METHOD AND APPARATUS FOR PREVENTION OF CATHETER AIR INTAKE

Abstract

A system for preventing air from entering a first catheter of a multi-catheter system. Air is prevented from entering the proximal end of the first catheter by an axially elongate chamber having an impeller, the chamber being affixed to the proximal end of the first catheter. The air is removed through a port near the centerline of the chamber. Liquid removed with the air is returned to the chamber to minimize liquid loss during the procedure. A second catheter inserted through the chamber and into the first catheter is unable to entrain gas into the first catheter because any gas that enters the chamber is routed to the centerline of the chamber where it is removed. Inflow of fluid from an external pump scrubs the second catheter shaft of air bubbles attached by surface tension.

Description

FIELD OF THE INVENTION

The field of this invention is cardiology, radiology, electrophysiology, or endovascular surgery, and more particularly the fields of cardiac or circulatory system catheterization.

BACKGROUND OF THE INVENTION

Catheters are introduced into the cardiovascular system for various diagnostic and therapeutic reasons. Catheters are often introduced into the cardiovascular system through introduction sheaths that provide a pre-determined conduit from the access site to the treatment site and facilitate vascular access of new catheters as well as the exchange of catheters within the vasculature. Such catheters and introducer sheaths are used in both the arterial, higher pressure, circulation and the venous, lower pressure, circulation. Introducer sheaths suitable for guiding devices through the vasculature and into the right or left atrium of the heart are prime examples of such vascular access.

The introducer sheaths and catheters used for these purposes are generally primed with saline and purged of any air prior to being inserted into the patient's cardiovascular system through a percutaneous or open surgical access to an artery or vein. The purpose of purging air from a catheter or introducer sheath is to prevent that air from inadvertently being forced, under a pressure drop generated within the catheter or sheath, out the distal end of the catheter and into the patient's circulatory system.

The act of inserting a therapeutic or diagnostic catheter through an introducer sheath can cause air or other gas to be introduced into the central lumen of the introducer sheath. Such air can migrate distally into the patient's cardiovascular system under certain circumstances, especially when the distal end of the introducer sheath is located within the venous side of the cardiovascular system or in the left atrium of the heart. In certain pathological and physiological states, relatively low pressures can exist within the venous side of the heart with a pressure gradient existing between the right and left atrium. Such gradients in the presence of a Patent Foramen Ovale (PFO), a not uncommon congenital cardiac condition, can easily result in air emboli traversing from the right heart to the left heart during right heart interventional procedures. In addition, these relatively low pressures can exist for a non-trivial portion of the cardiac cycle resulting in the potential for a negative pressure gradient between the room pressure, which in a clean room, catheterization lab, or surgical suite is generally slightly elevated, and the distal end of the introduction sheath. There is a potential for any gas or air entrained into the proximal end of the introduction sheath to migrate out the distal end of the introduction sheath and into the patient's cardiovascular system where it could cause an air embolism. During a portion of the cardiac cycle, pressures within the left atrium can approach very low values and can even go negative relative to room pressure.

The clinical ramifications of an air embolism range from no noticeable effect to cerebrovascular stroke or cardiac ischemia, either of which could have mild to severe outcomes and could even result in patient death. Air can also be entrained out the distal end of the sheath by surface tension forces between the catheter and the air. This surface tension can cause the air to adhere to the catheter while it is advanced out the distal end of the sheath. Thus, any air that inadvertently enters the sheath or catheter system is at risk for introduction to the patient, an event with potentially catastrophic consequences such as cerebrovascular embolism, coronary embolism, and the like. Air embolism is clearly an issue especially with catheters directed toward the cerebrovasculature or the coronary circulation, but also with catheters or sheaths directed anywhere within the circulatory system of the mammalian patient.

New devices and methods are needed to more efficiently remove gas that inadvertently migrates into a catheter or sheath so that it is prevented from being routed into the patient's cardiovascular system. The need has been heightened by recent Medicare regulations that restrict or deny reimbursement for certain hospital acquired conditions including air embolism.

SUMMARY OF THE INVENTIONS

This invention relates to a blood filter, blood-air filter, or trap for removing air or other gas from the fluid within a primed introducer sheath, catheter, or similar device placed anywhere within the cardiovascular circuit of a patient. The liquid fluid within a cardiovascular catheter or sheath can comprise blood, blood products, water, sodium chloride, various pharmacologic agents, and the like. In some embodiments of the inventions, the device or apparatus comprises a chamber or housing with a catheter inlet port and a catheter outlet port, the catheter outlet port being connected to the proximal end of an introduction sheath, or first catheter. In addition, the chamber has a third outlet port for removing gas from the liquid. The device additionally comprises a stirring rod or impeller to spin the blood circumferentially within the chamber. This stirring rod or impeller is coupled to a rotary motor that generates the rotational energy necessary to separate gas from the blood by buoyancy, or centripetal effects. The less dense bubbles move toward the center of the rotating fluid field while the more dense liquid is moved to the periphery of the rotating fluid field. The faster the fluid field rotates, the more quickly the air is separated from the liquid. The present inventions actively remove gas and debris from the catheter, including both tiny gas bubbles and large boluses of gas. The inventions can strip gas or air bubbles, attracted to a secondary catheter inserted through the chamber by surface tension effects or similar forces, away from the secondary catheter and into a rotational flow field where the gas can be actively removed from the chamber. The gas has less mass than the same volume of blood or saline, i.e. the bubbles are buoyant in the liquid, so that rotation causes them to move toward the center of the liquid filter by centripetal force. The centripetal force accelerates the gas until the bubbles reach an axially inward radial velocity where the drag force balances the centrifugal force and the bubbles move toward the center of rotation of the device.

In some embodiments, the invention actively rotates the blood or other liquid within a chamber to drive gas toward the center of the chamber under centrifugal forces interacting with buoyant forces on the gas, and allows separation of the blood or other liquid from the aforementioned gas. The gas is removed from the chamber of the device through a gas vent, approximately aligned with the axis of rotation, where the air is stored in a gas reservoir, while any liquid is pumped back into the chamber of the device. The gas trap or filter of the present invention is designed to remove the majority of air bubbles and prevent those air bubbles from entering or escaping the distal end of the catheter or sheath.

In some embodiments, the axis of the chamber, and the axis about which the impeller rotates, is aligned parallel to the longitudinal axis of the catheter or sheath to which it is affixed. In another embodiment, the chamber is aligned with its rotational axis lateral to that of the catheter major axis. In this embodiment, rotational fluid flow is less restricted by the presence of a catheter being inserted along the longitudinal axis of the sheath because the inserted catheter, which passes through the chamber is aligned generally in the direction of the rotational fluid flow and not transverse thereto.

In other embodiments, the chamber does not comprise an impeller but the chamber comprises an inlet seal or valve that separates the chamber from the outside environment, an optional outlet seal or valve that separates the chamber from the distal end of the first catheter or sheath, an outlet port for air and a return port for liquids. The inlet seal or valve and the outlet seal or valve serve to trap any air within the chamber so that the air cannot pass into the proximal end of the sheath or catheter through the outlet valve or seal. The chamber further comprises an external fluid pump, air reservoir, return line, and electrical power source.

In some embodiments, a filter is described that is affixed or integral to the proximal end of an introducer or introduction sheath. The filter is completely self-contained, small, and non-bulky. The filter, including all components, can be contained or integrated within a shell. The filter, including all components, can be contained either within a shell or within modules directly affixed to the shell. In certain embodiments, the filter is a unitary or integral structure with no wires, lines, tubes, or other flexible linkages extending therefrom. The filter system does not require a hanging bag or reservoir of saline or other liquid since it gets its fluid from the catheter itself. The filter is capable of being maneuvered at the proximal end of the sheath and allows therapeutic or diagnostic catheters to be passed therethrough on their way into the sheath or introducer. Thus, all components or modules are integral to, or affixed to, the filter unit. The components or modules can all be integrated within or housed within a single shell, casing. This is extremely important so that the filter assembly does not render the sheath or catheter system unwieldy, awkward, or unbalanced. In certain embodiments, the chamber, the return line, the air separation chamber, the pump, the pump motor, the battery, any inlet and outlet valves, and all interconnecting components are integral to or affixed to each other. The components can be rigidly or flexibly affixed to each other. The battery can comprise chemistries such as, but not limited to, alkaline, lithium, lithium ion, nickel metal hydride, lead acid, and the like. Battery operating voltages can range between 1.25 and 12 volts with a preferred range of between 3 and 7 volts. Computers, controllers, and other circuitry can be used to monitor motor function, presence of gas via ultrasound transducers, battery power, and the like. The controllers can further comprise circuitry, software, or both to process the information and provide warnings to the user.

In accordance with another aspect of the invention, a method is described to remove gas from an axially elongate chamber affixed to the proximal end of an introducer, first catheter, or introduction sheath. This method includes the step of affixing the chamber to the proximal end of the first catheter or sheath such that the first catheter or sheath is connected near the radial periphery of the chamber. Next the method includes spinning the fluid, blood, saline, air, and the like, within the chamber about a central axis by means of an impeller at high rotational rates to move the gas to the center, or axis of rotation, of the chamber and away from the first catheter or sheath port to a gas removal port located generally near the axis of rotation within the chamber where the gas is removed. In a further aspect of the invention, the air or gas removed from the fluid at or near the center of the chamber is separated from the liquid in an external gas separation chamber and the liquid is ultimately returned to the chamber or the patient. In an embodiment, the same impeller that spins the blood within the chamber can be used to pump the liquid back into the chamber. In another embodiment, a separate impeller or pump can be used to move the liquid back into the chamber. In another embodiment, the same motor but different impellers or pumping devices can be used to spin the blood and move the blood through the system.

In other embodiments, the chamber is configured so that fluid, blood, air, non-cellular prime, or the like, are pumped out of the chamber where the air is separated from the liquid, and the liquid is returned to the chamber. In yet another embodiment, entry and exit valves are provided at the proximal and distal end of the chamber. These entry and exit valves minimize the amount of fluid, either air or liquid that can escape therethrough, with or without a secondary catheter having been passed through these valves. In some embodiments, the return line to the chamber is aligned tangentially to the circumference of the chamber such that the return flow generates rotational flow within the chamber that strips air from a secondary catheter inserted therethrough and drives the air toward the center of the chamber where it is drawn off. In some of these embodiments, the chamber is aligned with its axis of rotation vertical so that the air or gas directed toward the center can rise and be removed out the exit vent from the chamber. In some embodiments, the top of the generally cylindrical chamber can have a domed, funnel, or otherwise tapered shape to coerce gas and air toward the center, where the fluid exit from the chamber is located.

The present inventions distinguish over the cited prior art because they use an active component, or tangential return flow jet, to spin the liquid to forcibly remove gas and gas bubbles from the blood, catheter prime, saline, or other liquid. The invention is most useful during endovascular surgery, interventional neuroradiology procedures, interventional cardiology procedures, electrophysiology procedures, and the like. The invention does not block air from entering a bubble filter chamber by application of high pressure but rather quickly removes air entrained into the chamber away from the catheter where it can be pulled off and separated from any liquid, thus allowing the air-free liquid to be returned to the system. The system also has the advantage, due to the high rotational velocity of the liquid within the chamber, of being able to scrub any air away from a second catheter inserted through the chamber, wherein the air is adherent to the catheter by surface tension effects.

In another embodiment of the invention, an ultrasound transducer is affixed to the chamber and the ultrasound transducer is connected to control circuitry such that the presence of air can be detected and a warning device such as an audible bell, buzzer, a visible light or warning device, or the like can be activated to alert the operator that air is within the system and that caution should be maintained or corrective steps applied. The ultrasound transducer can be made to monitor the chamber inlet, the chamber, outlet, or both such that, in an embodiment, the warning signal only occurs if air nears the outlet of the chamber, where it could potentially pass into the first catheter or sheath. Once the gas or air is detected, system checks can be performed to prevent any flushing of fluid and air, within a guide sheath and/or catheter, into the patient.

