Patent Description:
Field of the Invention. The present invention relates generally to the field of medical devices and methods. More specifically, the invention described herein relates to devices and methods for controlling clot removal from a patient's vasculature by aspiration thrombectomy.

Stroke is a significant cause of disability and death, and a growing problem for global healthcare. More than <NUM>,<NUM> people in the United States alone suffer a stroke each year, and of these, more than <NUM>,<NUM> people die. Of those who survive a stroke, roughly <NUM>% will suffer long term impairment of movement, sensation, memory, or reasoning, ranging from mild to severe. The total cost to the U. healthcare system is estimated to be over $<NUM> billion per year.

Stroke may be caused by a blockage in a cerebral artery resulting from a thromboembolism (referred to as an "ischemic stroke"), or by a rupture of a cerebral artery (referred to as a "hemorrhagic stroke"). Hemorrhagic stroke results in bleeding within the skull, limiting blood supply to brain cells, and placing harmful pressure on delicate brain tissue. Blood loss, swelling, herniation of brain tissue, and pooling of blood that results in formation of clot mass inside the skull all rapidly destroy brain tissue. Hemorrhagic stroke is a life-threatening medical emergency with limited treatment options.

Aside from cerebral stroke, thromboembolism throughout the vasculature, in both arterial and venous circulation, is characteristic of numerous common, life-threatening conditions. Examples of potentially fatal diseases resulting from thrombotic occlusion include pulmonary embolism, deep vein thrombosis, and acute limb ischemia. Acute pulmonary embolism is a significant cause of death in the United States, with roughly <NUM>,<NUM> patients dying each year. Pulmonary embolism can be a complication from deep vein thrombosis, which has an annual incidence of <NUM>% in patients <NUM> years and older. All of the aforementioned diseases are examples of conditions in which treatment may include aspiration or evacuation of clot and/or blood.

Of particular interest to the present invention, the Penumbra System® mechanical thrombectomy system is a fully-integrated system designed specifically for mechanical thrombectomy by aspiration. It is intended for revascularization of patients with acute ischemic stroke secondary to intracranial large vessel occlusion. A comparable system designed for the peripheral and coronary vasculature, the Indigo® System is also a mechanical thrombectomy aspiration system, designed for revascularization of patients with thrombotic occlusion of the peripheral vasculature. Both the Penumbra System and the Indigo System are commercially available at the time of filing the present provisional patent application and include aspiration or reperfusion catheters, aspiration tubing, other accessories, and an aspiration pump (sold under the tradename: Pump MAX™ aspiration pump or Penumbra Engine™ aspiration pump) for connection to the aspiration tubing and aspiration catheters. As illustrated in <FIG>, the Pump MAX™ aspiration pump <NUM> includes a base unit <NUM> which encloses a vacuum pump (not shown) which operates off line voltage. The base unit has an on-off switch <NUM> and a separate knob <NUM> for adjusting the level of vacuum provided by the pump. The vacuum level can be read on a pressure gauge <NUM>. Blood and clot are drawn into a collection canister <NUM> from an aspiration tube <NUM> (shown in broken line) which is connected to a reperfusion catheter (not illustrated) which has been introduced to the vasculature of a patient to aspirate clot. The blood and clot are drawn into the collection canister by a partial vacuum which is provided by a vacuum connector <NUM> on the base unit <NUM> which is connected to the vacuum pump, not shown. The vacuum from vacuum connector <NUM> is applied to a vacuum port <NUM> on a removable lid <NUM>. The vacuum connector <NUM> is connected to the vacuum port <NUM> by an external vacuum tube <NUM>.

Although very effective, clot aspiration using the Indigo System mechanical thrombectomy apparatus or other similar vacuum-assisted thrombectomy systems must sometimes be terminated due to the risk of excessive blood loss by the patient, especially when using large aspiration catheters. During aspiration thrombectomy, when the catheter tip falls out of contact with the thrombus or other occlusive material, the tip is exposed to healthy blood and full flow ensues. Under such conditions, the blood loss rate is excessive, and in some cases, may result in premature termination of the procedure. In one example, during a procedure when the catheter enters healthy blood and full flow ensues, the blood loss rate is in the range of <NUM>-<NUM> cc per second with an <NUM> French size catheter. With a maximum tolerable blood loss of <NUM>-<NUM>, the catheter cannot run in unrestricted mode for more than approximately <NUM> to <NUM> seconds. When a physician operates the system manually, the aggregate blood loss may reach an unacceptable level before sufficient clot is removed. In addition, reliably identifying whether the tip of the catheter is in contact with clot or is undesirably aspirating healthy, clot-free blood is a significant problem, and such manual control is not optimum.

During other procedures using the Penumbra System, such as, for example, neurovascular procedures for treatment of ischemic stroke, excessive removal of blood is less of a risk, and the primary focus of the procedure is maximization of removal of occlusive material. Optimizing both technique and aspiration control are of upmost importance for successful removal of occlusive material.

Therefore, it would be desirable to provide improved methods and apparatus for controlling the aspiration of thrombus and clot using aspiration catheters in combination with pumping consoles. It would be particularly useful to provide systems and methods which limit blood loss during such aspiration procedures such as by automatically stopping aspiration while the aspiration catheter is not in contact with clot or thrombus. Additionally, it would be desirable to provide systems and methods which optimize system performance, and procedures for removal of occlusive material. At least some of these objectives will be met by the inventions described herein below.

Description of the Background Art. The Penumbra System® as it is commercially available at the time of filing this provisional patent application is described in a brochure entitled "Science of Aspiration: The Penumbra System® Approach. " Relevant patents and patent publications include: <CIT>; <CIT>; <CIT>; <CIT>; <CIT>; <CIT>; <CIT>; <CIT>; <CIT>; <CIT>; <CIT>; <CIT>; <CIT>; <CIT>; <CIT>; <CIT>; <CIT>; <CIT>; <CIT>; <CIT>; <CIT>; <CIT>; and <CIT>.

<CIT> discloses a rapid aspiration thrombectomy system and method, in particular a device for removing a thrombus from a blood vessel, wherein the device optimizes the blood loss. It discloses a vacuum aspiration control system for use with a vacuum source (par. <NUM>) and an aspiration catheter (reference <NUM> <FIG>), wherein the system comprises a connecting tube (reference <NUM>, <FIG>) configured to connect the vacuum source with the aspiration catheter or component thereof; an on-off valve (par. <NUM>, a solenoid valve) configured to be operatively coupled to the connecting tube; a sensing unit configured to detect flow within the connecting tube and to produce a signal representative of such flow (reference <NUM>- <FIG>); and a controller (<NUM> -<FIG>) configured to receive the signal representative of flow through the connecting tube. However the controller has no effect on the valve and manual intervention is needed.

<CIT> discloses an aspiration monitoring system and method, in particular real time monitoring of catheter aspiration for removing a thrombus. In particular, it discloses a vacuum aspiration control system for use with a vacuum source (<NUM>) and an aspiration catheter (<NUM>), wherein said system comprises a connecting tube (<NUM>) configured to connect the vacuum source with the aspiration catheter or component thereof; an on-off valve (is equivalent to a one-way valve, paragraph <NUM>, <FIG>) configured to be operatively coupled to the connecting tube; a sensing unit configured to detect flow within the connecting tube and to produce a signal representative of such flow (par. <NUM>); and a controller configured to receive the signal representative of flow through the connecting tube. Here also the controller has no effect on the valve and manual intervention is needed.

