary peripheral element that rotates during operation through the momentum exchange forces generated by the gas jets 522. The rotational motion may be continuous during gas delivery or may occur in intermittent cycles that coordinate with other operational functions of the clearing device 500. The momentum exchange mechanism enables self-sustaining rotational movement that operates independently of external mechanical systems while providing enhanced clearing capabilities through the combination of pressurized gas flow and dynamic mechanical motion.

[0136] Referring to FIG. 9A - 9C, a further exemplary clearing device 600 is demonstrated. The device 600 demonstrates comprehensive debris clearing capabilities that coordinate gas delivery functions. The clearing device 600 may be configured to provide debris removal from hollow tubular organs while maintaining coordinated control over gas flow parameters and jet formation processes. The clearing device 600 incorporates an elongated tube 611 that may feature an endotracheal / tracheostomy tube or catheter that extends between a distal end 613 and a proximal end 633. The clearing device 600 includes a gas conduit 616 that establishes communication pathways between external gas sources and internal distribution components within the elongated tube 611. The gas conduit 616 may extend along the length of the elongated tube 611 and provide dedicated channel for pressurized gas delivery that operate under controlled flow and pressure parameters. In some cases, conduit 616 maintains sufficient cross-sectional area to accommodate required gas flow rates. Conduit 616 may be coupled to the elongated tube 611 and positioned as discrete channel that provides isolated gas flow pathways without interfering with other functional systems within the tubular assembly.

[0137] The clearing device 600 incorporates a jet emitting member in the form of a sleeve 620 that may be positioned around a portion of the elongated tube 611 from the outside and configured to direct gas flow through strategically positioned outlets, i.e., a peripheral slit 623. The jet emitting member in the form of a sleeve 620 functions as a controlled distribution platform that surrounds the elongated tube 611 and receives gas flow 618 from the gas conduit 616 and creates localized pressure conditions that enable jet formation through one or more designated aperture(s) 621, optionally covered with an elastic cover (not shown). In some cases, sleeve 620 may be configured as an expandable chamber that accommodates varying gas volumes while maintaining consistent pressure relationships throughout the operational cycle. Sleeve 620 may be manufactured from materials that provide adequate structural support for gas containment while enabling controlled expansion and contraction in response to internal pressure variations and external operational conditions.

[0138] With continued reference to FIG. 9 A - 9C, the gas 618 flow path represents the controlled movement of pressurized gas through the gas conduit 616 toward orifice 621, into sleeve 620, and then emerges out as jet(s) 622 through slit 623. The gas flow 618 accumulates under monitored pressure conditions before emerging through the orifice 621 , and then through slit 623. The gas flow 618 may be managed through automated control systems that adjust flow rates and pressure parameters based on feedback from monitoring components within the clearing device 600. In some cases, the gas flow 618 operates under continuous surveillance that enables real-time adjustments to maintain optimal jet formation characteristics while preventing excessive pressure conditions that could compromise patient safety or procedural effectiveness. The gas flow 618 may be delivered in a continuous manner. The gas flow 618 may be delivered in intermittent pulses that coordinate with respiratory cycles or specific procedural requirements to optimize debris clearing effectiveness while maintaining controlled operational parameters. The distal end 613 of conduit 616 may terminate with a conduit aperture, i.e., orifice 621 that converts the accumulated gas flow 618 within the gas conduit 616 into high-velocity jet 622 that emerges through an aperture, being slit 623 with sufficient kinetic energy to mobilize accumulated materials within the anatomical environment. In some cases, the orifice 621 may be configured with specific diameter relationships and spacing patterns that optimize jet formation. The orifice 621 may have diameters between 0.2 to 2 millimeters and may be arranged in circular or linear configurations. In some cases, the slit 623 may be configured with specific diameter relationships and spacing patterns that optimize jet formation. The slit 623 may have diameters between 0.2 to 2 millimeters and may be arranged in circular or linear configurations.