In other embodiments of the invention, the system is self-priming and withdraws liquid retrograde through the sheath and into the bubble filter such that it does not require a separate source of liquid or fluid. Such separate sources of liquid or fluid, which are not required for the present device or method, can include bags or reservoirs of fluid hung beside the patient. In some embodiments, the system comprises a valve at its proximal end but not at its distal end. In other embodiments, the system comprises a valve at both the proximal end and the distal end. The valve can be a hemostasis valve of the type including, but not limited to, a duckbill valve, a pinhole valve, a slit valve, a Tuohy-Borst valve, and the like. Any valves located at the distal end of the bubble filter are preferably able to permit retrograde flow therethrough, even with a secondary catheter inserted therethrough. Such retrograde flow capability facilitates priming of the filter with blood withdrawn from the patient. Any valves located at the proximal end of the bubble or air filter preferably seal both in the antegrade and retrograde directions.

In other embodiments, an external bubble collection system is provided outside the bubble or air filter. Air removed from the air or bubble filter main chamber, through which the secondary catheter passes, is moved through the external bubble collection system. The external bubble collection system can comprise a mesh filter having a pore size of about 25 microns and can further comprise a gravity separator to remove air from a high port while blood or non-cellular liquids are removed through a lower port. The external bubble collection system can further comprise a membrane filter operating under pressure to separate gas from liquid.

The present invention distinguishes over the cited prior art because it uses an active component to spin the blood to forcibly remove gas bubbles from the blood. The invention is useful during cardiovascular catheterization procedures, especially those accessing the left atrium, the venous circulation, and the cerebrovasculature. The device is also useful during surgery when cardiopulmonary bypass is instituted to maintain the patient on temporary cardiopulmonary support. It is also useful for removal of gas and bubbles during intravenous infusion of liquids to a patient. Patients with increased risk of pulmonary emboli are especially vulnerable during intravenous infusion and would benefit from such protection.

For purposes of summarizing the invention, certain aspects, advantages and novel features of the invention are described herein. It is to be understood that not necessarily all such advantages may be achieved in accordance with any particular embodiment of the invention. Thus, for example, those skilled in the art will recognize that the invention may be embodied or carried out in a manner that achieves one advantage or group of advantages as taught herein without necessarily achieving other advantages as may be taught or suggested herein.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1A illustrates a breakaway side view of a catheter air removal filter, integrated to the proximal end of an access sheath, catheter, or cannula, wherein the filter comprises a chamber, an impeller within the chamber, an inlet seal or valve, and a motor to drive the impeller, according to an embodiment of the invention;

FIG. 1B illustrates a cross-sectional rear view of the catheter air removal filter of FIG. 1A showing the impeller, the motor, the batteries, the external gas separation chamber, and the liquid return line, according to an embodiment of the invention;

FIG. 2 illustrates a breakaway side view of a catheter air removal filter comprising a chamber, an external pump, an external gas separation chamber, and a liquid return line, according to an embodiment of the invention;

FIG. 3 illustrates breakaway side view of a catheter air removal filter comprising ultrasound transducers to detect air within the system, according to an embodiment of the invention;

FIG. 4 illustrates breakaway side view of a catheter air removal filter comprising a chamber configured to generate circular flow of liquid therein, wherein the circular flow is generated by an external pump and a tangential fluid return line into the chamber, according to an embodiment of the invention;

FIG. 5 illustrates a breakaway side view of a catheter air removal filter comprising a chamber configured to scrub a catheter shaft inserted therethrough by means of a fluid jet emanating from the outlet of the fluid return line from an external liquid pump, according to an embodiment of the invention;

FIG. 6A illustrates a breakaway side view of a catheter air removal filter comprising a chamber, a rotary impeller, and a motor drive wherein the filter is affixed to the proximal end of a guide catheter, sheath, or cannula, according to an embodiment of the invention;

FIG. 6B illustrates a lateral sectional view of the filter of FIG. 6A showing the circular internal geometry and off-center disposition of the catheter access ports, according to an embodiment of the invention;

FIG. 7 illustrates a lateral, partial breakaway view of a catheter, sheath, introducer, or cannula air filter wherein the filter comprises a flow through impeller that not only spins the blood but also provides pumping action to circulate the blood through return ducts connecting one end of the filter with the other end, according to an embodiment of the invention;

FIG. 8 illustrates a lateral, partial breakaway view of a catheter, sheath, introducer, or cannula air filter comprising a two-stage impeller that spins the blood and pumps the blood, an air trap chamber, and an air removal device, according to an embodiment of the invention;

FIG. 9 illustrates a lateral, partial breakaway view of a catheter, sheath, introducer, or cannula air filter comprising a pumping impeller disposed downstream of the catheter introduction region, a central air trap, and an air filter to remove air from blood returned to the bottom of the filter by means of the return ducts, according to an embodiment of the invention;

FIG. 10 illustrates a lateral, partial breakaway view of a catheter, sheath, introducer, or cannula air filter comprising a narrow, shear impeller, one or more return ducts, a central air trap, and a mesh or membrane air separation filter disposed around the air trap, according to an embodiment of the invention; and

FIG. 11A illustrates a lateral view of a catheter or sheath air filter having a double battery pack, a switch, an electric motor drive, a main chamber, an inlet hemostasis valve, an outlet connector, a gas separator module, according to an embodiment of the invention;

FIG. 11B illustrates an inlet end view of the catheter or sheath air filter of FIG. 11A further having a foot to stabilize and hold the filter at an angle relative to the patient, according to an embodiment of the invention;

FIG. 12 illustrates a lateral, partial breakaway view of a catheter or sheath air filter comprising a shear impeller, at least one return duct, an air separator module, a magnetic coupling, and a battery power supply, according to an embodiment of the invention; and

FIG. 13 illustrates a close-up cross-section of the illustration in FIG. 12 without the catheters attached to the air filter, according to an embodiment of the invention.

FIG. 14A illustrates an oblique view of an impeller comprising a threaded exterior in one location;

FIG. 14B illustrates a side view of an impeller comprising a threaded exterior in two locations;

FIG. 15A illustrates a oblique view of an impeller comprising an exterior shroud, a central body, a pair of connector blades, and an exterior thread, according to an embodiment of the invention;

FIG. 15B illustrates a side view of an impeller comprising a tapered cone with a more steeply tapered bottom surface, according to an embodiment of the invention;

FIG. 16 illustrates a gas filter system comprising a sonic generator to shake the system such that air is separated from the physical components of the system, according to an embodiment of the invention;

FIG. 17 illustrates a gas filter system comprising an introduction sheath and a hanging bag of heparinized saline attached to the filter system distal to a hemostasis valve;

FIG. 18 illustrates a gas filter system comprising a power supply and controller separated from the motor drive by an electrical bus running parallel to the fluid drip line, according to an embodiment of the invention; and

FIG. 19 illustrates a gas filter system operably connected to a fluid injector such that any air entrained into the filter chamber from the fluid injector is removed prior to exiting the filter chamber and passing into a catheter, sheath, cannula, or introducer, according to an embodiment of the invention.

DETAILED DESCRIPTION OF THE INVENTIONS

As used herein the terms distal and proximal are used to clarify the location of various points along the axial length of a catheter or sheath. Points are defined with respect to the end grasped by the user and the end that is inserted in the patient in the same manner as would one skilled in the art of medical device catheter construction. The proximal end of the catheter or sheath is defined as that end closest to the user or operator, or user, of the catheter or sheath while the distal end of the catheter or sheath is defined as that end that is inserted into the patient.

FIG. 1A illustrates a side view of a catheter blood air filter assembly 100 of the present invention. The filter assembly 100 comprises a shell 102 further comprising an internal chamber 104, and an impeller 118 further comprising a plurality of vanes 106. The filter assembly 100 further comprises a second catheter inlet port 110, a second catheter outlet port 108, an inlet hemostasis valve 112, an optional outlet hemostasis valve (not shown), a gas vent (not shown), a motor drive (not shown), an electrical power source (not shown), a gas separator chamber (not shown), an on-off switch (not shown), a power cable connecting the electrical power source and the motor drive (not shown), and a return liquid port (not shown).

The shell 102 is configured with an axis of rotation about which fluid within the shell 102 can rotate. Therefore the shell 102 is approximately round in internal cross-section with the chamber 104 having a generally axially elongate cylindrical shape. The impeller 118 is affixed to the shaft of the motor drive (not shown) and rotates about the shaft axis at speeds between approximately 10 and about 10,000 revolutions per minute (RPM), and preferably between about 100 and about 5,000 RPM. The primary concern is for removal of larger air bubbles that can be easily moved to the center of the device at these rotational rates, even if the device is flipped sideways, upside down, or any other orientation since the rotational, buoyant—forces will overpower gravitational at these rotation rates. The second catheter inlet port 110 is aligned generally tangential to the outer circumference of the chamber 104 and the lumen of the second catheter inlet port 110 is operably connected to the interior of the chamber 104. The second catheter outlet port 108 is aligned generally tangential to the outer circumference of the chamber 104 and is aligned generally coaxially with the second catheter inlet port 110. A second catheter 116, further comprising a second catheter hub 114 and a second catheter shaft 140, when inserted through the second catheter inlet port 110 can be advanced through the chamber 104 and into the second catheter outlet port 108 without restriction, binding, or obstruction. The entry 142 to the second catheter outlet port 108 from the chamber 104 can, in a preferred embodiment, be flared, beveled, or funnel shaped such that should the second catheter shaft 140 bend slightly out of the line of the straight axis, it will be coerced or guided into the second catheter outlet port 108.

The main axis, along which the second catheter 116 runs, can be oriented parallel to the rotational axis of the impeller 118 or, in a preferred embodiment, the catheter axis can be oriented perpendicular to the rotational axis of the impeller 118. The rotational axis of any fluid within the chamber 104 will be approximately the same as that of the impeller 118, since the impeller 118 directly drives the rotational motion of said fluid. By orienting the catheter 116 axis perpendicular to the rotational axis of the impeller 118, the blood and fluid within the chamber 104 will rotate generally in a similar direction as the axis of the second catheter shaft 140 as it passes the second catheter shaft 140 and thus flow disturbance by the catheter shaft 140 will be minimized. High velocity flow passing the second catheter shaft 140 will entrain any bubbles of gas attached thereto and drive the bubbles into the flow vortex created by the spinning impeller 118. The bubbles entrained in the flow vortex will migrate to the center of the vortex by buoyancy effects operating within the rotational flow field. Thus the lighter gas elements or bubbles will move inward while the heavier liquid and solid elements will move outward in the rotational flow field. The axis of rotation of the impeller 118 is preferably higher than the axis of the second catheter 116 so that passive buoyancy effects facilitate bubble separation from the region of the second catheter 116.

The shell 102 and the impeller 118 can be fabricated from polymers such as, but not limited to, polycarbonate, polysulfone, polyvinyl chloride, polyurethane, polyethylene, polyimide, polyamide, polyester, and the like. The shell 102 is preferably fabricated from a generally transparent polymer so that visualization of air or gas within the chamber 104 is possible. The diameter of the chamber 104 can range from about 0.5-cm to about 10-cm with a preferred diameter of about 2-cm to about 5-cm. The width of the chamber 104 along its rotational axis can range from about 1-cm to about 10-cm with a preferred range of about 2-cm to about 7-cm. The weight of the filter assembly 100 should be as low as possible so as to minimize forces on the first catheter or sheath 144 to which the filter assembly 100 is attached. The weight of the filter assembly 100 should be less than 450 grams and preferably less than 200 grams. The outlet port 108 of the filter assembly 100 can be attached to the first catheter or sheath 144 with a reversible coupling 146 such as a Luer lock, bayonet mount, screw thread, fastener, or the like, or it can be permanently affixed thereto. It is beneficial to use a locking type connector 146, or a permanent connection, to minimize the risk of the filter assembly 100 from inadvertently becoming disconnected from the first catheter or sheath 144 as air could then enter the first catheter or sheath 144, defeating the purpose of the filter assembly 100.

The valve 112 can be affixed, or integral, to the second catheter inlet port 110, which is affixed, or integral, to the chamber 104. The valve 112 can be a Tuohy-Borst valve, an elastomeric membrane with a pinhole, a duckbill valve, an elastomeric gasket with a central orifice slightly smaller than shaft 140 of the second catheter 116, or a combination of the these designs.

FIG. 1B illustrates the catheter blood air filter assembly 100 of FIG. 1A as viewed from the proximal end. The filter assembly 100 comprises the shell 102, the chamber 104, the impeller 118, the inlet valve 112, the gas removal port 134, the gas separation chamber 136, the liquid return line 138, the liquid return port 130, the motor bearing 120, the motor 122, the motor shaft 148, the electrical connections 126, 128, the battery 124, and an on-off switch (not shown).