The present invention provides systems and methods that improve catheter aspiration by enabling a longer procedure, by enhancing the ingestion of occlusive material, or both. In some examples, the amount of fluid flowing through an aspiration catheter under vacuum aspiration is monitored to determine whether the flow is unrestricted, restricted, or clogged. Depending on the determined flow state, the present invention may employ different techniques and methods to improve catheter aspiration. In one example, unrestricted flow is detected, and aspiration is automatically and temporarily restricted for blood saving purposes. This may beneficially prolong the time available to perform the procedure and thereby allow more complete removal of occlusive material. In another example, restricted flow is detected, and full vacuum aspiration is automatically applied. In yet another example, a clogged catheter is detected, and pulsed aspiration is automatically applied. This may beneficially enhance the ingestion of large, tough, or otherwise troublesome occlusions. Alternatively, pulsed aspiration, full aspiration, or restricted aspiration may be applied on demand by a user of the present invention.

In one example, which is not claimed, the systems and methods of the present invention address the problem of excessive blood loss through dynamic aspiration cycling. The nature and flowability of the material being withdrawn by the aspiration catheter is monitored so that the system can either allow continuous aspiration when in clot, or sampling of extraction rate to determine whether the tip of the catheter is in contact with clot, in order to reduce the risk of excess blood loss. While determining and monitoring of blood flow rate is disclosed in the exemplary embodiments below, other measurements of the flowability and/or structural composition of the aspiration effluent, such as monitoring the collection chamber's volume, monitoring the collection chamber's fill rate, visually monitoring the aspiration tubing (clot is darker than fresh blood), or placing a strain gauge on aspiration tubing, could also be used.

The systems and methods of the present invention may respond to variations in flow rate, pressure, differential pressure, or other indicators of the composition of the material inside or adjacent to an aspiration catheter in a sub-second time frame to limit the unnecessary aspiration of blood during a thrombectomy procedure. The present invention may be useful with any thrombectomy, embolectomy, atherectomy, or other catheter or probe system where blood and clot are withdrawn wholly or partially by application of a vacuum to the proximal end of any reperfusion, aspiration catheter or probe for the purpose of clot extraction.

In a first aspect, the present invention provides a vacuum aspiration control system for use with a vacuum source and an aspiration catheter. The system comprises a flexible connecting tube, an on-off valve, a sensing unit, and a controller. The connecting tube is linear in an unconstrained configuration and is configured to connect the vacuum source to an aspiration lumen in the aspiration catheter. The on-off valve is configured to be operatively connected to the connecting tube, and the sensing unit is configured to determine flow rate within the connecting tube and to produce a signal representative of such flow, typically as either unrestricted flow, restricted flow, or clogged. The controller is connected to receive the signal representative of flow through the connecting tube and to open and close one or more on-off valve(s) in response to the signal. In one example, the controller is configured to automatically close the on-off valve to stop flow through the connecting tube when the signal indicates unrestricted flow, e.g. that primarily healthy blood or blood free of vessel-obstructing clot is flowing through the connecting tube and/or that the catheter is substantially free from contact with clot or other occlusive material. In another example, the controller is configured to initiate pulsed aspiration when the signal indicates a clog, which may be caused by some occlusive material in or adjacent to the catheter or connecting tubing.

The controller is typically further configured to automatically open the on-off valve at a predetermined interval to sample effluent material through the connecting tube and the valve will typically only remain open if the signal indicates a return to clot. The controller algorithm is capable of deciphering the difference between healthy blood and clot independent of aspiration source and the inner diameter of the attached catheter.

The sensing unit may comprise any one or more of a variety of sensors, including differential pressure sensors, acoustic (including ultrasonic) flow sensors, optical flow sensors, thermal flow sensors, magnetic flow sensors, sensors which detect circumferential expansion of the connecting tube. While differential pressures are described in more detail below, it will be appreciated that any sensing unit capable of detecting when flow or extraction rate through the connecting tube is excessive and/or clogged, would be suitable for use in the present invention.

In exemplary embodiments, the sensing unit comprises a pair of pressure sensors at spaced-apart locations along the connecting tube to measure differential pressure. The controller can calculate flow based on the differential pressure and, from this, determine whether the calculated flow rate indicates unrestricted flow, restricted flow, or a clog.

In another embodiment, the sensing unit uses optical sensors that measure transmission, absorption, or both of light to characterize the contents flowing through the connecting tube. In one such example, visible light is used determine whether flow contains clot or is primarily clot-free. Typically, flow with clot is darker, which is detectable by optical sensors. Alternatively, the optical sensors may infrared, ultraviolet, visible light, or some such combination to analyze contents within the connecting tubing.

In another embodiment, the sensing unit uses circumferential expansion sensors to determine the contents flowing through the connecting tube. The internal pressure of the connecting tubing and the contents flowing through it effect the circumference of the connecting tubing. Under strong vacuum, such as during a clog, the tubing may maximally contract. During high flow of primarily clot-free blood, the tubing may contract only slightly. During restricted flow, the clots and blood may cause a relative expansion of the connecting tubing.

The on-off valve may also take a variety of specific forms. Typically, regardless of form, the on-off valve will comprise an actuator, such as a solenoid actuator, that is powered to open the valve. The valve itself may take a variety of forms, including a pinch valve, an angle valve, or any one of a variety of other valves that provide actuation. Alternatively, the manual on-off valve may be provided that allows a user to initiate and/or terminate functions and features of the present invention.

In further exemplary embodiments, the controller may be configured to open the valve and hold the valve open until a flow pattern which indicates unrestricted flow is detected whereupon the controller closes the valve. The controller may be further configured to automatically re-open the on-off valve. For example, in what may be referred to as "sampling mode", the controller may be further configured to periodically sample, or test flow to re-characterize flow and determine if it is safe to recommence aspiration. For example, the controller may periodically test flow by opening the on-off valve for a fixed time interval, in one embodiment <NUM> milliseconds, to establish a "test" flow. The test flow is characterized and, if it so indicates, the on-off valve may be reopened into a "treatment" mode to allow continued aspiration treatment. If the system characterizes the flow as unrestricted, e.g. excessive, then the system will dwell in a closed configuration for a fixed time interval, in one embodiment between a quarter second and two seconds, before an additional pressure differential sample is taken.

In other instances, however, the controller may not be configured to automatically reestablish flow when safe conditions have been reached. For example, the controller may be configured to allow a user to reposition the aspiration catheter and, after repositioning, manually open the on-off valve (typically by actuating a switch which causes the controller to open the on-off valve) to resume aspiration treatment. In such instances, the controller may immediately return to the "sampling mode," however, and if the reestablished flow is characterized as unrestricted flow, the controller will again close the on-off valve, and the user can again reposition the aspiration catheter in order to engage clot and manually resume aspiration. Such systems will typically provide a manual switch which allows the user to manually open the on-off valve.

The controller may be configured to control two or more valves. In one example, the controller controls a first on-off valve between an aspiration catheter and a vacuum source and a second on-off valve between an aspiration catheter and a pressure source with a pressure at least above that of the vacuum source. The controller may alternate between opening the first on-off valve and the second on-off valve to generate pressure variations within an aspiration catheter or tubing adjacent to such a catheter. The controller may sample flow while the first on-off valve is opened to determine whether an attached catheter is still positioned in clot or otherwise occluded. The controller may hold the first on-off valve open and the second on-off valve closed if no occlusions or clogs are detected.