[0139] As further shown in FIG. 9 A and FIG. 9B, gas 618 emerges from the orifice 621 and disperses through the cavity formed between the inner surface of sleeve 620 and the outer wall of the elongated tube 611. The dispersed gas then emerges as one or more jet(s) 622 through a peripheral slit 623 present between the proximal open end of the sleeve 620 and the elongated tube 611. Slit 623 is directed toward the proximal end of device 600. In some cases, the peripheral slit 623 may provide a continuous circumferential opening that enables uniform gas distribution around the perimeter of the elongated tube 611.

[0140] The device 600 may incorporate one conduit. Optionally, the device may include multiple conduit 616 configurations that enhance gas delivery capabilities through distributed flow pathways. In some cases, the elongated tube 611 may include two or more conduits 616 wherein each conduit comprises at least one aperture such as orifice 621 that provides independent gas delivery point. The conduit(s) 616 may be integrated into the elongated tube 611 structure through various manufacturing approaches. In some cases, the conduits 616 may be embedded within the wall structure of the elongated tube 611, creating integral channels that maintain the structural integrity of the tubular assembly while providing dedicated gas flow pathways. Alternatively, the conduits 616 may be configured as added channels that extend along the longitudinal axis from the outer or inner surface of the elongated tube 611, providing gas delivery pathways that may be attached or integrated after primary tube manufacturing. Each conduit terminates with an aperture, such as orifice 621 that may be positioned at strategic locations along the elongated tube 611.

[0141] The jet 622 may operate at flow velocities between 1 to 100 meters per second, providing adequate kinetic energy for material entrainment and debris clearing while preventing excessive pressure concentrations that could cause tissue damage or patient discomfort. The jet 622 may operate continuously during gas delivery cycles or may be activated in coordinated patterns that synchronize with respiratory cycles to optimize clearing effectiveness.

[0142] The gas flow 618 may be delivered at pressures between 200 to 4000 millibars and flow rates between 50 to 500 milliliters per second. In some cases, the clearing device 600 may incorporate automated feedback mechanisms that adjust the gas flow 618 parameters based on real-time pressure measurements within the anatomical environment. The coordinated operation of monitoring and control functions enables the clearing device 600 to maintain optimal performance while providing safety oversight that prevents excessive pressure conditions and ensures appropriate operational parameters throughout the gas delivery and jet formation processes.

[0143] FIG. 9C is a cross-sectional view of the clearing device 600. The elongated tube 611 incorporates a tube lumen 658 configured for respiratory gas delivery and / or other medical applications.

[0144] The clearing device 600 may incorporate an inflatable cuff 612 that synchronizes with the respiratory cycles and moves between an inflated configuration at the inhaling phase and a deflated configuration at the exhaling phase of the respiratory cycle of a subject. The inflatable cuff 612 may be positioned near the distal end 613 of the elongated tube 611. Sleeve 620 is positioned proximally to inflatable cuff 612, creating jets toward the proximal direction of the device 600. One or more cuff apertures 662 extend from lumen 658, such to inflate the cuff 612 when respiratory gas flows within lumen 658. In the exhaling phase, the gas is withdrawn from the cuff, deflating the cuff 612.

[0145] During the inhalation phase, the inflatable cuff 612 may expand through gas flown via cuff apertures 662 to create a seal that blocks the airway distal to the cuff position, preventing gas flow beyond the cuff location. Optionally, the gas flow through conduit 618 and jets 622 formation is synchronized with the inhalation phase, providing clearing capabilities during this respiratory phase.

[0146] During the exhalation phase, the inflatable cuff 612 may deflate to allow natural expiratory flow around the exterior of the elongated tube 611. Optionally, the gas flow through conduit 618 and jets 622 formation is synchronized with the exhalation phase, creating additional flow pathways that may enhance the overall clearing effectiveness through coordinated interaction between natural expiratory flow and directed jet streams 622.

[0147] A continuous operation of jets 622 is optionally provided during the entire respiratory cycle, i.e., jet streams 622 are formed during both the exhalation and inhalation phases providing continuous clearing pathways throughout the entire respiratory cycle, enabling sustained debris mobilization.

[0148] This configuration advantageously enables continuous jet formation and clearing pathways during both inhalation and exhalation phases, providing comprehensive debris management that operates independently of respiratory cycle variations.