Referring to FIG. 1B, the second catheter (not shown) has its axis aligned with that of the inlet valve 112. The motor is affixed to the impeller 118 by the motor shaft 148. The gas outlet port 134 is aligned generally along the rotational axis of the impeller 118 and allows air collected within the fluid vortex to escape from the chamber 104 and rise up into the gas separation chamber 136. Gas can be drawn off from the gas separation chamber 136 through the gas escape port 150, which is affixed to the top of the gas separation chamber 136 and operably connected to the internal volume of the gas separation chamber 136. The liquid return line 138 is affixed and operably connected to the bottom of the gas separation chamber 136 so that liquid can be returned back to the chamber by the action of the impeller 118, which not only generates rotational motion to the fluid within the chamber 104 but serves to drive fluids into the chamber 104 and toward the gas removal port 134.

The impeller 118 can be configured to drive forward flow by creating openings in the motor 122 side of the impeller 118 and beveling the surfaces around the openings to form propeller-type geometries within the impeller 118. Thus, a single motor 122 and impeller 118 can perform all the fluid forcing required by the filter assembly 100. In another embodiment, a second motor and pump (not shown), or at least a second pump (not shown) operated by the same motor 122 causes fluid flow within the liquid return line 138. Flow rates within the liquid return line 138 can range between 0.5-cc per minute and 100-cc per minute. A separate liquid infusion port (not shown) can be operably connected to a hanging bag or source of non-cellular prime (not shown) such as saline, but this is not required for operation of the filter assembly 100 since all liquid can be drawn from the catheter or the initial filter assembly priming step.

In an embodiment, the impeller 118 can be housed within the chamber 104 without any impeller or motor shaft 148 passing through the wall of the chamber 104. This can be performed by embedding permanent magnets within the impeller 118 and having the motor 122 and shaft 148 turn complementary permanent magnets, which are affixed thereto. These permanent magnets can engage the impeller, by means of magnetic fields, through the walls of the chamber 104 and generate rotational motion of the impeller 118. The magnetic field interacts with the magnets within the impeller 118 and causes the impeller 118 to rotate at the same rate as that of the motor 122. The magnetic driver (not shown) is preferably a bar magnet that spins about its central region with north and south poles diametrically opposed and equidistant from the center of rotation. Typical permanent magnets are fabricated from materials such as, but not limited to, neodymium iron boron, iron, ceramics, samarium cobalt and the like. Materials that are magnetically attracted to a magnet include, but are not limited to, iron or metallic alloys of iron. The magnetic driver (not shown) is desirable because it allows for a sealed chamber 104.

All components of the blood air removal system 100 can be fabricated preferably from biocompatible materials, which are sterilizable using methods such as, but not limited to, ethylene oxide, gamma irradiation, electron beam irradiation, or the like. The blood air removal system 100 can be provided separately for attachment to a first catheter or sheath 140, it can be pre-attached thereto, or it can be provided in a kit, separately attached but provided therewith. The blood air removal filter system 100 is preferably provided sterile in an aseptic packaging system (not shown).

Optionally, the interior of the shell 102 of the blood filter 100 can be treated or coated with an anti-thrombogenic material such as heparin and a bonding agent. The impeller 118 can be made from materials that include polycarbonate, polypropylene, polyethylene, polystyrene, acrylonitrile butadiene styrene (ABS), polyvinyl chloride, fluorinated ethylene polymer (FEP), polysulfone, polytetrafluoroethylene (PTFE), and the like.

FIG. 2 illustrates a catheter blood air filter system 200 comprising a shell 226 comprising a chamber 202, an air vent port 228, a blood air separation chamber 204, a gas vent 224, a liquid return line 208, a motor driven pump 206, a pump return line 210, a second catheter inlet port 230, an inlet valve 212, an outlet valve 214, a first catheter 232, a first catheter connector 234, a second catheter outlet port 236, a battery 218, an electrical bus 220, an on-off switch 222, and a second catheter 116, further comprising a hub 114 and a second catheter shaft 140.

The air vent port 228 is affixed to the shell 226 and is operably connected to the chamber 202 at or near the top of the chamber 202. The gas vent 224 is affixed to the top of the blood air separation chamber 204, which is affixed to the air vent port 228. The inlet side of the liquid return line 208 is affixed at or near to the bottom of the blood air separation chamber 204. The outlet side of the liquid return line 208 is affixed to the motor driven pump 206. The motor driven pump 206 is operably connected to the battery 218 by the electrical bus 220 and the on-off switch 222 is operably connected to the electrical bus 220 to provide a means for turning the motor driven pump 206 on and off. The outlet of the motor driven pump 206 is physically and operably connected to the inlet of the pump return line 210. The outlet of the pump return line 210 is physically affixed to the shell 226 and operably connected to the chamber 202.

The second catheter inlet port 230 is affixed to the shell 226 and comprises a central lumen, which is operably connected to the chamber 202 near the bottom of the chamber 202. The inlet valve 212 is affixed to the second catheter inlet port 230 and comprises a central lumen operably connected to the central lumen of the second catheter inlet port 230. The second catheter outlet port 236 is affixed to the shell and further comprises a lumen that is operably connected to the chamber 202 near the bottom. The second catheter outlet port 236 is affixed to the outlet valve 214 and to the first catheter connector 234. The first catheter connector 234 is affixed or reversibly coupled to the first catheter 232. The second catheter outlet port 236 can comprise a funnel-shaped or beveled entrance, or other type of guide structure 238, to coerce the second catheter shaft 140 to becoming coaxially aligned, should the second catheter shaft 140 become bent out of the axis slightly during insertion.

The shell 226 and other components of the blood air filter system 200 can be fabricated from the same materials as those used in the embodiment 100 shown in FIGS. 1A and 1B. The sizes and flow rates of the two systems 100 and 200 are also similar. The wall thickness of the shell 226, and the shell of all devices disclosed herein, can range between about 0.010 inches and 0.125 inches with a preferred range of about 0.030 inches and 0.090 inches. The shell 226, as well as the shell of all devices disclosed herein is beneficially small in size, lightweight, and is free from flexible attachments other than the catheter itself or any fluid drip lines associated therewith.

The method of operation of the blood air filter system 200 is that it can be affixed to the proximal end of the first catheter 232. It can be primed and purged of air with saline through the gas vent 224. The motor driven pump 206 is turned on with the on-off switch 210. Flow is generated within the system to pull liquid out of the chamber 202 through the air vent port 228, and then pump liquid back into the chamber 202 through the pump return line 210, wherein air will separate in the air separation chamber 204 due to buoyant effects. Since the air vent port 228 is at the top of the chamber 202 any air in the chamber will preferentially collect near the air vent port 228 and be withdrawn from the chamber 202. Blood and other liquids, separated from the air in the air separation chamber 204 are returned to the chamber 202 by the motor driven pump 206.

The motor driven pump 206 can operate at voltages ranging between 1.5 and 24 volts DC and preferably between 1.5 and 12 volts DC. The battery 218 can match the voltage needs of the motor driven pump 206 and can operate for periods of up to 12 hours, preferably at least up to 6 hours once switched on. The system 200 is preferably disposable and is provided sterile in aseptic packaging similar to that described for the filter system 100 of FIGS. 1A and 1B. The battery 218 can be rechargeable or single use. The battery 218 can comprise chemistries including, but not limited to, lithium ion, nickel metal hydride, alkaline, nickel cadmium, and the like. In some embodiments, the on-off switch 210 can comprise a layer of electrically insulated material, such as, but not limited to, paper, cardboard, polyvinyl chloride, polyethylene, polypropylene, or the like, the insulated material being disposed between two electrical contacts that are spring biased toward each other. These embodiments provide generally automatic on once the filter system 200 is put into service. The switch 210 layer can further comprise a tab that is removed, along with the attached layer of electrically insulating material, prior to use of the filter system 200 such that once the tab (not shown) is removed, the switch contacts 210 move to the closed position and remain in electrical contact until the battery 218 loses its charge or becomes depleted. The tab can be removed manually or it can be affixed to the packaging such that once the filter system 200 is removed from its sterile package, the on-off switch 210 is engaged. The on-off switch 210 can also comprise a toggle switch, rocker switch, or other design that is manually engaged by the user. Such power sources and automatic or manual switching can be used for all the embodiments of catheter air filters described herein.

FIG. 3 illustrates a blood air filter system 300 comprising ultrasound transducers 342 and 344 to detect the presence of air within the system 300. The blood air filter system 300 comprises a shell 302 enclosing a chamber 304, a gas exit port 334, a gas reservoir 336, a gas removal and purge port 350, a second catheter inlet port 310, a second catheter outlet port 308, a first catheter connector 146, a first catheter or sheath 144, a motor drive 322, an impeller 318, a battery pack 324, an inlet hemostasis valve 312, an ultrasound detection control system 346, at least one warning light 348, and a warning audible signal 352. The system 300 further comprises a second catheter 116 further comprising a hub 114 and a second catheter shaft 140.

Referring to FIG. 3, the blood air filter system 300 operates similarly to the filter system 100 described in FIGS. 1A and 1B except that the axis of the chamber is aligned vertically and the second catheter inlet port 310 and second catheter outlet port 308 are disposed on one side of the chamber 304 so that the vortex or circular flow field generated by the impeller 318 within the shell 304 forces any air or bubbles toward the central axis of the chamber 304 where it can rise to the top and be removed out the gas exit port 334 and into the gas reservoir 336.

The ultrasound transducers 342 and 344 can be affixed to the second catheter outlet port 308 and the second catheter inlet port 310, respectively and can detect the presence of air or gas in the system, which is normally supposed to be filled only with liquid (blood, saline, etc.). Ultrasound signals can pass easily through liquids but they do not travel through gas well, so discrimination of the two phases is easily accomplished with ultrasound transducers. The ultrasound transducers 342 and 344 are wired to the ultrasound control unit 346 by an electrical bus (not shown). Power can be derived from the battery 324 or from another battery (not shown). The ultrasound control unit can display the presence of air by illuminating the warning light 348, sounding the audible signal 352, or both. Each transducer 342 and 344 can, in another embodiment, have a separate warning light, audible warning frequency, or both. Another ultrasound transducer (not shown) can be used to detect significant buildup of gas in the gas reservoir 336 such that the gas can be removed through the purge port 350.

FIG. 4 illustrates a catheter blood air filter system 400 comprising a shell 402, which encloses an axially elongate chamber 404. The filter 400 system further comprises a motor driven pump 406, a second catheter outlet port 408, a second catheter inlet port 410, an inlet valve 412, a liquid return line 414, a tangential liquid return line inlet 416 to the chamber 404, a power source 418, a gas vent 420, a gas collection chamber 422, a gas bleed and purge port 424, a first catheter or sheath 144, a first catheter or sheath connector 146, and a second catheter 116 further comprising a hub 114 and a second catheter shaft 140.

Referring to FIG. 4, the gas vent 420 is affixed to the top of the shell 402. The chamber 404 is generally cylindrical and axially elongate but the top of the chamber 404 can beneficially be tapered or rounded to funnel air toward the center as it rises. The gas collection chamber 422 is affixed to the gas vent 420 or the shell 402 and the internal volume of the gas collection chamber 422 is operably connected to the lumen of the gas vent 420. The inlet to the motor driven pump 406 is affixed near the bottom of the gas collection chamber 422. The liquid return line 414 is affixed to the outlet of the motor driven pump 406. In this and the other embodiments requiring an external pump, the motor driven pump 406 can be a centrifugal pump, as illustrated, or it can be a roller pump, a piston pump, a diaphragm pump, or the like.

Fluid being pumped back into the chamber 404 through the return inlet line 416 forms a fluid jet which, directed tangentially along the wall of the chamber 404, generates a circular flow pattern or vortex within the chamber 404. This circular flow pattern entrains air and bubbles toward the center due to the effects of air buoyancy acting in a centrifugal flow field. Thus air is moved away from the second catheter inlet port 410 and the second catheter outlet port 408, both of which are affixed to the shell 402 near the bottom and near the periphery of the chamber 402. Air can be entrained into the chamber 404 by insertion of the second catheter shaft 140 through the inlet valve 412, which is a hemostasis type valve as described in the embodiment shown in FIGS. 1A and 1B, at the inlet to the chamber 404 if the hemostasis valve 412 leaks or becomes faulty.