In specific embodiments, the vacuum aspiration systems of the present invention comprise a base unit which incorporates at least one on-off valve and the controller. The base unit will typically be configured to be mounted directly on or near a vacuum pump or console and will usually include a connecting cable in order to receive power from the vacuum console or line and optionally exchange information with the controller and the vacuum console. The connecting tube typically has a proximal end configured to connect the vacuum source and distal end configured to connect to the aspiration catheter. In such instances, the vacuum aspiration system will typically further comprise an external unit configured to be secured to the connecting tube at a location between the distal end and the proximal end thereof. Exemplary external units comprise at least a portion of the sensing unit. For example, the sensing unit may comprise a first pressure sensor in the base unit and a second pressure sensor in the external unit. In those instances, the controller will typically be configured to determine if a differential pressure exists based on the signals from the first and the second pressure sensor.

In a second aspect, the present invention provides a vacuum aspiration method. The vacuum aspiration method comprises engaging a distal end of an aspiration catheter against an occlusion in the blood vessel. A vacuum is applied through an aspiration lumen of the aspiration catheter using a vacuum source coupled to a proximal end of the aspiration lumen by a connecting tube. In this way, portions of clot and other occlusive material may be drawn into the aspiration lumen, through the connecting tube, and into a collection receptacle by the vacuum source. Flow through the connecting tube is sensed, and a valve is automatically closed to stop flow through the connecting tube when the sensed flow exceeds a determined value while the vacuum source remains on. Flow through the connecting tube will be later reestablished by opening the valve, and the steps are repeated until a desired amount of clot has been aspirated.

In a third aspect, the present invention provides an assembly for generating pressure differentials that may result in pressure pulses to execute an extraction cycle. The assembly may include a fluid injection apparatus, a mechanical displacement apparatus, gravity induced pressure head, or a combination thereof. A fluid injection apparatus may provide a source of relative positive pressure for a catheter currently or previously under vacuum aspiration. For instance, the fluid may be at a pressure above that of the vacuum aspiration system, between full vacuum pressure and ambient pressure, at ambient pressure, between ambient pressure and systolic pressure, at systolic pressure, or above systolic pressure. The fluid injection apparatus may utilize an aperture, a valve, a pump, a pressure chamber, or some such combination. A mechanical displacement apparatus may physically displace the volume of a catheter system to provide relative increases and decreases of pressure depending on the direction of displacement. In one example, a mechanical displacement assembly assists vacuum recovery after a catheter has had its pressure increased above the pressure of the vacuum source.

In some embodiments of the present invention, the controller includes an algorithm that is used to interpret pressure sensor signals to determine whether the contents flowing through a catheter should be characterized as unrestricted, restricted, or clogged. Generally, unrestricted flow is a high flow that may be characterized as excessive and may be primarily or completely comprised of healthy blood, clot-free blood, or blood free of vessel-obstructing clot that is not helpful to aspirate, restricted flow may be comprised of a mix of healthy blood and clot or other occlusive material, and a clog may be caused by a clot or other occlusive material within an aspiration catheter, partially within an aspiration catheter, adjacent to an aspiration catheter, or in other connecting tubing attached to the aspiration catheter. In some examples, healthy blood is blood with a low enough proportion of cross-linked fibrin such that it is not sufficiently integrated to cause ischemia or other similar vessel occlusions. When the algorithm detects unrestricted flow, it may cause the system to initiate a sampling mode. When the algorithm detects restricted flow, it may cause the system to enable full vacuum aspiration. When the algorithm detects a clog, it may cause the system to generate a variety of pressure pulses with an extraction cycle. The algorithm may be responsive and adaptable to changing circumstances, such as changing to a catheter of a different size mid-procedure. The algorithm may adjust sampling modes and pressure pulse magnitudes if the catheter state remains static, changes too quickly, changes to slowly, or improves as expected.

In specific aspects of the method, the present invention may remove clot and other occlusive material from a blood vessel that comprises a vein or an artery. Sensing of flow may comprise one or more of differential pressure measurement, acoustic flow measurement, optical flow measurement, thermal flow measurement, measurement of circumferential expansion of the connecting tube.

In preferred aspects of the method, sensing flow comprises measuring the differential pressure using a first sensor located proximate the vacuum source and a second sensor located on or adjacent the connecting tube between the vacuum source and the aspiration catheter.

In still further embodiments of the method, the resuming flow through the connecting tube comprises opening the valve for a sub-second interval, detecting when the sensed flow is characterized as acceptable, and automatically resuming flow. Automatically resuming flow typically comprises automatically detecting when the sensed flow can be characterized as acceptable and the valve remains open as long as the flow is so characterized. Alternatively, resuming flow may comprise manually opening the on-off valve.

In further embodiments of the method, which are not claimed, pressure differentials are generated by closing a valve to a vacuum pump, opening a valve to a source of pressure, wherein the pressure is at least above that of the vacuum, and then re-opening the valve to the vacuum pump. Alternatively, or in combination, pressure differentials are generated by mechanical displacement, wherein a volume of a chamber is reduced to increase pressure within a catheter and a volume of the chamber is increased to decreases pressure within a catheter, whereby the actuation of the mechanical displacement chamber results in pressure differentials. The pressure differentials may be tailored to have a specific or dynamic amplitude and frequency that facilitates the removal of clot or other occlusive materials.

Some embodiments of the inventions of the present application are described below. For clarity, not all features of each actual implementation are described in this specification. In the development of an actual device, some modifications may be made that result in an embodiment that still falls within the scope of the invention as defined in the claims.

Referring to <FIG>, a vacuum system <NUM> of the type useful with the apparatus and methods for controlled clot aspiration of the present invention will be described. The vacuum system <NUM> includes a vacuum console <NUM> and a blood/clot collection canister <NUM>. The vacuum console <NUM> comprises an enclosure having a recess <NUM> which is shaped to removably receive the collection canister <NUM> as will be described in more detail below.

Referring to <FIG>, the vacuum console <NUM> is shown with the vacuum canister <NUM> removed. A post <NUM> which forms a contiguous portion of the outer surface or wall of the enclosure <NUM> is formed within the recess <NUM> and extends upwardly from a bottom plate <NUM> which acts as a support for the collection canister <NUM> when it is received within the recess. A vacuum connector <NUM> and a pressure sensing connector <NUM> are formed in or on an upper surface of the post <NUM> and are located so that they will align with a pressure sensing port <NUM> and a vacuum port <NUM> (<FIG>) on the vacuum canister <NUM> when it is received within the recess <NUM>. One light <NUM> is located on a wall surface of the enclosure <NUM> within the recess <NUM> and is located so that it will illuminate the contents of the collection canister <NUM> when the system is in use. A second light (not visible in in <FIG>) is present on the opposite wall of the recess <NUM>. The vacuum console <NUM> also has an on-off switch <NUM> on its upper surface. The on-off switch <NUM> illuminates when it is on (as shown in <FIG> and <FIG>) and is not illuminated when the system is off (<FIG>). Additionally, a pressure display <NUM> is provided on the upper surface of the enclosure <NUM>. As shown in <FIG> and <FIG>, the display may be a circular light, e.g. having four segments which are sequentially illuminated as the vacuum level within the canister increases. Each quadrant represents the measured vacuum as a percentage of ambient pressure.