[0149] Figure 10 is a block diagram of a pressure monitoring and control unit of the herein system. Pressure is sensed at or near the distal opening of an elongated tube 1042 and transmitted through a narrow channel 1044 running along the tube to a pressure sensing transducer 1046. The analogue or digital representation of the pressure signal is amplified 1048 and the instantaneous value is fed into a comparator 1050 that compares the actual value to the desired set value dialled in by a P-Set dial 1052. The comparator 1050 is then outputs a signal into the flow control 1054 to either increase the flow 1056 or decrease it or even stop it completely if the pressure level is reaching a dangerously high level. As such, the intra-airway pressure at the airway opening 1042 can be servo-controlled to be within narrow pre-set boundary. This pressure can be above atmospheric also known as Positive End Expiratory Pressure or PEEP or sub-atmospheric also known as Continuous Negative Airway Pressure or CNAP. The latter has beneficial effects during cardiopulmonary resuscitation (CPR) whereby it enhances venous return of blood to the chest and the heart.

[0150] DEFINITIONS

[0151] As used herein the terms ‘a’ and ‘an’ may mean ‘one’ or ‘more than one’.

[0152] As used herein the terms ‘comprising’, ‘including’, ‘containing’, ‘featuring’, ‘having’ and any forms of the terms thereof are inclusive and open ended and do not exclude additional elements or method steps, which are not recited.

[0153] The term 'consisting essentially of’ as used herein means that the scope is limited to the specified elements and those that do not materially affect the basic and novel characteristic(s) of the claimed device and materials.

[0154] Each of the phrases 'consisting of and 'consists of, as used herein, means 'including and limited to'.

[0155] The term 'method', as used herein, refers to steps, procedures, manners, means, or / and techniques, for accomplishing a given task including, but not limited to, those steps, procedures, manners, means, or / and techniques, either known to, or readily developed from known steps, procedures, manners, means, or / and techniques, by practitioners in the relevant field(s) of the disclosed invention. Throughout this disclosure, a numerical value of a parameter, feature, characteristic, object, or dimension, may be stated or described in terms of a numerical range format. Such a numerical range format, as used herein, illustrates implementation of some exemplary embodiments of the invention, and does not inflexibly limit the scope of the exemplary embodiments of the invention. Accordingly, a stated or described numerical range also refers to, and encompasses, all possible sub-ranges and individual numerical values (where a numerical value may be expressed as a whole, integral, or fractional number) within that stated or described numerical range. For example, a stated or described numerical range 'from 1 to 6' also refers to, and encompasses, all possible sub-ranges, such as 'from 1 to 3', 'from 1 to 4', 'from 1 to 5', 'from 2 to 4', 'from 2 to 6', 'from 3 to 6', etc., and individual numerical values, such as T, '1.3', '2', '2.8', '3', '3.5', '4', '4.6', '5', '5.2', and '6', within the stated or described numerical range of 'from 1 to 6'. This applies regardless of the numerical breadth, extent, or size, of the stated or described numerical range. All ranges disclosed herein include the endpoints. The use of the term “or” shall be construed to mean “and / or” unless the specific context indicates otherwise.

[0156] The term 'about', in some embodiments, refers to ±30 % of the stated numerical value. In further embodiments, the term refers to ±20 % of the stated numerical value. In yet further embodiments, the term refers to ±10 % of the stated numerical value.

Claims

CLAIMS1. A device for clearing hollow tubular organs from debris, particles and / or secretions, the device comprising a gas source configured to accommodate compressed gas; an elongated tube extending between a distal end and a proximal end; a jet emitting member connected to said elongated tube; a conduit in fluid communication with said jet emitting member configured to convey said gas from said gas source and into said jet emitting member, wherein said jet emitting member comprising at least one aperture positioned to direct gas flow toward the proximal end of said elongated tube and configured to form at least one jet emitting gas in a proximal direction of said device, when said gas fills said jet emitting member.

2. The device of claim 2, wherein the device is a ventilation device and the elongated tube is an endotracheal tube, and wherein the conduit is configured to provide gas into the jet emitting member in a direction of the lung airways and the aperture is positioned in an opposite direction relative to the lung to generate at least one jet emitted essentially in an expiratory direction, away from lungs of the subject.