FIG. 5 illustrates a breakaway side view of a catheter air removal filter system 500 comprising a shell 402 enclosing a chamber 404. The filter system 500 system further comprises a motor driven pump 406, a second catheter outlet port 408, a second catheter inlet port 410, an inlet valve 412, a liquid return line 502, a liquid return line inlet 504 to the chamber 404, a power source 418, an on-off switch 512, a gas vent 420, a gas collection chamber 422, a gas collection chamber case 510, a gas bleed and purge port 424, a particulate filter 508, a first catheter or sheath 144, a first catheter or sheath connector 146, and a second catheter 116 further comprising a hub 114 and a second catheter shaft 140. Liquid entering the chamber 404 is in the form of a fluid jet 506 capable of scrubbing the catheter shaft 140.

Referring to FIG. 5, the liquid return line 502 is generally routed near to, against, or integral to the chamber shell 402. The motor driven pump 406 is affixed to the shell 402, as is the case 510 of the gas collection chamber 422. The components are all rigidly, or semi-rigidly, affixed to the shell 402 to minimize bulk and to make the system easily maneuverable without excess weight, or dangling components. There is no requirement for a lead line to a reservoir of fluid (not shown). Such a drip line to a reservoir can be added for the purpose of adding heparinized saline to the system but is not required for the function of the filter system 500. Such drip lines (not shown) are often comprised by the hub 114 of the second catheter 116 but are not the subject of this disclosure. The interior components of the filter system 500 can comprise coatings that comprise anti-thrombogenic properties.

The motor driven pump 406 can, in certain embodiments, serve to withdraw liquid from the distal end of the first catheter or sheath 114 all the way back to the gas collection chamber 422 where it can be removed from the system through the gas bleed 424. The power source 418 can be affixed directly to the shell 402 to minimize bulk. The on-off switch 512 for the motor driven pump 406 can be a separate on-off or on switch that runs until the battery power source 418 is depleted of energy. The on-off switch 512 can further be embedded within the second catheter inlet port 410, the second catheter outlet port 408. The on-off switch 512 can further be a light activated, ultrasonically activated by ultrasound transducers 342, 344, such as those described in FIG. 3, or pressure activated device associated with the filter system 500. The ultrasound transducers 342, 344 can be affixed to the shell 402, the second catheter inlet port 410, the second catheter outlet port 408, or both. The weight of the filter assembly 500 should be less than 450 grams and preferably less than 200 grams. The size of the filter assembly 500 or any of the other filter systems described herein is ideally less than approximately 5-cm in any direction or side dimension, including all components, to minimize bulk and maximize maneuverability of the first catheter 144 and second catheter 116. The filter assemblies 500, 400, 300, 200, or 100 can further be configured to permit a plurality of second catheter inlet ports 410 so the filter assemblies can be part of a second catheter hub Y connector, for example.

The gas purge port 424 can be monitored by an ultrasonic transducer to detect the presence of gas in the collection chamber 422 and audibly or visually signal the need to remove the gas. The gas purge port 424 can be terminated by a stopcock or other valve, such that application of a syringe or hypodermic needle can permit the removal of collected gas or air. The gas purge port 424 can further be interconnected to a pump system that automatically, or manually, actuates removes collected gas.

FIG. 6A illustrates a catheter, cannula, sheath, or introducer blood air filter 600 comprising a shell wall 618 and a central volume 616, an air collection region 620, an air bleed port 624, an impeller 610, an impeller shaft 614, a motor drive 622, an inlet port 608, an outlet port 606, a sheath connector 604, an inlet valve 312, an introducer, cannula, sheath, or first catheter 144 further comprising a cannula hub 602, and a second catheter 116 further comprising a hub 114 and a second catheter shaft 140. The filter 600 further comprises a power supply (not shown), an on off switch (not shown), an impeller shaft seal (not shown) and an electrical bus (not shown).

Referring to FIG. 6A, the impeller 610 is affixed to the impeller shaft 614, which is affixed to the rotational part of the motor drive 622. The impeller 610 rotates about its central axis, which is concentric and parallel with the impeller shaft 614. The impeller 610, as illustrated is a shear impeller and does not have vanes or other projections. The shear impeller is generally smooth with no substantial radial or spiral projections from its structure. While a shear impeller is not as efficient at spinning fluid as a vane impeller, the shear impeller causes less damage to the red and white blood cells than does the vane impeller. Rotation of the shear impeller 610 imparts a circular motion of fluid (generally blood and saline), generated by viscous or inertial forces, within the central volume 616 with the circular motion directed about the central axis of the impeller 610. Centrifugal forces cause the blood and liquid within the chamber to move outward and any air or gas to move inward toward the center of the central volume 616. Collected air within the air collection region 620 can be removed through the gas or air bleed port 624. The gas or air bleed port can comprise a bayonet, threaded, or Luer fitting, or it can further comprise a valve system (not shown) such as a stopcock, one way valve, or the like. There is beneficially no valve associated with the outlet port 606 but any valves so integrated need to permit retrograde flow in the proximal direction because the system is primed through the lumen of the cannula or sheath 144 by fluids from the vascular system.

The filter 600 can be releasably affixed to the hub 602 of the cannula or first catheter 144 by means of a Luer lock 604, bayonet mount, threaded fitting, or the like. The Luer lock 604 is affixed to the distal end of the outlet port 606. The inlet port 608 is affixed to the hemostasis valve 312, which can comprise a duckbill valve, a Tuohy-Borst valve, a pinhole valve, a slit valve, a combination thereof, or similar. The motor drive 622, the shell 618, the impeller 610, and other components of the system can be fabricated from materials similar to those used for the filter embodiments illustrated in FIGS. 1A-5. In the illustrated embodiment, the upper region of the shell 618 tapers inward toward the air collection chamber 620. In other embodiments, different geometries such as substantially non-tapered walls or substantially outwardly tapered walls may be advantageous.

FIG. 6B illustrates a lateral cross-sectional view of the filter 600 of FIG. 6A, looking toward the bottom or motor drive 622 end along the line A-A. The filter 600 comprises the shell wall 618, the inlet port 608, the outlet port 606, the inlet valve 312, the outlet connector 604, the impeller 610, the impeller shaft 614, and the shaft or tubing 140 of the second catheter 116. The central volume 616 is generally cylindrical in shape, as illustrated in this sectional view. The cylindrical shape can also comprise an hourglass, a trapezoid tapering downward, a trapezoid tapering upward, or complex geometries, all of which are substantially circular in cross-section. The circular cross-sectional shape permits the blood or liquid to flow in a circular pattern to the maximum achievable rotational velocity. The second catheter shaft 140 is disposed near the periphery of the shell 618 such that any air introduced thereby is forced toward the center of the chamber 616 and away from the outlet port 606.

FIG. 7 illustrates a partial breakaway side view of another embodiment of a catheter, sheath, cannula, or introducer air filter 700. The filter 700 comprises the inlet port 608, the inlet valve 312, the outlet port 606, the outlet port connector 604, an outer shell 712, the inner shell 618 further comprising the chamber 616 and the upper chamber 716, a plurality of return inlet ducts 704, a plurality of return duct inlet ports 706, the motor drive 622, an impeller seal 728, the impeller shaft 614, the impeller 702 further comprising flow through vents 724 and propeller or fan blades 726, a plurality of return duct outlet ports 722, the air vent 624, an air collection chamber 720, an air collection chamber inlet port 708, and an air collection chamber baffle 710. Affixed to the filter 700 are the cannula, sheath, introducer, or first catheter 144 further comprising the hub 602, and the second catheter 116 further comprising the second catheter shaft 140 and the second catheter hub 114.

Referring to FIG. 7, the outlet connector 604 is releasably affixed to the first catheter hub 602 but can also be permanently affixed thereto if desired. The second catheter shaft 140 is inserted through the inlet valve 312. The impeller 702 comprises holes or fenestrations 724 that permit blood to flow through the impeller 702 and into the chamber volume from the return ducts 704. The spinning impeller 702 creates high fluid pressure near the periphery of the inner shell 618 and low pressure near the central axis. Thus blood entering near the central axis through the return duct outlet ports 722 enters the chamber 616, flows upward toward the upper chamber 716, and exits via the return duct inlet ports 706 with a circulation setup thereby. Flow within the chamber 618 is circular as driven by the impeller 606 and moves from the bottom end, near the motor drive 622 toward the top end nearest the air collection chamber 720. Bubbles of air or gas are forced toward the central axis by centrifugal effects and enter the air collection chamber 720 where they can be withdrawn through the air vent 624. The air collection chamber 720 is beneficially fabricated from transparent materials so that collected air can be visualized and removed. A bubble or gas detector (not shown), such as an ultrasonic probe with an alarm can be used to further indicate the presence of air in the system or in the air collection chamber 720. By setting up both a bottom to top flow as well as a rotational flow, the system becomes independent of gravitational orientation and can function no matter in which direction the central axis is aligned. The materials of fabrication, motor specifications, rotation rates, etc. are consistent with other filter embodiments described herein.

FIG. 8 illustrates an air trap or filter 800 affixed to the hub 602 of a first cannula, sheath, introducer, or catheter 144. The air trap 800 comprises the inlet port 608, the inlet valve 312, the outlet port 606, the outlet port connector 604, an outer shell 712, the inner shell 618 further comprising the chamber 616 and the upper chamber 716, a plurality of return inlet ducts 704, a plurality of return duct inlet ports 706, the motor drive 622, an impeller seal 728, the impeller shaft 614, the impeller 702 further comprising flow through vents 724, a plurality of return duct outlet ports 722, the air vent 624, an air collection chamber 720, an air collection chamber inlet port 708, and an air collection chamber baffle 710. Inserted through the filter 800, is the second catheter 116, further comprising the second catheter shaft 140 and the second catheter hub 114. The impeller shaft 614 further comprises an extension 806 and an upper propeller 804 configured to move blood from the bottom to the top of the chamber 616. Affixed to the gas outlet port 624 (FIG. 6A) of the gas collection chamber 720 is a stopcock 802 and a syringe 808 for withdrawal of gas or air.

Referring to FIG. 8, the propeller 804 moves blood, liquid, and gas toward the top of the system while the impeller 702 establishes and maintains circular flow to accelerate air and bubbles toward the axis of the system. The syringe is one way to remove air although an automated gas venting system can also be used. The stopcock 802 can be used to close the gas removal port 624 while the syringe 808 is being emptied of air.

FIG. 9 illustrates an air trap or filter 900 affixed to the hub 602 of a first cannula, sheath, introducer, or catheter 144. The air filter or trap 900 comprises the inlet port 608, the inlet valve 312, the outlet port 606, the outlet port connector 604, an outer shell 712, the inner shell 618 further comprising the chamber 616, the return duct 704, a bubble mesh or membrane filter element 902, the motor drive 622, the impeller seal 728, the impeller shaft 614, further comprising the extension 806, the propeller 804, the return duct outlet port 722, the air vent 624, an air collection chamber 720, an air collection chamber inlet port 708, and an air collection chamber baffle 710. Inserted through the filter 900 is the second catheter 116 further comprising the second catheter shaft 140 and the second catheter hub 114. The impeller shaft 614 further comprises an extension 806 and the upper propeller 804 configured to move blood from the bottom to the top of the chamber 616. Affixed to the gas vent 624 (FIG. 6A) of the gas collection chamber 720 is a stopcock 802 and a syringe 808 for withdrawal of gas or air. The air collection chamber 720 further comprises an upper access port 906. The inner chamber 616 further comprises a residual gas collection plenum 904.