The internal components of the vacuum console <NUM> are schematically illustrated in <FIG>. The primary internal components of the vacuum console include a pressure sensor <NUM>, a pump <NUM>, a power supply <NUM>, and a microprocessor controller <NUM>. The pump <NUM> has an inlet connected to the vacuum connector <NUM> on the post <NUM> of the enclosure <NUM>. Similarly, the pressure sensor <NUM> is connected to the pressure sensing connector <NUM> on the post <NUM>. The pump can be turned on by the switch <NUM> and will draw vacuum through the connector <NUM> and release removed gas into an interior of the console. The console in turn is vented by a vent <NUM> on a bottom surface of the enclosure <NUM>.

The functions of the pump will be controlled by the microprocessor controller <NUM>, and the pressure output from sensor <NUM> will also go through the microprocessor controller <NUM>. Each of the light <NUM>, switch <NUM>, and display <NUM> will be connected to the microprocessor controller <NUM> which is powered by the power supply <NUM>. The power supply <NUM> is powered through line current connector 72A. The USB connector 72B is powered by microprocessor controller <NUM>. The pump is plugged into an outlet via a power cord that is supplied with the pump. The power supply converts the AC current from the wall outlet to DC current which is what the microprocessor controller uses to power the pump, switch, lights, USB connector, etc..

In specific examples, pressure sensor <NUM> is connected to the microprocessor controller <NUM> and measures vacuum pressure in the canister through the pressure sensing connector <NUM>. A second pressure sensor (not shown) is also connected to the microprocessor controller <NUM> and measures ambient pressure outside of the pump enclosure through an internal tube that is routed to a vent in the base of the pump. The microprocessor controller takes the vacuum pressure reading from the pressure sensor <NUM> and divides it by the ambient pressure reading from the second pressure sensor to calculate the vacuum pressure in the canister as a percent of ambient pressure.

Referring now to <FIG>, the collection canister <NUM> has a main body <NUM> which is typically formed from a polished, clear plastic material which is molded into the illustrated shape. The main body <NUM> has an open upper end <NUM> which can be covered by a removable clear plastic lid <NUM>. The clear plastic lid <NUM> is typically attached by a bayonet connector <NUM>, and a form or other gasket <NUM> will seal the lid to the open end of the main body <NUM>.

A groove <NUM> is formed in one side of the main body <NUM> and is shaped so that it can be placed over the post <NUM> in the recess <NUM> of the enclosure <NUM> of the vacuum console <NUM>. As best seen in <FIG>, the pressure sensing port <NUM> and the vacuum port <NUM> are located at the upper end of the groove <NUM> so that they align and connect with the vacuum connector <NUM> and pressure sensing connector <NUM> on the post <NUM> when the canister <NUM> is in place in the recess <NUM>.

The pressure sensing port <NUM> is connected to a tube or lumen which extends upwardly in the main body <NUM> of the canister <NUM> and terminates in an upper opening or aperture <NUM>. Similarly, the vacuum port <NUM> extends upwardly through a much larger lumen or tube and terminates in an open aperture <NUM> at its upper end. The apertures <NUM> and <NUM> are located near the top of the interior of the main body <NUM> but will be below the bottom of the lid <NUM> when the lid is in place on the canister <NUM>. Thus, both of the apertures <NUM> and <NUM> will be exposed to the interior of the canister <NUM> but will be maintained well above the mid-section and bottom where the clot and blood are collecting. In this way, the risk of contamination from blood and clot is minimized.

A filter plate <NUM>, shown as a perforated screen but which could also be a woven screen or other separating member, is held in the mid-section of the interior of the main body <NUM> of the canister <NUM>. The clot is drawn into the interior of the canister through a connector <NUM> which is attached to a proximal end of the catheter or other tubing. The clot and blood are drawn into the interior of the main body <NUM> by the vacuum which is drawn through the vacuum port <NUM> by the vacuum console <NUM>, as previously described. As the clot and blood fall downwardly from connector <NUM> into the canister <NUM>, the clot collects on the upper surface of the filter plate <NUM> while the blood flows through the perforations in the plate and collects in the bottom of the canister. As the plate is inclined downwardly from a sleeve <NUM> which is mounted on a post <NUM> in the interior of the canister, excess blood may flow over an open bypass region <NUM> (<FIG>) which is formed on a backside of the plate and allows the blood to flow directly down to the bottom of the canister. Filter body <NUM> occupies the interior of post <NUM> and aperture <NUM> and prevents extracted material from contaminating the interior of enclosure <NUM>. Filter body <NUM> occupies the interior of post <NUM> and extends to aperture <NUM>. The filter body can thus prevent extracted material from contaminating the interior of enclosure <NUM>. A groove <NUM> is formed on a side of the main body <NUM> of the canister <NUM> and is received over the post <NUM> in the recess <NUM> of the enclosure <NUM> in order to align the vacuum and pressure sensing connectors and vacuum ports. A gasket <NUM> is further provided at the seal between the vacuum ports and the vacuum connectors.

While the exemplary apparatus and methods for controlled clot aspiration described in <FIG> may be used with the vacuum system <NUM>, as just described, it will be appreciated that the inventions described and claimed herein are not limited to use with any particular vacuum console and instead are useful with any clot or other vascular thrombectomy or aspiration system including a thrombectomy or other vascular aspiration catheter in combination with a vacuum pump or other source where there is a risk of excess blood aspiration, clogging, or both.

<FIG> illustrate one example of an exemplary system <NUM> for performing controlled clot aspiration in accordance with the principles of the present invention comprises a base unit <NUM> and an external unit <NUM>. A proximal end of a connecting tube <NUM> is connected to the base unit <NUM>, and the external unit is secured on or to the connecting tube at a location spaced apart from the proximal end, typically by some distance sufficient to make conclusions about flow. The external unit <NUM> may be configured to connect directly to a hub or other proximal end of an aspiration catheter or may be configured to be connected in the middle of the connecting tube. The connecting tube is linear in an unconstrained configuration and flexible along its length.

The base unit <NUM> may be configured to sit directly atop the lid <NUM> on the collection canister <NUM> of the previously described vacuum console <NUM>. Typically, a communication cable extends from the base unit <NUM> through a portion of connecting tubing <NUM> to a connection receptacle on the vacuum console <NUM> so that the base unit may be powered by the vacuum console and optionally can communicate data with the controller within the vacuum console.

As shown in <FIG>, an external unit 204a may include a switch for initiating treatment using the vacuum console <NUM> and controlled clot aspiration system <NUM>. The switch may also turn off the system, thereby providing a manual override of the algorithm that ensures the system is off with no flow. When the switch is on, the system may immediately enter an algorithm mode where it decides to remain open, enter a sampling mode, or initiate an extraction cycle in response to pressure sensor readings. Further details of the external unit 204a are shown in <FIG>.