3. The device of any one of the preceding claims, wherein said gas is a respirable gas.

4. The device of claim 2, wherein said at least one jet has kinetic energy sufficient to entrain additional gas from the surrounding environment and lower the pressure in the airways and lungs.

5. The device of claim 2, wherein said at least one jet is capable for preventing debris and secretions from entering the lungs and said at least one jet is directed to expel debris and secretions from the airway lumen and walls, away from the lungs.

6. The device of any one of the preceding claims, further comprising a pressure monitoring and control unit comprising a pressure sensor configured to monitor and adjust gas pressure within the device and / or its surrounding to maintain pressure below 3000 Pa.

7. The device of any one of the preceding claims, wherein the elongated tube is configured as a catheter.

8. The device of any one of the preceding claims, wherein the conduit is embedded within a wall of the elongated tube or positioned as a separate channel that extends along the outer and / or inner wall of the elongated tube.

9. The device of any one of the preceding claims, wherein the elongated tube is configured as a suction catheter.

10. The device of any one of the preceding claims, wherein said elongated tube is configured as a bronchial blocker catheter.

11. The device of any one of the preceding claims, wherein the conduit conveying said gas is configured as a visualization catheter (bronchoscope).

12. The device of any one of the preceding claims, wherein the jet emitting member is configured as a sleeve connected to elongated tube at a distal end of said sleeve and positioned around a portion of an outer surface of the elongated tube, wherein the conduit comprises at least one conduit aperture that delivers gas through the conduit such that it is emitted to a cavity formed between the sleeve and the elongated tube, wherein said aperture in the form of a peripheral slit is present between the proximal end of the sleeve and the elongated tube, wherein gas delivered through the conduit is emitted to the sleeve through said conduit aperture and is dispersed to form said one or more jet(s) in a proximal direction through the peripheral slit.

13. The device of any one of the preceding claims, wherein said jet emitting member is disposed to encircle an outer surface of said elongated tube and said at least one aperture is disposed on a proximal top surface of said jet emitting member.

14. The device of claim 13, wherein said at least one aperture is located sequentially along the top proximal surface of said jet emitting member.

15. The device of any one of the preceding claims, wherein said jet emitting member is disposed internally and surrounds an inner surface of said elongated tube and said at least one aperture is located internally inside the lumen of said tube.

16. The device of any one of the preceding claims, wherein said gas flows into said jet emitting member in a continuous manner.

17. The device of any one of the preceding claims, wherein said gas flows into said jet emitting member in pulses.

18. The device of any one of the preceding claims, wherein said elongated tube is an endotracheal tube, and said jet is emitted from said at least one aperture synchronously with the expiratory phase of a ventilation cycle.

19. The device of any one of the preceding claims, wherein said elongated tube is an endotracheal tube, and said jet is emitted from said at least one aperture synchronously with the inspiratory phase of ventilation cycle.

20. The device of any one of the preceding claims, wherein a distal end of said conduit or elongated tube is connected to a pressure sensor.

21. The device of claim 6, further comprising an alarm, wherein when the pressure detected by said pressure sensor exceeds a pressure value ranging between 2000 Pa and 3000 Pa, an alarm signal is triggered by said alarm.

22. The device of claim 6, wherein when the pressure detected by said pressure sensor exceeds a pressure value of 3000 Pa- 5000 Pa, an instantaneous flow of said gas is halted.

23. The device of any one of the preceding claims, wherein the number of apertures is between 1 and 8.

24. The device of any one of the preceding claims, wherein the number of apertures is between 3 and 8.

25. The device of any one of the preceding claims, wherein the number of apertures is up to two.

26. The device of any one of the preceding claims, wherein the number of apertures is greater than 8.

27. The device of any one of the preceding claims, wherein the jet emitting member is configured as a sleeve positioned on an inner or outer surface of the hollow tube.

28. The device of any one of the preceding claims, wherein the jet emitting member is configured as a protruding ring positioned on an inner or outer surface of the hollow tube.

29. The device of any one of the preceding claims, wherein the elongated tube comprises an inflatable cuff that is moveable between an inflated configuration and a deflated configuration, the inflatable cuff positioned near the distal end of the elongated tube and the jet emitting member is positioned proximally to the inflatable cuff, wherein the inflated configuration holds the tube steadily within the tubular organ.