Referring to FIG. 9, blood flowing through the return duct 704 passes through the filter element 902, which comprises a mesh or membrane 902 having pores of about 20 to 50 microns in size, or preferably between about 0.1 and about 2 microns in size, and most preferably between about 0.2 and about 1.0 microns in size, such that large bubbles will catch therein and not pass through due to surface tension effects. The system can generate pressure drops across the mesh or membrane 902 with the pressure drop ranging between about 0.5-mm Hg and about 10-mm Hg with a preferred pressure drop of between about 1-mm Hg and about 5-mm Hg. The pressure drop can be generated using a vacuum generator operably coupled to the downstream side of the mesh or membrane 902 or with a positive pressure generator operably attached to the upstream side of the mesh or membrane 902. The residual gas collection plenum 904 routes gas that is prevented from passing the mesh filter element 904 back into the gas collection chamber 720 through the upper access port 906. The propeller 806 serves to pump liquid and air upward away from the motor drive 622 end and toward the gas collection chamber 720 but also serves to impart rotational flow within the chamber 616. Rotational rates, materials of fabrication, sizes, and specifications are similar to other embodiments described herein.

FIG. 10 illustrates a partial breakaway side view of another embodiment of a catheter, sheath, cannula, or introducer air filter 1000. The filter 1000 comprises the inlet port 608, the inlet valve 312, the outlet port 606, the outlet port connector 604, an outer shell 712, the inner shell 618 further comprising the chamber 616 and the upper chamber 716, a plurality of return inlet ducts 704, a plurality of return duct inlet ports 706, the motor drive 622, an impeller seal 728, the impeller shaft 614, an elongate impeller 1008, a plurality of return duct outlet ports 722, the air vent 624, an air collection filter wall 1004, an air collection chamber inlet port 1002. Affixed to the filter 700 are the cannula, sheath, introducer, or first catheter 144 further comprising the hub 602. The tubing or shaft 140 of the second catheter 116 further comprising the second catheter hub 114 is inserted through the inlet 608 and outlet 606 ports of the filter 1000.

Referring to FIG. 10, the elongate impeller 1008 spins the fluid or blood through shear effects while minimizing potential blood damage. The pressure drop generated across the chamber 616 causes blood to flow from the return duct outlet ports 722 through the chamber 616 and exits through the return duct inlet ports 706 to the return ducts 704. Gas, air, and bubbles are forced centrally by the rotational flow generated inside the chamber 616 by the shear impeller 1008 and forced into the air collection chamber 720 where they can be removed through the gas vent 624. Blood and liquid can flow out through the air collection filter wall 1004 and into the upper chamber 716 where it can return to the bottom of the chamber 616 through the return ducts 704. The narrow, axially elongate impeller 1008 permits fluid to flow around it without the need for perforations, vanes, or holes therein.

Other aspects of the inventions include methods of use. In an exemplary embodiment, a sheath, such as a Mullins sheath is used to access the left atrium of the heart by way of femoral venous access via the Seldinger technique or similar. The Mullins-type sheath is advanced through the inferior vena cava into the superior vena cava. A transseptal needle, such as a Brockenbrough needle, is inserted through the Mullins-type sheath or catheter and aligned medially. The transseptal needle and sheath combination is withdrawn from the superior vena cava into the right atrium where the catheter, protecting the tip of the needle engages the fossa Ovalis. The needle is advanced out through the distal end of the Mullins-type sheath and through the fossa Ovalis. The Mullins sheath is advanced over the transseptal needle into the left atrium. The transseptal needle is removed and therapeutic or diagnostic catheters are inserted through the Mullins-type sheath into the left atrium. Procedures such as electrophysiology mapping, electrophysiology ablation of the heart, atrial appendage procedures including plugs, filters, and closure devices, mitral valve procedures, and the like can be performed through such an access procedure. The application of the air filter, described herein, to the proximal end of the Mullins-type sheath would significantly reduce the risk of air embolism in these procedures. The left atrium can expose the distal end of the catheter to low enough pressures to draw air into the left atrium through an inserted catheter, thus the need for such a prevention device. Other procedures, where such an air embolism protection device would be beneficial, include central venous access catheters, cardiac access catheters and catheters used for cerebrovascular access. Fluid withdrawn through a purge port on the air filter can drain from the patient's cardiovascular system through the annulus between the first and second catheter into the air filter and out through the air filter purge port or through the gas removal port on the catheter air filter. Thus, the catheter air filter assists with purging of dangerous air or other gas from the first catheter or sheath.

FIG. 11A illustrates a side view of an embodiment of the catheter or sheath air filter 1100. The filter 1100 comprises a main housing 1102, a gas separator housing 720, the gas withdrawal port 624, the gas withdrawal stopcock 802, the inlet port 608, the motor 622, two batteries 124, the electrical leads 126, 128, a pair of motor electrical terminals 1106, and the electrical on off switch 222.

Referring to FIG. 11A, the batteries 124 can comprise cells having voltages of about 1.5 volts DC or about 3 volts DC. The batteries 124 can be wired in parallel or series to achieve voltages appropriate to the operation of the motor 622 at the required shaft rotational velocities necessary to spin the fluid within the housing 1102. The switch 222 provides an open contact in the electrical lead 126 that can be closed upon closure of the switch 222. In some preferred embodiments, the switch 222 comprises a normally closed bias that is held open by means of a shim or other separation device. Once the user removes the separation device, prior to using the filter, the motor 622 receives power from the batteries 124 and continues to run until the batteries 124 run out of power. Suitable batteries 124 can include the Sony CR2450 Lithium cell which has an operating voltage of 3VDC and can provide up to 0.5 amp-hours of power. This power is sufficient to drive a motor 622 having a low power requirement for up to 6 hours or more. A suitable motor 622 can include the Fulhaber 1516T006SR which can generate shaft speeds up to about 3,000 RPM under loads experienced within the air filter. Another suitable motor 622 can include the more powerful Fulhaber 1319006SR. These motors comprise 6 VDC windings but can also be obtained in 9 and 12 volt versions. These motors 622 are generally used without any gearboxes that would drain energy from the system. Speed control is therefore maintained by control of voltage input to the motor 622. The main housing 1102 is affixed to the inlet port 608 as well as to the motor 622. A motor shroud (not shown) can cover the motor 622, the batteries 124, any electronics, and the electrical leads 126, 128, as required. The system can further comprise optical displays (not shown) such as light emitting diodes (LED) that can be configured to glow green when the system is running properly, yellow when the system is running out of energy, and red when the system stops working, for example. The source of information for these optical displays can be battery 124 power, motor 622 RPM, pressure within the housing 1102, and the like.

FIG. 11B illustrates an end view of the catheter or sheath air filter 1100 looking from the inlet side. The catheter or sheath air filter 1100 further comprises the gas separator module 720, the main housing 1102, a foot or stand 1108 and a foot or stand attachment bracket 1110.

Referring to FIG. 11B, the attachment bracket 1110 is affixed to the filter 1100 at any convenient point. The attachment bracket 1110 can be integrally formed, or separately formed and attached to the housing 1102 of the filter 1100. The attachment bracket 1110 can be integral to, or separately formed and affixed to, the foot 1108. The foot 1108 provides a relatively large, footprint that can hold the filter 1100 in a stable position on the patient, generally in the region of the groin, shoulder, etc. and on top of a surgical drape to which it may be merely resting or it can be affixed thereto with clips, pins, snaps, tape, hook and loop fasteners, adhesive, or the like. The hollow gas separator module 720 is affixed to the upper end of the housing 1102 and its internal volume is operably connected to the internal volume of the housing 1102. The attachment bracket 1110 can be oriented relative to the foot 1108 and the housing 1102 such that the housing 1102 resides at any appropriate angle relative to the flat bottom of the foot 1108. In the illustrated embodiment, the foot holds the longitudinal axis of the housing 1102 and the gas separator module 720 at an angle of about 30 degrees from horizontal. The angle can range anywhere from about 90 degrees (horizontal) to about 0 degrees (vertical) from horizontal. The angle can be greater than 0 degrees to improve the stability of the filter 1100 so that its longitudinal axis is not entirely vertical and thus resides more horizontally. Some vertical tilt can be beneficial for the operation of the filter 1100 since gravity and buoyancy then enhances the movement of air from the main housing 1102 into the gas separator 720, although a general current within the housing 1102 moves all fluids (air, blood, water, etc.) toward the gas separator 720.

FIG. 12 illustrates a side, partial breakaway cross-section view of the catheter or sheath air filter 1100. The filter 1100 is shown in partial cross-section as described by the section lines A-A in FIG. 11B. The main housing 1102 is illustrated in breakaway view while the inlets and outlets are illustrated without any breakaway. The catheter or sheath air filter 1100 comprises the motor shaft 614, an impeller magnetic coupler 1210, an impeller shaft 1208, the fluid return manifold 714, the vaneless shear impeller 1008, the main chamber internal volume 616, the inlet hemostasis valve 312 further comprising a purge port 1218, the one or more return fluid channels 704, the one or more fluid channel inlet openings 706, a gas separator collection volume 1224, a gas separator membrane 1226, a gas separator membrane support 1228, a gas separator outlet volume 1230, the gas separator housing 720, the gas collection shroud 1002, a catheter guide channel 1220, the second catheter 116 further comprising the second catheter shaft 140 and the hub 141, the first catheter hub 602, the first catheter tube 144, the first catheter hemostasis valve 604, the one or more return outlet orifices 722, the impeller shaft bearing 728, one or more impeller magnetic coupler magnets 1212, one or more motor magnetic coupler magnets 1214, a motor magnetic coupler 1216, an outlet port 1202 further comprising a groove 1204, a short outlet tube stub 1232, and a releasable clamp 1206.

Referring to FIG. 12 the filter 1100 is releasably affixed to the proximal end of the first catheter hub 602. The first catheter hub 602 comprises the first catheter hemostasis valve 604 but has no Luer fitting on its proximal end. The outlet port connector 1202 further comprising the stub tube 1232 is affixed to the first catheter hemostasis valve 604 by inserting the stub tube 1232 into the proximal end of the first catheter hemostasis valve 604 proximal and then applying the clamp 1206. The clamp 1206 prevents inadvertent separation of the outlet port connector 1202 and the first catheter hub 602. The clamp 1206 can be released or removed by controlled effort but not inadvertently. Other suitable clamps 1206 can include devices such as, but not limited to, hinged clamps, threaded fasteners, hook and loop fasteners, bayonet mounts, clips, and the like. The stub tube 1232 is a short axially elongate hollow tube that penetrates a short distance into the first catheter hemostasis valve 604 without blocking any purge ports or lines. The stub tube 1232 can further comprise an obturator (not shown) with a tapered distal end that fits through the lumen of the filter 1100 and the stub tube 1232 projecting out and leading the stub tube 1232 through the pinhole or membrane of the first catheter hemostasis valve 604. After the stub tube 1232 is in place, the obturator can be removed. The stub tube 1232 is configured to fluidically seal with the hemostasis valve 604 such that fluid cannot leak around the stub tube 1232.

The clamp 1206 grasps the outlet connector 1202 in a complimentary groove 1204. The clamp 1206 can further comprise locks to prevent it from coming disengaged from the groove 1204, the first catheter hemostasis valve 604, or both. The second catheter 116 comprises the second catheter tube 140 that projects through the filter hemostasis valve 312, through the central chamber 616, through the outlet connector 1202 and stub tube 1232 and through the central lumen of the first catheter tube 144. The purpose of the filter 1100 is to remove any air adhered to the second catheter tube 140 and route that air into the gas separator module housing 720 from which it can be removed through the gas separator outlet port 802 (see FIG. 11A). It is the exposure of the first catheter tube 144 within the central chamber 616 to a high velocity fluid vortex that removes any attached bubbles of air and routes those bubbles toward the central axis of the central chamber 616.

The motor 622 (see FIG. 11A) is coupled to the impeller 1008 by a magnetic coupler comprising the motor magnetic coupler 1216, which is affixed to the shaft of the motor 622 and spins therewith. The motor magnetic coupler 1216 comprises the magnets 1214 that are affixed thereto and spin with the motor magnetic coupler 1216. The impeller 1008 is affixed to the impeller shaft 1208, which is affixed to the impeller magnetic coupler 1210 which comprises the magnets 1212. The magnets 1212 are configured with their north and south poles opposite those of the magnets 1214 of the motor magnetic coupler 1216. Thus, the north of the magnets 1212 is attracted to the south of the magnets 1214 and is repelled by the north of magnets 1214. The spinning motor magnetic coupler 1216 causes the impeller magnetic coupler 1210 to spin therewith about a concentric axis. This magnetic coupling permits the impeller 1008 to be driven by the motor 622 without the need for the motor shaft 614 to penetrate into the liquid filled chamber 616. Such rotating seals with the motor shaft 614 penetrating the liquid filled chamber 616 can be functional in many cases but a risk of leakage is always present, even if the rotating seal 728 is lubricated with a slippery material such as silicone fluid or fluorosilicone fluid. The rotating seals also tend to have high resistance and cause the motor 622 to generate more force and use more energy than would be required with a magnetic coupling with reduced friction. The rotating seals 728 thus steal and drain energy from the system more so than do the magnetic couplings. Typical rotating seals 728 can comprise O-rings or quad rings fabricated from materials such as, but not limited to, silicone rubber, BUNA, and the like. The magnetic coupling further has the advantage of never leaking through this seal 728 since the chamber 616 is completely sealed from the motor and its shaft. The motor magnetic coupling 1216 is separated from the impeller magnetic coupling 1210 by a wall of the housing 1102.