Referring now to <FIG>, an exemplary base unit 200b may comprise a base unit enclosure <NUM> having an open interior cavity <NUM> which receives a number of components. For example, a controller <NUM>, typically including a microprocessor on a printed circuit board, may be mounted within the cavity <NUM> together with a pressure sensor <NUM> secured between a tube segment <NUM> and a proximal end on the connecting tube <NUM> by a pressure fitting <NUM>. The tube segment <NUM> may be collapsible and positioned in a pinch valve <NUM> which is driven by a solenoid <NUM>. Pinch valve <NUM> may be biased into a closed position by a compressive spring (not visible), unless it is opened by solenoid <NUM>. The base unit 200b further includes a connecting fitting <NUM> which is configured to be removably secured to a vacuum fitting (not shown) on the lid <NUM> of the canister <NUM>. The controller <NUM> is configured to open and close the pinch valve <NUM> to allow and prevent, respectively, the flow of clot and blood through the tubing segment <NUM> from the aspiration catheter into the collection canister. Optionally, base unit 200b may include a button (not pictured) in electronic communication with printed circuit board <NUM>, for advanced user control of various parameters of the system. In further embodiments, a base unit of the present invention may house or be in communication with a pressure chamber, a fluid source, additional on-off valves, or some such combination.

Referring now to <FIG>, an exemplary external unit <NUM> includes an external unit enclosure <NUM> having a flow fitting <NUM> in an interior cavity thereof. The flow fitting <NUM> may be connected to portions 206a and 206b of the connecting tubing <NUM>, as shown for example in <FIG>, <FIG>. A second pressure sensor <NUM> may be mounted on a printed circuit board <NUM> and also within an internal cavity of the enclosure <NUM>, and the output of the pressure sensor may be delivered to the controller <NUM> via a connective cable (not shown) which may be connected via a signal/power connector <NUM> and a mating signal-power connector <NUM>, which may be a conventional USB port and plug. The connecting cable <NUM> may have dual lumens, as shown for example in <FIG>, where one of the lumens can be used to route a communications cable between the external unit and the base unit, while the other lumen accommodates fluid flow. In further embodiments, an external unit of the present invention may house or be in communication with a pressure chamber, a fluid source, additional on-off valves, or some such combination.

By providing a first pressure sensor <NUM> in the base unit and a second, axially separated pressure sensor <NUM> in the external unit <NUM>, the material flow rate through the connecting tube can be calculated based upon measured differential pressure by the controller. The controller may analyze the pressure differentials and flow rate to determine the contents flowing through the aspiration catheter, connective tubing, or both.

In an exemplary embodiment, the controller characterizes the state of a catheter's contents as unrestricted flow, restricted flow, or clogged. In one example, a high pressure differential between spaced-apart pressure sensors indicates unrestricted flow that may be comprised of primarily healthy, clot-free blood, or blood free of vessel-obstructing clot. In some examples, healthy blood is blood with a low enough proportion of cross-linked fibrin such that it is not sufficiently integrated to cause ischemia or other similar vessel occlusions. Aspirating such healthy blood with full aspiration may result in excessive blood loss that may require the premature termination of the aspiration procedure. In another example, a variable and intermediate or low pressure differential indicates restricted flow that may be comprised of clot, occlusive material, and blood. Such flow may benefit from full aspiration. In another example, a small pressure differential or a pressure differential approaching zero indicates a clog. Such flow, or lack thereof, may benefit from an extraction cycle. The use of differential pressure for detecting increased flow and occlusions, however, is exemplary and other flow measurement and material property measurement techniques will be available within the scope of the present invention as defined in the claims.

Referring now to <FIG>, instead of the pinch valve <NUM> shown in the base unit <NUM>, an angle valve <NUM> may be employed. The angle valve has a connector <NUM> for being secured to a connector on the vacuum canister (not illustrated) as well as a fitting <NUM> that may be connected to the connecting tubing <NUM> which is in turn connected to the aspiration catheter. A solenoid <NUM> is typically present to open and close valve stem <NUM> and valve seat <NUM>. In one example, the valves of the present invention open to permit aspiration and close to block aspiration. Alternatively, the valves of the present invention may open to allow fluid to enter the aspiration tubing and/or aspiration catheter and close to block the fluid.

Referring now to <FIG>, the pressure sensors may be integrated into a single base unit <NUM> which may be fixedly attached to a canister cap <NUM>. In this example, a first pressure sensor <NUM> and a second pressure sensor <NUM> are attached to opposite ends of a coiled flow tube <NUM> so that differential pressure may be measured. An angled valve <NUM> may be secured directly to an outlet of the coiled flow tube <NUM> in order to provide for the desired on/off flow control.

The controller <NUM> in base unit <NUM> may implement an algorithm that receives and analyzes pressure sensor data to open and close the on-off valve, e.g. a pinch valve <NUM> (<FIG>) or an angle valve <NUM> (<FIG>) or <NUM> (<FIG>). The algorithm receives and analyzes the pressure data input hundreds of times per second. The data are compiled to determine the diameter of the attached catheter, determine the contents flowing through the catheter and aspiration tubing, and to determine the flow rate.

In one embodiment, the controller <NUM> implements an algorithm that uses pressure sensor data to analyze the contents flowing through an aspiration catheter and characterizes it as unrestricted flow, restricted flow, or clogged. A catheter with unrestricted is aspirating primarily healthy, clot-free blood, or blood free of vessel-obstructing clot. A catheter with mixed flow is aspirating a combination of clot, occlusive material, and blood. A catheter with little to no flow is clogged or occluded. If the algorithm determines that an excessive amount of blood is being aspirated, as is often the case for a catheter with unrestricted flow, it may restrict aspiration to reduce blood loss. If the algorithm determines that a catheter has restricted flow, it will typically allow full aspiration. If the algorithm determines that a catheter has little to no flow, it may initiate an extraction cycle to help remove any clogs or occlusions. As used herein, the term "clot" should be understood to encompass any occlusive material found in vasculature, such as thrombus, embolus, plaque, occlusive material, vessel blockage, or any other obstructive material. Clot references all such occlusive material for brevity's sake.

<FIG> illustrates an example of an algorithm that uses pressure differentials ("ΔP") to determine flowrate and, based on the determined flowrate, controls the on-off valves of the present invention. In the illustrated algorithm logic tree, the first step is to measure max and minimum pressure differential windows over some assessment period and, after the assessment period, take an instantaneous pressure differential and compare it to these max and minimum pressure differential windows, which are incrementally updated. If the instantaneous pressure differential is lower than the minimum pressure differential of the assessment period, the algorithm determines that the system is in clot and instructs the system to continue full aspiration. On the other hand, if the instantaneous pressure differential is above the minimum pressure differential the algorithm determines whether the instantaneous pressure differential is above the product of the max pressure differential multiplied by a confidence interval, if it isn't the algorithm allows full aspiration, if it is the algorithm restricts aspiration to limit blood loss and enters a sampling state where aspiration is limited to brief surges to make new instantaneous pressure differential readings. In either case, whenever aspiration is allowed, the algorithm continually takes instantaneous pressure differential readings and compares them to the max and minimum pressure differentials collected throughout the procedure. In one example, when unrestricted flow (e.g. open flow) is detected the algorithm triggers a sampling state. In another example, when a clot is detected the algorithm initiates full aspiration or initiates an extraction cycle with pulsed aspiration.

In one embodiment, the present invention utilizes a correlation algorithm that determines whether a catheter has unrestricted flow, restricted flow, or is clogged, e.g. the catheter's state, based on a correlation between flow rate and such states. In another embodiment, the present invention utilizes a windowing algorithm that analyzes discreet portions of pressure sensor data to establish local minimum and local maximum pressure sensor readings. These windowed minimums and maximums are compared to a global maximum and global minimum across the data set. Given a sudden large delta in pressure readings, the system preferentially makes determinations of a catheter's state according to local minimums and local maximums. Pressure readings below minimums and above maximums signify a change in catheter state, e.g. below a minimum indicates a clogged catheter and above a maximum indicates an unrestricted flow state.