30. The device of claim 29, wherein the cuff is inflated and deflated intermittently, optionally in synchronization with pulses of the pressurized gas emitted from the jet emitting member.

31. The device of any one of the preceding claims, wherein the gas source provides an intermittent flow of the pressurized gas, each period of flow lasting between 0.2 to 10 seconds and each interval between flow pulses lasting between 0.2 to 20 seconds.

32. The device of claim 31, wherein the intermittent flow of the pressurized gas is synchronized with a specific phase of a ventilation cycle, the specific phase being at least one of an expiratory phase, an inspiratory phase, or a portion thereof.

33. The device of any one of the preceding claims, wherein the jets have a flow velocity between 1 to 100 m / s.

34. The device of any one of the preceding claims, wherein the at least one aperture comprises between 5 and 25 apertures arranged in a circle on the jet emitting member.

35. device of any one of the preceding claims, wherein of the at least one aperture has a diameter between 0.2 and 2 mm.

36. The device of any one of the preceding claims, wherein the pressure of the pressurized gas entering the tube or conduit is between 200 to 4000 millibars.

37. The device of any one of the preceding claims, wherein the flow rate of the pressurized gas entering the tube or conduit is between 50 to 500 milliliters per second.

38. A method for clearing debris and secretions from a hollow organ, comprising: providing a hollow tube extending between a distal end and a proximal end, the hollow tube comprising a jet emitting member and a conduit in fluid communication with the jet emitting member and a gas source, the jet emitting member comprising at least one aperture pointing generally towards an opening of the hollow organ; flowing a pressurized gas through the conduit and into the jet emitting member; and emitting at least one jet from the at least one aperture in a direction of the opening of the hollow organ, the at least one jet entraining fluid to assist fluid movement and push debris and secretions outward.

39. A method of injecting jets of compressed respirable gas inside a lung airway in the outward direction, the method comprising providing a ventilation device comprising an endotracheal tube extending between a distal end and a proximal end, the endotracheal tube comprising a jet emitting member and a conduit in fluid communication with the jet emitting member and a gas source comprising pressurized gas, wherein said jet emitting member comprises at least one aperture facing a proximal end of the endotracheal tube; inserting the endotracheal tube into a trachea of a subject in need thereof; connecting the conduit of said endotracheal tube to the gas source; and flowing a pressurized gas through said conduit and into said jet emitting member; and forming at least one jet emitting said gas in the proximal direction of said device when said gas fills said jet emitting member.

40. A method for outwards clearing of debris and secretions from a lung airway, comprising providing a hollow tube extending between a distal end and a proximal end, the hollow tube comprising a jet emitting member, and a conduit in a fluid communication with said jet emitting member and a gas source, the jet emitting member comprising at least one aperture pointing generally towards an opening of the lung airway; flowing a pressurized gas through the conduit and into said jet emitting member; and emitting at least one jet from the at least one aperture in a direction of the opening of the lung airway, the jet entraining exhaled air to assist exhalation, and push debris and secretions outward.

41. The method of any one of claims 38-40, wherein the hollow organ is selected from the group consisting of airways, gastrointestinal tract, urinary tract, and bile ducts.

42. The method of any one of claims 38-40, wherein the step of flowing a pressurized gas is synchronized with a subject's respiration such that the at least one jet is emitted during an expiratory phase of a ventilation cycle.

43. The method of claim 38, wherein the hollow tube is an endotracheal tube, a suction catheter, or a bronchial blocker catheter.

44. A system for clearing hollow tubular organs from debris, particles and secretions, comprising: a gas source configured to accommodate compressed gas; an elongated hollow tube extending between a distal end and a proximal end; a jet emitting member associated with the elongated hollow tube; a conduit in communication with the jets emitting member and configured to convey the gas from the gas source into the jets emitting member; and at least one orifice in the jets emitting member oriented to direct gas flow toward the proximal end of the elongated hollow tube and configured to form at least one jet emitting the gas in a proximal direction when the gas fills the jets emitting member.

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