In the case of the magnetic coupling configuration, as shown, the seal 728 can be configured as a low friction bushing fabricated from brass, fluoropolymers such as PTFE, FEP, PFA or other low friction material, or the like and the seal 728 does not have to seal against liquid leakage and can be much more loose so friction losses are minimized. The seal 728 can also comprise roller or ball bearings fabricated from, for example, stainless steel, titanium, and the like.

The side channels 704 are configured integrally, or affixed, to the chamber housing 1102 and are operably connected with the central volume 616. The side channels 704 have their entrance 706 near the radial periphery of the chamber 616 and experience high fluid pressure. The liquid (blood, water, etc.) exits the side channels 704 through the bottom manifold 714 and flows back into the main chamber 616 near its axial center through ports 722. The ports 722, being located near the longitudinal central axis of the chamber 616 experience very low fluid pressure because of the vortex being generated therein. The fluid flows from the high pressure region at entrance 706 to the low pressure region 722. This fluid flow returns fluid that has been removed of at least a portion of its air or gas content to the chamber 616 for additional processing and air removal by the vortex being generated by the spinning impeller 1008. As the fluid moves from the bottom of the chamber 616 toward the top and out the entrances 706 to the side channels 704, air or gas is entrained therein and flows upward also but is constrained toward the center of the chamber by the vortex to move into the gas separator housing 720 where it can be removed from the filter 1100 through port 624 (FIG. 11A). The membrane 1226, which is supported by the perforated support structure 1228, can be configured to pass only gas and not a significant amount of liquid at specific operating pressure drop ranges, as described herein. The membrane 1226 can range in thickness from about 0.005 inches to about 0.025 inches and preferably between about 0.010 to about 0.020 inches. In an exemplary embodiment, the membrane 1226 has a thickness of between about 0.010 and 0.015 inches and a pore size of about 0.45 microns. The membrane support structure 1228 can be fabricated from a rigid polymer or metal and have pores or holes that permit gas passage but sufficient structure so as to prevent the membrane 1226 from billowing upward away from the chamber 616. The membrane 1226 is preferably sealed around its edges such that air cannot pass around the membrane 1226 from chamber 1224 into chamber 1230.

The gas separator housing 720 is divided into two chambers, the lower chamber 1224 and the upper chamber 1230. The lower chamber 1224 and the upper chamber 1230 are separated by the membrane 1226 and the membrane support 1228, which prevents the membrane 1226 from billowing up into the upper chamber 1230 under the applied pressure drop of a syringe, or some other vacuum source, attached to the gas extraction port 624. The lower chamber 1224 collects liquid and gas. The applied, controlled, pressure drop across the controlled porosity membrane 1226 pulls the gas but not the liquid across the membrane 1226 into the upper chamber 1230 from which it is permanently separated from the main chamber 616 and can be removed from the system.

The second catheter tube 140 projects across the perimeter of the internal volume 616 and is routed from the inlet port 312 to the outlet port 1202. The second catheter tube 140 can be straight but it can often be quite curved. Some catheters used for electrophysiology studies have a pre-formed curve that is completely circular forming a shape called a lasso. Such highly curved catheters need to be able to traverse across the gap between the inlet port 312 and the outlet port 1202 without missing the outlet port 1202. To facilitate passage of this second catheter tube 140, the entrance to the outlet port 1202 can be formed as a funnel or chamfer to guide the second catheter tube 140 into the outlet port 1202. In other embodiments, the shell 1102 of the filter 1100 can comprise one or more catheter guides 1220 affixed, or integral, to its interior. These catheter guides 1220 can comprise side walls that are circumferentially disposed or disposed along the longitudinal axis of the second catheter tube 140. The catheter guides 1220 are configured to not block the circumferential fluid flow within the chamber 616. The catheter guides 1220, in some embodiments, can comprise polymeric walls of about 0.010 to about 0.1 inches thickness and project inwardly toward the center of the filter 1100 sufficiently to constrain any second catheter tube 140 deflection. The catheter guides 1220 can further comprise a partial covering to further constrain and funnel the second catheter tube 140 into the outlet port 1202 but the catheter guide should not completely cover the second catheter tube 140 or hide it from the circumferential fluid flow within the chamber 616.

FIG. 13 illustrates a close-up view of the air filter 1100 of FIG. 12. In partial cross-section, without the associated catheters attached thereto. The filter 1100 is shown in partial cross-section as described by the section lines A-A in FIG. 11B. The catheter or sheath air filter 1100 comprises the housing 1102, the motor shaft 614, the impeller magnetic coupler 1210, the impeller shaft 1208, the fluid return manifold 714, the vaneless shear impeller 1008, the main chamber internal volume 616, the inlet hemostasis valve 312 further comprising a purge port 1218, the one or more return fluid channels 704, the one or more fluid channel inlet openings 706, the gas separator collection volume 1224, the gas separator membrane 1226, the gas separator membrane support 1228, the gas separator outlet volume 1230, the gas separator housing 720, the gas collection shroud 1002, the catheter guide channel 1220, one or more de-bubbler units 1322, the one or more return outlet orifices 722, the impeller shaft bearing 728, the one or more impeller magnetic coupler magnets 1212, the one or more motor magnetic coupler magnets 1214, the motor magnetic coupler 1216, a seal wall 1310, the outlet port 1202 further comprising the groove 1204, and the short outlet tube stub 1232. The housing 1102 further comprises, on its interior, the inlet port exit 1304 and the outlet port entrance 1302. The general direction of the fluid flow 1306 within the filter 1100 is illustrated with arrows although there exists also a circumferential flow field 1308 within the chamber 616, which can also be termed a vortex.

Referring to FIG. 13, the fluid flow 1306 is a circular vortex rotating about its axis which is substantially the same as the longitudinal axis of the housing 1102. The inlet port 312 further comprises the inlet port chamber exit 1304 while the outlet port 1202 further comprises the outlet port chamber entrance 1302. The catheter guide 1220 is configured to assist with guiding the second catheter tube 140 (see FIG. 12) into the outlet port chamber entrance 1302 with minimal difficulty on the part of the user.

The one or more de-bubbling units 1322 can be affixed within the return lines 704 or near the top of the walls of the chamber 616. The de-bubbling units 1322 can comprise coarse mesh open cell foam and can optionally be coated with an adherent surfactant to further eliminate bubbles from the system. The de-bubbling units 1322 can be fabricated from polyurethane foam, polycarbonate foam, or other suitable biocompatible open cell foam, mesh or other coarse porous structure.

The cowling 1002 of FIG. 12 is not present in the embodiment shown in FIG. 13. The gas collection shroud 1002 of FIG. 12 can be reduced, perforated with windows, or removed on one or more sides to facilitate de-bubbling of the interior of the chamber. In FIG. 13, there is only one return duct 704 and the gas collection shroud 1002 is eliminated approximately 20% to about 40% of its circumference on the side away from the entrance 706 to the return duct 704. The cowling 1002 can be perforated with holes or windows to permit gas to move from the exterior of the gas collection shroud 1002 to the interior of the gas collection shroud 1002 during priming or during operation.

It is preferential, but not essential, that the circular fluid flow 1308 within the chamber 616 rotate against, or toward, the inlet port 1304 into the chamber 616. By rotating with the tangential fluid velocities generally moving proximally with regard to the system and toward the inlet port 312, liquid with any entrained air or gas is less likely to be inadvertently injected into the entrance 1302 to the outlet port 1202. In the view of FIG. 13, the inlet port chamber exit 1304 and the outlet port chamber entrance 1302 are on the side of the housing 1102 opposite the viewer and on the other side of the impeller 1008. Thus, looking down on the system toward the top (where the gas separator housing 720 resides) the preferred flow is counterclockwise. If the inlet port 312 and its outlet 1304 were coaxially aligned with the outlet port 1202 and its entrance 1302 on the side of the chamber 1102 toward the viewer and on the viewer side of the impeller 1008 in this view, the preferred flow would be clockwise looking down from the top.

The motor 622 is sealed from the liquid interior volume 616 by the seal wall 1310. The impeller magnetic coupler 1210 rides within the region where liquid can reside and is separated from the motor magnetic coupler 1216 by the seal wall 1310.

The impeller 1008 comprises an axially elongate structure that spins about its axis on the impeller shaft 1208. The impeller 1008 is narrower at the bottom to permit flow from the chamber return ports 722 to flow past the impeller 1008. The impeller 1008 is narrower at the top to permit fluid to rise toward the gas separator housing 720 with minimal resistance. The axial center of the impeller 1008 can be increased in diameter to improve efficiency at driving the fluid vortex. The impeller 1008 beneficially comprises no substantial vanes or edges that can churn the fluid or generate cavitation at the high rotation rates of its operational state.

The impeller 1008 and the impeller shaft 1208 need to rotate concentrically about their longitudinal axis, such that wobble is minimized, in order to minimize cavitation. Furthermore, the rotation rate of the impeller 1008 may be limited to a range below which cavitation and bubble generation by the impeller 1008 are substantially eliminated or reduced. For example, in some embodiments with the impeller 1008 design illustrated in FIG. 13, a rotation rate of between about 1,500 and about 3,500 RPM may provide adequate vortex generation without excessive bubble generation or cavitation.

FIG. 14A illustrates a shear impeller 1400 comprising screw threads 1408 on its intermediate region 1406. The shear impeller 1400 comprises a distal conical region 1402, the intermediate region 1406, a proximal end 1404, and an impeller shaft hole 1410. The threads 1408 are configured to increase the surface area of the impeller 1400 to provide additional shear grip on the fluid through which it turns without generating cavitation. The threaded impeller 1400 generally runs at a lower rotation rate than a non-threaded impeller in order to eliminate or minimize any cavitation in the fluid. The threads 1408 are formed integral to, or affixed to, the exterior surface of the impeller 1400. The threads 1408 are configured so that when the impeller spins about its longitudinal axis, fluid passes around the impeller 1400 and is forced from proximal to distal. The thread 1408 pitch and configuration are carefully formed to prevent cavitation. The threads have a gentle lead-in and the edges are tapered. The distal end of the threads is tapered. The threads are carefully cut or formed so that there are no bumps or deformities that could generate cavitation. Thread 1408 pitches of between about 10 and 100 threads per inch are suitable for rotation rates of about 1,000 to about 7,000 RPM and preferably between about 1,500 and about 4,000 RPM. There are no approximately or generally longitudinally disposed vanes on the impeller 1400 and the impeller 1400 works as a shear impeller with the threads 1408 increasing the surface area grip on the fluid as well as driving or pumping the fluid distally. The threads 1408 are beneficially located on the region of the impeller 1400 which has the largest diameter, which is, in the illustrated embodiment, the intermediate region 1406. The distal end 1402 is tapered to allow the fluid to flow inward toward a gas trap or gas separator unit with minimum wake effects.

FIG. 14B illustrates a double threaded shear impeller 1450 comprising a distal end 1462, a distal thread 1458, a tapered intermediate region 1452, a threaded intermediate region 1454, a proximal region 1456, and an impeller shaft 1460. The threaded intermediate region 1454 serves the same area increase function as the threads 1408 of FIG. 14A. The distal thread 1458, however, serves as a fluid pump to force air laden fluid upward into the gas separator or gas trap (not shown). The threads 1454 and 1458 are configured so that clockwise rotation when looking from the proximal end of the impeller forces fluid distally. Both threads 1458 and 1454 are wound in the same direction and have approximately the same thread pitch, although some difference in pitch of one of the threads can benefit performance, depending on rotation rate and other conditions.