In an additional embodiment, the present invention utilizes an algorithm emphasizing an analysis of standard deviations across a discreet window of data points. The flow rate is compared to the average and mean flow rate. A small standard deviation indicates a catheter that is clogged or unrestricted, while a large standard deviation indicates a catheter that has restricted flow.

In one embodiment, a learning algorithm is used to determine the contents flowing through an aspiration catheter. Training data is formed by collecting pressure readings along the length of catheter in a variety of states, e.g. unrestricted flow, restricted flow, or clogged. Numerous pressure readings are recorded for each catheter state, and the algorithm then references those data sets to interpret never seen pressure readings to predict what state the catheter is in.

In another embodiment, the present invention utilizes an artificial neural network (ANN) that employs a multinomial logistic regression algorithm. The ANN is trained to predict answers by considering numerous training data sets. The training data includes both observed data as inputs and the actual outputs. The inputs are propagated across the ANN, which is comprised of layered nodes that each represent a linear transformation within the solution space. The ANN then "learns" by analyzing the difference between the ANN's calculated output and the actual output. This difference is translated into an error function. The error function is back-propagated across the ANN, whereby the weight of each node is modified according to its contribution to the error function. Weighting is a process of mathematical optimization that establishes which nodes optimally map inputs to their correct outputs. Numerous sets of training data are propagated across the ANN iteratively until the error function reaches convergence, i.e. some acceptable level of tolerance. Once the nodes have been properly weighted, in that the error function has reached convergence, the ANN can accurately predict the output of previously unseen input. Here, that means that the learned ANN can take novel pressure sensor data inputs and accurately predict catheter size and whether a catheter's contents should be classified as unrestricted, restricted, or clogged.

In some embodiments, the algorithm employs semi-supervised and unsupervised learning to continually update node weights. The algorithm may employ clustering, dimensionality reduction, and reinforcement learning to further improve prediction accuracy. In preferred embodiments, the algorithm can accurately interpret pressure fluctuations associated with switching between catheters of different diameters and filter out pressure fluctuations generated by manual movements of a separator within the aspiration catheter by determining and accounting for the cadence of the movement. Additionally, the present invention may employ an algorithm that uses a combination of the above algorithmic flow analysis techniques.

The algorithm may initiate a sampling mode when unrestricted flow is detected. In exemplary embodiments, the algorithm can detect a change in flow indicating unrestricted flow within milliseconds. In one embodiment of the sampling mode, the algorithm will cycle off aspiration and then open and close the on-off valve at a predetermined frequency. The sampling state conducts an aspiration surge when the valve is briefly opened and makes an assessment of the pressure sensor readings. Based on this aspiration surge, the algorithm determines whether the system should revert to full aspiration, with the on-off valve in the open position or remain in the sampling state. These sampling surges occur over a millisecond order of magnitude and ensure that full aspiration occurs only when the system is engaging clot and thus minimizes blood loss.

In an alternative embodiment, the system is powered on and has a brief delay before the algorithm assesses flow in the aspiration tubing. If the sensors indicate unrestricted flow, then an appropriate delay of time is calculated for which the on-off valve remains shut. After this delay, the on-off valve opens to briefly allow aspiration and take a pressure reading sample in the aspiration tubing to assess whether the system still has unrestricted flow or if it has been positioned into clot or other occlusive material. If the sampling detects unrestricted flow, a new delay is calculated (in some instances, incrementally longer for each consecutive reading up to a threshold). If the sampling detects clot, e.g. restricted flow or a clog, an appropriate delay of time is calculated for which the valve remains open. While open, the system assesses pressure sensors readings at a regular frequency to determine whether the system has been positioned such to cause unrestricted flow. These processes repeat until the procedure is finished.

An extraction cycle may be useful to clear occlusions in an aspiration catheter or to facilitate the aspiration of clot that are large or otherwise hard to aspirate. An extraction cycle establishes pressure differentials between the aspiration catheter and the vacuum source to generate pressure pulses. In general, these pressure pulses can employ multiple mechanisms to facilitate thrombus ingestion into an aspiration catheter. In one mechanism, the pressure pulse introduces an acceleration component that facilitates the extraction of occlusive material. In another mechanism, the pressure pulse creates a force impulse that breaks static friction momentarily, allowing a lower dynamic friction to ingest thrombus. In yet another mechanism, the pressure pulse moves the thrombus away from the distal tip of the catheter and subsequently rapidly forces contact between the thrombus and the catheter, macerating the thrombus.

In one example, an extraction cycle alternates between providing vacuum aspiration and relative positive pressure. An extraction cycle is typically initiated when an aspiration catheter is already under full vacuum. When an extraction cycle is initiated, the vacuum on-off valve between the catheter and the aspiration source is closed and the pressure in the aspiration catheter is increased, which may cause a positive pressure pulse and establish a pressure differential between the vacuum source and the catheter. When the on-off valve is then opened, the contents and the distal tip of the aspiration catheter experience the pressure differential as a negative pressure pulse that negatively impacts the structural integrity of any occlusions to a degree that a static force could only achieve with a greater supply of energy. The amplitude, or magnitude, of these pressure pulses are directly correlated to the pressure differential between an evacuated catheter and a pressure source (for positive pressure pulses) and a pressurized catheter and a vacuum source (for negative pressure pulses). The frequency with which the on-off valve opens and closes may be predetermined or responsive to pressure sensor data. An extraction cycle's pressure pulses may have an amplitude and frequency optimized to extract thrombus and similar occlusions from vasculature.

Pressure differentials in a catheter may be generated in a number of ways. In one example, pressure is generated by simply closing off a catheter's access to the vacuum source. In another example, pressure is generated by introducing fluid into the catheter, where the fluid is at a pressure between full vacuum and ambient pressure, at ambient pressure, at systolic pressure, or above systolic pressure (<FIG>). In another example, pressure differentials are generated by mechanical displacement of a pressure chamber (<FIG>).

An extraction cycle may be automatically initiated when an algorithm of the controller <NUM> detects a clogged catheter, an occluded catheter, or a catheter positioned in clot. A catheter may be identified as in clogged state when the pressure differentials approach zero. In one example, the controller automatically initiates an extraction cycle after the system has detected a clog lasting for more than <NUM> seconds. Alternatively, an extraction cycle is initiated, or terminated, on demand by a user. An extraction cycle may provide pressure pulses for a predetermined time period. Alternatively, an extraction cycle assesses pressure sensor data each time the on-off valve opens to assess flow and to determine whether the extraction cycle should continue or end. If an extraction cycle has trouble clearing a clog, it may vary the amplitude and frequency of the pressure pulses. In one example, an algorithm on the controller <NUM> consults a library of different pressure pulses and chooses from among the library. If a specific amplitude and frequency starts to clear the clog, the algorithm may continue to generate pressure pulses of that frequency and amplitude until the clog is cleared.

<FIG> illustrates an example of a fluid system that may be used to generate pressure differentials, and thus pressure pulses. In this example, a fluid introduction unit <NUM> is attached along a length of the connection tubing <NUM> with a three-point junction <NUM>. The three-point junction <NUM> may be positioned between the base unit <NUM> and the external unit <NUM> or may be positioned distal to both the base unit <NUM> and the external unit <NUM>-i.e. in close proximity to an attached aspiration catheter. A fluid injection on-off valve <NUM> controls the flow of fluid (either liquid or gas) to inject pulses of pressure into the clot flow path that may facilitate the extraction of clot or other occlusive substances. In some instances, the flow of fluid is introduced directly into the connection tubing <NUM>. In other instances, the flow of fluid first traverses an injection tube <NUM> before entering the connection tubing <NUM>. The injection tubing <NUM> may direct the pressure pulse towards the catheter, which may optimize the pressure pulse. In one example, the three-pint junction <NUM> has a T-joint structure as illustrated in <FIG>. Alternatively, a three-point junction may have a Y-joint structure (not illustrated). The Y-joint may beneficially direct fluid from the fluid introduction unit towards the catheter, which may optimize the pressure pulse in a similar manner to the injection tubing of the prior example.

<FIG> illustrates an alternative fluid system that uses a pump <NUM> that may be connected between a fluid reservoir <NUM> and an injection valve <NUM>. In one embodiment, the pump <NUM> cycles on when the injection valve <NUM> opens. The pump provides work by forcefully injecting fluid from a fluid reservoir <NUM>, through the injection on-off valve <NUM>, into an injection tube <NUM> and/or connection tubing <NUM>. In this example, the magnitude of the positive pulse of pressure is directly correlated to the throughput (e.g. size) of the pump <NUM>. In a second embodiment, a pressure chamber <NUM> is positioned between the pump <NUM> and the injection valve <NUM>. A pressure chamber <NUM> allows the pump <NUM> to provide work even when the injection valve <NUM> is closed. While the injection valve <NUM> is closed, the pump <NUM> forcefully injects fluid from the reservoir <NUM> into the pressure chamber <NUM>, whereby the pressure chamber <NUM> becomes pressurized. When the injection valve <NUM> opens, pressure is released from the pressure chamber <NUM> into the injection tube <NUM> and/or connection tubing <NUM>. In this embodiment, since the pump <NUM> can build up pressure over time, the magnitude of the positive pulse of pressure is not directly correlated to the throughput (e.g. size) of the pump <NUM>, thus this embodiment allows for a smaller pump. To provide even greater control over the duration or magnitude of positive pressure pulses, the opening and closing of the injection valve may be throttled or manipulated to modulate rate of injection. Additionally, a pressure sensor may be included in pressure chamber <NUM> to monitor and control the buildup of pressure.

<FIG> illustrates another three-point junction <NUM> attached along connection tubing <NUM>. The three-point junction <NUM> may be positioned between the base unit <NUM> and external unit <NUM> or may be positioned distal to both the base unit <NUM> and the external unit <NUM>. A pressure valve <NUM> controls the generation of positive pulses of pressure from fluid chamber <NUM>. Fluid from the fluid chamber <NUM> may flow directly into connection tubing <NUM> or may first traverse an injection tube <NUM> before entering the connection tubing <NUM>. An aspiration valve <NUM> controls the application of vacuum aspiration from an attached vacuum source. In this embodiment, the three-point junction <NUM> has valves to control both vacuum forces and positive pressure pulses. This allows the three-point junction <NUM> to alternate between applying vacuum aspiration and pulses of pressure, wherein the pressure is above that of the vacuum source. The aspiration valve <NUM> and the pressure valve <NUM> may be opened alternatively, simultaneously, with a delay, or in some overlapping sequence. In one overlapping sequence, one valve starts to open when the other valve is starting to close, whereby there is a brief period where both valves are at least partially open. In other overlapping sequences, sometimes both valves are open and both valves are closed for at least short periods of time.

In one embodiment, which is not claimed, an aspiration valve <NUM> is positioned between a catheter and an aspiration source to modulate aspiration and a pressure valve <NUM> is positioned between the catheter and fluid source to modulate fluid injection. The present invention may selectively open and close both aspiration valve <NUM> and pressure valve <NUM> to create pressure differentials within the catheter and/or aspiration tubing that result in pressure pulses of a desired amplitude and frequency.

<FIG> provides a perspective view of a three-way joint and the components it connects. In this example, a connection tubing <NUM> acts as a common conduit between a vacuum source <NUM>, a pressure source <NUM>, and an aspiration catheter <NUM>. The connection tubing <NUM> may have a first end configured to attach, or be placed in fluid communication with, the vacuum source and a second end configured to attach, or be placed in fluid communication with, the aspiration catheter. In one example, the second end is attached to the aspiration catheter with a rotating hemostasis valve. A three-way joint <NUM> may be positioned proximate to the second end to provide pulses of relative positive pressure near the aspiration catheter <NUM>. In one example, the three-way joint <NUM> is an angled joint or Y-joint, whereby fluid from the pressure source is directed towards the aspiration catheter <NUM>. In some examples, the three-way joint <NUM> includes injection tubing <NUM>, which directs fluid from the pressure source towards the aspiration catheter <NUM>. In some examples, the injection tubing <NUM> extends from the three-way joint into the aspiration catheter, whereby fluid flows from the pressure source into the aspiration catheter <NUM>. In another example, the injection tubing <NUM> extends from the three-way joint to a position proximate a distal end of the aspiration catheter, as depicted in perspective <NUM>, which provides a zoomed-in perspective of the distal end of the aspiration catheter <NUM>. In this example, the pressure source may cause fluid to flow according to directional arrow <NUM> and the vacuum source may cause fluid to flow according to directional arrow <NUM>. In some embodiments, which are not claimed, the controller may modulate a vacuum valve <NUM> and a pressure valve <NUM>, whereby the closing of the vacuum valve <NUM> and the opening of the pressure valve <NUM> may result in a relative increase in pressure at a distal tip of an aspiration catheter. Alternatively, the opening of the vacuum valve <NUM> and the closing of the pressure valve <NUM> may result in a relative decrease in pressure at the distal tip of the aspiration catheter <NUM>. In some instances, these changes in pressure are transmitted along a length of the aspiration catheter as a pressure pulse. In some embodiments, a controller may close vacuum valve <NUM> and open pressure valve <NUM> for a small period of time, thus allowing a minimal volume of fluid from the pressure source <NUM> to be introduced into a proximal end of aspiration catheter <NUM> to increase the relative pressure at a distal end of the aspiration catheter <NUM> before reverting to vacuum by re-opening vacuum valve <NUM> and closing pressure valve <NUM>. Similarly, a controller may close vacuum valve <NUM> and open pressure valve <NUM> for a longer period of time, allowing a larger volume of fluid from the pressure source <NUM> to be introduced into the aspiration catheter <NUM> to facilitate movement of obstructive material away from the distal end of aspiration catheter <NUM> before reverting to vacuum by re-opening vacuum valve <NUM> and closing pressure valve <NUM>. In some embodiments, which are not claimed, the connecting tubing <NUM> may have a dual lumen along a portion of its length, whereby one lumen accommodates fluid and a second lumen accommodates wiring, which enables the controller to modulate both the vacuum valve <NUM> and the pressure valve <NUM>.