FIG. 15A illustrates a shear impeller 1500 comprising an exterior ring 1504, a core 1502, an impeller shaft hole 1510, an optional external thread 1508, and a plurality of ring connectors 1506. The exterior ring, or shroud, 1504 and the core 1502 serve as shear impellers to rotate the flow without generating cavitation. The threads 1508 serve to increase the surface area of the exterior ring 1504 and to force fluid to move distally toward the tapered tip of the core 1502. The ring connectors 1506, of which two are illustrated but which can number from about 1 to about 10 can be configured as being disposed totally laterally with no pitch, or the ring connectors 1506 can be configured with some pitch, similar to that defined for the threads 1408 of FIG. 14A. The trailing edges of the ring connectors 1506 are beneficially tapered to a very thin thickness so that the wake region is minimized to eliminate cavitation. The ring connectors 1506 can be configured as airfoils, simple or complex, with distal surfaces having greater arc length than proximal surfaces such that lift is generated. The shear impeller 1500 is generally disposed within a circular, axially elongate chamber (not shown) with the fluid inlet to the chamber disposed within the outer ring 1504. However, a preferable configuration is to provide a fluid inlet to the chamber that exits both inside and outside the shroud or ring 1504 such that fluid flow moves both interior to the ring 1504 and exterior to the ring 1504. Flow exterior to the ring 1504 is important so that fluid moves from proximal to distal past a catheter shaft exposed tangentially near the outside extents of the axially elongate chamber and moves any air and fluid toward the distal end of the chamber where air can be removed and liquid re-circulated.

FIG. 15B illustrates a large diameter shear impeller 1550 comprising a proximal surface 1554, a distal surface 1552, a distal tip 1558, an intermediate region 1556, and an impeller shaft 1560. The shear impeller 1550 is much wider than the impellers 1400 and 1450 but is similar in diameter to the ring 1502 of the impeller 1500. Fluid can still flow past the impeller 1550 and around its intermediate region 1556. The impeller 1550 comprises a large external surface area and threads may be less useful but can be added, especially in the intermediate region 1556. This large diameter impeller 1550 forces liquid radially outward from an entrance point near the shaft 1560 such that flow near the periphery of a chamber (not shown) in which it is disposed is very strong and can wash away air bubbles affixed to catheters by surface tension and move the air toward a central gas trap. The large diameter impeller 1550 is especially useful in short length chambers but can also function in longer length chambers. The distal end 1558 can also be configured as a teardrop such that it tapers at increasingly smaller angles moving distally until it reaches an approximate point such that wake flow is least disturbed around the distal end 1558 of the impeller 1550.

FIG. 16 illustrates a catheter air filter 1600 comprising the elements of the filter 1200 of FIG. 12 such as the chamber 616, the chamber walls 1102, and a single return duct 704, but with the addition of an electromechanical shaker 1602, a power supply and controller 1604, and an electrical bus 1606. The electromagnetic shaker is disposed in physical contact with the housing 1102 (either inside or outside the housing), such that vibrations of the shaker are transmitted to the chamber. The shaker may be directly or indirectly fixed the housing 1102. The electromechanical shaker 1602 can function at subsonic ranges of from about 10-Hz to about 20-Hz, audible ranges of about 20-Hz to 20,000-Hz, or ultrasonic ranges of about 20-kHz to about 5-mHz. Preferred operating frequencies are in the ultrasonic range from about 20-kHz to about 1-mHz. The electromechanical shaker 1602 can be affixed to the chamber wall 1102 as illustrated and can also be provided as a probe (not shown) that extends through the chamber wall 1102 into the fluid chamber 616. In the device illustrated in FIG. 16, there is only a single return duct 704.

FIG. 17 illustrates a catheter air filter 1700 comprising the elements of the filter 1200 of FIG. 12 but with the addition of a fluid line 1706, a container or bag 1702 filled at least partially with a liquid 1704, and a drip chamber 1708. The bag 1702 of liquid 1704 is elevated to a specified height above the hemostasis valve 312 and the fluid line 1706 is affixed at one end to the purge port 1218 of the hemostasis valve. The fluid line 1706 is operationally connected such that the lumen of the fluid line 1706 is in fluid communication with a central lumen (not shown) of the hemostasis valve 312 which is in fluid communication with the interior 616 of the filter 1700. Thus the liquid 1704 pressurizes the interior chamber 616 to a pre-defined level. This pressure is chosen such that the chamber 616 is pressurized sufficiently to force air through the membrane 1226 but liquid, such as blood, water, saline, heparin, etc., in the chamber 616 is not forced through the membrane 1226. The preferred pressure can range from about 1 mm Hg to about 50 mm Hg for venous applications and from about 80 mm Hg to about 300 mm Hg for arterial applications. These pressures can normally be supplied by pressure returning from the sheath 144 which extends into, and is in fluid communication with circulating blood in the patient at the ambient arterial or venous pressure but blockage of the sheath 144 by the inserted catheter 140 can interfere with such pressure transmission into the chamber 616. The fluid container or source 1702 can be connected to the port 1218 by the fluid line 1706 and the pressure can be generated and controlled with a liquid pump.

Ideally, it is beneficial for a catheter filter to be able to operate no matter what its orientation since they are subject to twisting, turning, axial advancement and withdrawal, bending, and the like. Practically, it is beneficial for the filter to operate within a wide range of orientations and for function to be restored if the catheter filter is oriented outside of its specified orientation but is then returned to within specified orientations.

Cavitation can occur if the impeller runs too fast, lacks adequate concentricity, comprises vanes, or comprises any other type of defect. Thus cavitation can occur when trying to generate the strongest vortex with high velocities or vanes on the impeller. However if the impeller surface area is too small, this geometry restricts the ability of the shear impeller to force the fluid into a rotational vortex of sufficient strength to work in this application.

Cavitation is the tendency of gas to come out of dissolution in a liquid when extremely low pressures occur in the liquid. The gas bubbles can re-collapse causing erosion of structures such as the impeller or the gas bubbles can remain in the liquid and defeat the purpose of a system configured to remove gas from the liquid. The operation al time of a gas filter in a surgical or catheter lab setting is not necessarily going to generate sufficient damage to the impeller or other filter structures to cause a problem, but this is always a possibility. However, the generation of bubbles in the liquid is a very real problem. Impellers with vanes cannot run at the velocities needed in this application without causing severe cavitation. The rotation rates in a filter having an internal chamber diameter of around 1.2 to 1.4 inches need to be in the 3,000 to 8,000 RPM range and preferably between about 4,000 and 7,000 RPM. The maximum diameter of the impeller should not be too great because fluid returning to the chamber from the return channels enters as close to the centerline axis of the chamber as possible and then moves toward the top of the chamber. The impeller cannot stop, impede, or substantially (functionally) disturb this flow from moving from the bottom to the top of the chamber. In exemplary embodiments for the chamber outlined above, the impeller diameter ranges from about 0.2 to about 0.75 inches with a preferred diameter of about 0.3 to about 0.5 inches. The length of the impeller can preferably range from about 0.5 inches to about 1.0 inches. The impeller is preferably tapered at the distal (downstream) end to allow the flow to collapse into the gas collection apparatus. The impeller is also preferably tapered at its proximal (upstream or leading end) end to allow flow to move around the impeller without restriction.

It can be beneficial for the dynamic catheter air filter to comprise a return channel to permit liquid that has been separated from the gas to return into the chamber. In some embodiments, the filter can comprise one return channel while, in other embodiments, a plurality of liquid return channels can be used. It is preferable to use a single return channel from the standpoint of purging air or gas from the system prior to use, however. The single liquid return line is beneficially disposed such that when the chamber is lying on its side or angled toward one side, the return line resides at either the top or the bottom, with respect to gravity. In a preferred embodiment, the return line resides on the bottom of the chamber such that a separate purge line for the return channel is not needed. The top of the return channel is operably connected near a periphery of the system chamber to generate high pressure at the entrance to the return channel. Since the bottom of the return channel is connected near the center of the chamber, the vortex generates low pressure there. Thus, the return line experiences a fluid pressure drop that maintains flow from the top of the chamber to the bottom of the chamber.

Purging all air from the system enhances its function. A separate purge port can be generally affixed and operably connected near the entrance to the return channel. This separate air purge port is generally useful if the return channel is located near the top side of the chamber, again the top side being with respect to the pull of gravity and the side meaning the side of the generally cylindrical or conical chamber. However if the return line is located on the bottom (w.r.t. gravity) side of the chamber, any air caught in the return line generally migrates into the main chamber where it can be removed through the gas separator. The gas separator can beneficially comprise a shroud that projects partially into the chamber to channel any air from the chamber into the gas separator. The shroud can further comprise windows, openings, fenestrations, holes, or other structures to permit any air residing in the chamber axially above the lip of the shroud to migrate or be pulled past the walls of the shroud and into the gas separator where it is removed from the chamber.

Since the dynamic catheter air filter is an axially elongate structure comprising a cylindrical, conical, frustoconical, or other circular geometry which may be a combination thereof, the filter length can reduce its stability in the upright position. Thus, the filter may tend to fall onto its side. In use, it is beneficial for the filter to be able to operate in almost any orientation, thus the need for a very strong vortex. The filter can be configured easily to operate in the vertical position where gravity provides assistance with its function. As the filter is tilted away from vertical, the vortex becomes defeated by gravity unless the vortex is able to overwhelm gravity. With a strong vortex, achievable by the embodiments illustrated above, the device can function when tilted on its side, or even when it is upside-down. Thus, during use, a surgeon need not grapple with the device to keep it in any particular orientation.

The expanded diameter region permits the entrance to the return channel to be as radially far from the chamber axis as possible, thus generating a maximum pressure drop and flow rate in the return channel. In the tapered configuration, it is important to maintain the entrance to the return line as far from the centerline of the chamber as possible given the tapering of the top.

It is beneficial for flow within a sheath or introducer, or the through lumen of a catheter for that matter, to move away from the patient in a controlled manner. Of course bleeding or hemorrhaging is clinically unacceptable but controlled withdrawal of blood retrograde through a catheter can prevent air, thrombus, or other emboli from migrating into the blood stream. In some embodiments, the catheter air filter can be configured such that liquid or fluid leaving the air filter chamber near the top is routed into a separate chamber where it can be collected and routed back to the patient. In the primary embodiments disclosed herein, the blood and other liquids are routed or pumped back into the chamber so that there is substantially no blood loss from the patient during the procedure. In some embodiments, however, the blood and liquid can be routed through a channel, tube, or lumen, into the arterial system after leaving the catheter air filter chamber. In preferred embodiments, however, the blood and liquid is routed back into the venous side of the patient's cardiovascular system. The venous side is preferable to the arterial side for functional reasons. The venous side is generally at a lower pressure (<50 mm Hg) than the arterial side (>100 mm Hg). Thus the pressure generated by the impeller pump in the chamber of the catheter air filter, or a separate external pump, can be sufficient to force blood back into the venous side of the patient. In some embodiments, the fluid entering the feedback or return channel of the catheter air filter can be routed both back into the chamber and back into the patient's vascular system.

The separate chamber disclosed herein can be used as a de-bubbling chamber, filter, cardiotomy reservoir, or the like. A separate pump outside the catheter air filter chamber can be used to pump blood either through the separate chamber and into the patient or it can be used to pump the blood from the separate chamber back into the patient. The separate chamber is preferably small, having a volume of about 0.25-cc to about 50-cc with a preferred range of about 1-cc to about 20-cc.

The blood can be pumped back into the patient for example, in the femoral vein or other vein of the legs or arms. Thus, any air or other debris enters the blood stream past the capillary beds of the systemic circulation minimizing the risk of an ischemic event in the heart or brain.

FIG. 18 illustrates a side, partial breakaway view of a dynamic catheter air filter 1800 comprising the impeller shaft 1208, the impeller 1816, the main chamber internal volume 616, the inlet port 1802 further comprising a purge port 1218, the one or more return fluid channels 704, the gas separator collection volume 1224, the gas separator membrane 1226, the gas separator membrane support 1228, the gas separator outlet volume 1230, the gas separator housing 720, the gas collection shroud 1002, the second catheter 116 further comprising the second catheter shaft 140, the first catheter tube 144, the one or more return outlet orifices 722. The dynamic catheter air filter system 1800 further comprises the fluid reservoir 1702, the volume of fluid 1704, and the fluid drip line 1706. The catheter or sheath air filter 1800 further comprises a motor drive 1804, a motor controller 1806, a power supply 1808, an electrical line or bus 1810, one or more electrical bus to fluid line connectors 1812, and a power supply fastener 1814.

Referring to FIG. 18, the motor power supply 1808 and the controller 1814 are separated from the main body of the dynamic catheter air filter 1800 to minimize weight and bulk. They controller 1814 is operably connected to the motor drive 1804 by the electrical bus 1810, which comprises a plurality of wire leads. The motor drive 1804 is preferably a brushless DC motor or servomotor to minimize electrical interference with other hospital equipment that might be in proximity to the system. The electrical bus 1810 can comprise between 2 and 20 or more separate electrical leads at least some of which, or all, are electrically isolated from each other. For the sake of minimizing interference in the surgical field, the electrical bus 1810 is routed substantially along the fluid drip line 1706 which is operably connected to the internal fluid volume of the system 1800 at the purge line inlet port 1218. The electrical bus 1810 is affixed to the fluid drip line 1706 in at least one location by the connector 1812. In a preferred embodiment, the electrical bus 1810 is affixed to the fluid drip line 1706 along substantially most of its length. In other embodiments, the electrical bus 1810 is formed substantially integrally to the fluid drip line 1706. The controller 1806 and the power supply 1808 are affixed at, to, or near the fluid reservoir 1702 by the connector 1814. The connector 1814 can affix the controller 1806, the power supply 1808, or both to a hook, a support, from which the fluid reservoir 1702 is affixed, or to the fluid reservoir 1702, itself. The power supply 1808 is preferably a direct current (DC) power supply provided by a battery, capacitor, or similar device to keep it separate from alternating current (AC) power supplies, which can be more dangerous.

FIG. 19 illustrates the combination of the air filter system described above with an angiographic power injector, to prevent air from passing into a patient when said air is entrained along with contrast fluid being injected through a catheter into a patient. The dynamic catheter air filter system 1900 comprises the impeller shaft 1208, the impeller 1816, the main chamber internal volume 616, the inlet port 1902 further comprising the purge port 1218 and the exit opening 1912 into the chamber volume 616, the one or more return fluid channels 704, the gas separator collection volume 1224, the gas separator membrane 1226, the gas separator membrane support 1228, the gas separator outlet volume 1230, the gas separator housing 720, the outlet port chamber opening 140, the outlet catheter 144, and the gas collection shroud 1002. The dynamic catheter air filter system 1900 further comprises the fluid reservoir 1702, the volume of fluid 1704, and the fluid drip line 1706. The catheter air filter 1900 further comprises the motor drive 1804, the motor controller 1806, the power supply 1808, the electrical line or bus 1810, the one or more electrical bus to fluid line connectors 1812, and the power supply fastener 1814. The dynamic catheter air filter system 1900 further comprises a fluid injection line 1908 further comprising a lumen 1910, and a fluid injection system 1906.

Referring to FIG. 19, the fluid injection system 1906 can comprise a power injector, such as a MEDRAD® power injector, or other mechanisms such as, a syringe with plunger, a pump, or a gravity fed system such as the bag 1702, or the like. The catheter tube 144 can be the primary catheter or it can be an axially elongate line affixed to and operably connected to a catheter that is inserted into a patient and routed into the vasculature.

Such systems as described in FIG. 19 can be especially useful when catheters are routed to the coronary arteries or the cerebrovasculature for the purpose of diagnostic and therapeutic procedures. For example, patients undergo cardiac catheterization to determine if there is blockage in their coronary arteries. This procedure involves placing the catheter and then injecting radiopaque dye (contrast agent) into the coronary arteries. A fluoroscope or other X-ray machine can observe and record images of the dye in the vessels (arteries or veins) and narrowing of said vessels can be detected. However, inadvertent injection of air can kill or severely injure a patient. The dynamic catheter air filter, when placed in line with the fluid being injected, can remove any air that is inadvertently passed into the system.

In the illustrated embodiment of FIG. 19, the inlet port exit window 1912 into the chamber 616 is located higher than the outlet port window 1410 because the air will be buoyant and thus an extra degree of separation is provided to keep air from entering the outlet port window 140 and subsequently into the outlet catheter 144. While this is preferred, the inlet port 1902 and the outlet catheter 144 can be aligned at the same height. The inlet port 1902 and the outlet catheter 144 need not be aligned coaxially in this embodiment but can be operably connected along different axes.

Liquid and air injected into the chamber 616 through the inlet port 1902 enter the chamber through the window 1912. The impeller spins the liquid in the chamber into a vortex forcing lightweight air toward the center of the chamber and the heavier liquids toward the outside, where the liquid is drawn off into the outlet port or window 140 and into the catheter 144 where it is forced under pressure into the patient. The air or other gas, coerced to the center of the chamber 616 by centrifugal and buoyancy effects is moved toward the gas collection volume 1224 where it is staged prior to removal from the system through the semi-permeable membrane 1226.

In use, the power injector and air filter will be used into inject contrast media into the patient through the housing 1102 and the catheter 144. A surgeon will secure the outlet of the power injector to the input of the air filter, and connect the outlet of the air filter to the proximal end of the catheter. While operating the air filter, to rotate the impeller, the surgeon will operate the power injector to force contrast media through the air filter and then into the catheter, and eventually into a blood vessel to be imaged with the help of the contrast media. As the contrast media flows through the air filter, the operation of impeller serves to strip any air entrained in the contrast media. The impeller also serves to agitate and mix the contrast media. This method may be used to inject other solutions useful for other imaging methods such as MRI.

The fluid bag 1702, and its associated equipment are optional and not necessary for the system 1900 to function but may be useful for other reasons. The power supply 1808 and controller 1806 can be affixed to the power injector system or otherwise located. In other embodiments, the power supply itself 1808 can draw from AC “house current” with suitable protections for the patient in place and need not be a battery. Referring to FIG. 18, there is no hemostasis valve in this system embodiment although, again, a hemostasis valve 1802 at the inlet port 1902 to the chamber 616 can be of benefit and could be used for other reasons.

The system embodiments disclosed herein are sensitive to the types of fluids enclosed within the chambers or inner volumes of the shells. Fluids with higher viscosity will be more effectively gripped by the rotating impeller, especially the impellers that are smooth and use fluid shear to grip the fluid and create a vortex. However, higher viscosities will slow the migration rate of the gas bubbles toward the center of the vortex and the drag of the fluid on the shell will correspondingly increase. The effects of viscosity on rotation rate can be accounted for by adjusting the impeller size, shape, and rotation rate. Fluids with higher mass densities, such as radiographic contrast media, will have an amplified effect on the movement of bubbles because the bubbles will have greater buoyancy in those heavy fluids and will be forced more aggressively to the center of the vortex. Thus, heavier fluids with relatively lower viscosities will be more effective at bubble separation from the liquid, given the same fluid rotation rates.

While the preferred embodiments of the devices and methods have been described in reference to the environment in which they were developed, they are merely illustrative of the principles of the inventions. The elements of the various embodiments may be incorporated into each of the other species to obtain the benefits of those elements in combination with such other species, and the various beneficial features may be employed in embodiments alone or in combination with each other. Other embodiments and configurations may be devised without departing from the spirit of the inventions and the scope of the appended claims.

Claims

1. An apparatus adapted for preventing gas from entering a first catheter upon insertion of a second catheter into the first catheter, said apparatus comprising: a shell, wherein the interior volume of the shell defines a chamber having a centerline;an impeller operable to rotate about or near the centerline of the chamber, wherein the impeller is located within the chamber and is configured to rotate liquid within the chamber;a catheter inlet port, in fluid communication with the chamber, located near a periphery of said chamber, said catheter inlet port in fluid communication with the chamber; anda catheter outlet port located near a periphery of said chamber, said catheter outlet port in fluid communication with the chamber;wherein the catheter inlet port is coaxially aligned with the catheter outlet port.

2. The apparatus of claim 1 further comprising a gas vent located near a central axis of the chamber, and in fluid communication with the chamber.

3. The apparatus of claim 1 further comprising a liquid return port.

4. The apparatus of claim 1 further comprising a gas collection chamber.

5. The apparatus of claim 1 wherein the proximal end of the catheter outlet port comprises a funnel to guide a flexible catheter into the lumen of the catheter outlet port.

6. The apparatus of claim 1 wherein said impeller spins at a rate of from 100 to 1,000 RPM.

7. The apparatus of claim 4 further comprising a gas vent to remove gas from the gas collection chamber.

8. The apparatus of claim 1 further comprising a pump to move liquid from a gas collection chamber to a liquid return port.

9. The apparatus of claim 1 wherein the interior surfaces of said chamber are coated with anti-thrombogenic materials.

10. The apparatus of claim 1 wherein said impeller is further operable to pump gas and liquid out of, or into, the chamber.

11. The apparatus of claim 1 wherein said catheter inlet port and catheter outlet port are located lower than the centerline of the chamber with respect to a gravitational vector.

12. The apparatus of claim 1 wherein said gas vent is located higher than the catheter inlet and outlet ports.

13. The apparatus of claim 1 wherein said impeller is magnetically coupled to a motor drive.

14. The apparatus of claim 1 wherein said impeller comprises a plurality of vanes to spin the blood.

15. (The apparatus of claim 1 wherein said impeller comprises a substantially smooth outer surface to spin the blood using viscous or shear effects.

16. The apparatus of claim 1 wherein said catheter inlet port comprises a hemostasis valve, wherein the hemostasis valve is operable to substantially seal fluid from passing therethrough whether or not a catheter is inserted through the apparatus.

17. The apparatus of claim 1 wherein the shell, the impeller, the motor drive, the gas vent, the catheter inlet port, the catheter outlet port, the electrical power source, and all components are integrated into a single module with no flexible interconnections.

18. An apparatus adapted for preventing gas from entering a first catheter upon insertion of a second catheter into the first catheter, said apparatus comprising: a shell, wherein the interior volume of the shell defines a chamber having a centerline, a top end and a bottom end;an impeller operable to rotate about or near the centerline of the chamber, wherein the impeller is located within the chamber and is configured to rotate liquid within the chamber;a catheter inlet port located near a periphery of said chamber, said catheter inlet port in fluid communication with the chamber; anda catheter outlet port located near a periphery of said chamber, said catheter outlet port in fluid communication with the chamber;a gas vent located near the centerline of the shell;a gas separation chamber in fluid communication with the gas vent; anda liquid return line communicating from the gas separation chamber to the chamber of the shell.

19. A system for injecting contrast media into a patient, said system comprising: a power injector having an outlet;a catheter characterized by a proximal end and a distal end;an air filter comprising: a shell, wherein the interior volume of the shell defines a chamber having a centerline, a top end and a bottom end;an impeller operable to rotate about or near the centerline of the chamber, wherein the impeller is located within the chamber and is configured to rotate liquid within the chamber;a catheter inlet port located near a periphery of said chamber, said catheter inlet port in fluid communication with the chamber; anda catheter outlet port located near a periphery of said chamber, said catheter outlet port in fluid communication with the chamber;wherein the outlet of the power injector is in fluid communication with the inlet of the air filter and the outlet of the air filter is in fluid communication with the proximal end of the catheter.

20. A method of injection contrast agent into a patient, said method comprising the steps of: providing a system comprising: a power injector having an outlet;a catheter characterized by a proximal end and a distal end;an air filter comprising: a shell, wherein the interior volume of the shell defines a chamber having a centerline, a top end and a bottom end;an impeller operable to rotate about or near the centerline of the chamber, wherein the impeller is located within the chamber and is configured to rotate liquid within the chamber;a catheter inlet port located near a periphery of said chamber, said catheter inlet port in fluid communication with the chamber; anda catheter outlet port located near a periphery of said chamber, said catheter outlet port in fluid communication with the chamber;wherein the outlet of the power injector is in fluid communication with the inlet of the air filter and the outlet of the air filter is in fluid communication with the proximal end of the catheter.securing the outlet of the power injector to the input of the air filter, and connecting the outlet of the air filter to the proximal end of the catheter;While operating the air filter to rotate the impeller, operating the power injector to force contrast media through the air filter and then into the catheter, and eventually into a blood vessel of the patient.