<FIG> illustrates another embodiment of a valve structure that controls both aspiration forces and positive pressure pulses. In this example, a three-point junction <NUM> attaches to connection tubing <NUM> and pressure chamber <NUM>. A gate valve <NUM> translates at axis <NUM> to block aspiration in a 550A position and to block fluid introduction in a 550B position. The gate valve <NUM> may provide pulsed aspiration by oscillating back and forth at a predetermined or responsive frequency as controlled by an algorithm in the controller <NUM>. In this example, the three-way gate valve exists at the juncture between the aspiration source, the pressure source, and the catheter. The gate valve <NUM> translates between blocking the aspiration source and blocking the pressure source to effect pressure pulses of a desired amplitude and frequency.

In an alternative embodiment, fluid injection does not occur at a three-point juncture, but rather occurs at a more distal region closer the catheter tip. The location of the relative pressure injection may be used to optimize the pressure pulse variation in order to facilitate clot removal. In one embodiment, a distal region of an aspiration catheter includes a valve that can be opened and closed, e.g. the distal valve. In one example, an aspiration valve is closed, and the distal valve is opened to allow blood to rush into the catheter, which increases the pressure in the catheter and amplifies the pressure differential between the catheter lumen and the vacuum source. Typically, the distal valve is then closed, and the aspiration valve is opened, wherein the pressure differential between the vacuum source and the catheter results in a pressure pulse. In another embodiment, fluid is transferred into an aspiration catheter from another adjacent catheter. For instance, an inner catheter may deliver fluid to an outer aspiration catheter. Alternatively, an outer catheter may deliver fluid to an inner aspiration catheter through a valve structure. In either case, the fluid is delivered along the length of the aspiration catheter, rather than through a proximal end. In a similar manner, an adjacent catheter may offer an additional connection to a vacuum source.

<FIG> illustrates a mechanical assembly for generating pressure pulses. In this example a mechanical piston <NUM> can replace the previous embodiment's injection valves, pressure chambers, pumps, and fluid reservoirs. The stroke of the piston <NUM> or alternative mechanical device can be controlled to adjust the volume of the catheter resulting in the generation of negative pressure on one stroke and the generation of positive pressure on the other stroke. In general, a mechanical actuation device actuates back and forth to increase and decrease the overall volume of the system. When the device actuates to increase volume, pressure decreases, and when the device actuates to decreases volume, pressure increase. These pressure changes may create, amplify, or assist pressure pulses of an extraction cycle. The piston <NUM> may be provided in a three-point juncture <NUM> that attaches to connection tubing <NUM>. Other mechanical means of controlling volume, or pressure, of the catheter include linear motors, stepper/servo motors, cam follower actuators, solenoids, audio exciters, voice coil actuators, diaphragms, peristaltic pumps, rotary vanes, gears, screws, syringes etc. (not pictured).

High frequency pressure pulses may be enabled by a mechanical method, such as that depicted in <FIG>. To provide high frequency pressure pulses, a catheter must be rapidly pressurized and rapidly evacuated. The fluid injection systems of <FIG> may readily provide a rapid influx of pressure; however, it may take a non-insignificant amount of time for the vacuum source to bring that catheter back to full vacuum. If the next influx of pressure occurs too early, the catheter will not have had time reach full vacuum, or near full vacuum. In this scenario, the pressure differential between the not-quite-evacuated catheter and the pressure source will be lower and the resulting pressure pulses will have a lower amplitude, which may be suboptimal in some scenarios. To avoid low amplitude pressure pulses caused by a high frequency, the present invention may utilize a vacuum recovery system to reduce the time required to return a catheter to full vacuum after an influx of positive pressure. With a vacuum recovery system, the present invention enables pressure pulses with both a high amplitude and a high frequency.

<FIG> illustrates a device that may function as a vacuum recovery system by generating pressure differentials. Alternatively, a vacuum recovery system may utilize a syringe, an evacuated chamber, a second aspiration pump, or some combination of these options. A syringe is a piston actuated device that retracts to increase a system's volume (and thus decrease pressure) and advances to decreases a system's volume (and thus increase pressure). A syringe-like device may beneficially assist not only vacuum recovery but also positive pressure pulse generation. In one example, a syringe is used during an extraction cycle. In such an example, a catheter starts at full vacuum. The vacuum source closes, the syringe advances (to reduce system volume), and, optionally, fluid is injected, which all facilitates the formation of a positive pressure pulse. Next, the vacuum source opens, and the syringe retracts (to increase system volume) to generate a negative pressure pulse, whereby the syringe speeds the catheter's return to near full vacuum. Alternatively, an aspiration pump is configured to selectively prime an evacuated chamber that is opened to the catheter, in addition to an aspiration pump, after each pressure pulse. Together, the aspiration pump and the evacuated chamber more rapidly return a catheter to full vacuum. While the aspiration pump is closed to the catheter, it may be opened to the evacuated chamber to further prime the evacuated chamber between pressure pulses. In a further alternative, a secondary aspiration pump assists a primary aspiration pump to facilitate vacuum recovery after each pressure pulse.

<FIG> illustrates a graphical representation of an example pulsation protocol. An extraction cycle may use a pulsation protocol to systemically manipulate the amount of pressure within a catheter to facilitate the extraction of occlusive material. Pressure in a catheter may be manipulated by a variety of methods. For instance, vacuum aspiration may be used to reduce pressure within the catheter and the removal of vacuum suction and/or the introduction of fluid may be used to increase pressure within the catheter. In other instances, a mechanically actuating device may alternate between increasing and decreasing pressure within a catheter. In the example illustrated by <FIG>, at time <NUM>, the catheter has not been subjected to any suction forces and is at atmospheric pressure. From time <NUM> to time <NUM>, the catheter has lost pressure, lunging from atmospheric pressure to near full vacuum (i.e. near -<NUM>. From time <NUM> to time <NUM>, the catheter has gained pressure, which decreases vacuum strength. From time <NUM> to <NUM>, the catheter has lost pressure, which returned the catheter to near full vacuum. From time <NUM> to <NUM>, the catheter has gained pressure and returned to ambient pressure. From time <NUM> to <NUM>, the catheter has lost pressure, again lunging from atmospheric pressure to near full vacuum. From time <NUM> to <NUM>, the catheter has gained pressure, which caused the pressure to surge from near full vacuum to above ambient pressure. From time <NUM> to <NUM>, the catheter has lost pressure, lunging from a pressurized state above atmospheric pressure to near full vacuum.

A pulsation protocol of the nature illustrated in <FIG> may be executed once or may be repeated several times. In alternative embodiments, the pulsation protocol may include additional time periods with additional pressure variations and pressure patterns. In general, the system's pressure may vary from between near vacuum to above average systolic pressure. The duration of the pulsation protocol may be predetermined or adaptive to pressure sensor readings. For instance, the controller may prolong or shorten a pulsation protocol based on pressure sensor readings. In some examples, the system may remain at a stable pressure state across one or more time periods. For instance, the controller may cause the system to dwell at near full vacuum. The dwell time in each pressure state and the frequency with which the system transitions between pressure states may be optimized to ingest different clot or occlusive material compositions. Although <FIG> illustrates a pulsation protocol with a stable and consistent frequency, in other examples the frequency of a pulsation protocol is variable or some combination of partially stable and partially variable. High amplitude (or high magnitude) pressure pulses may be generated by generating large pressure differentials. For instance, <FIG> illustrates a high amplitude pressure pulse between times <NUM> and <NUM>. Lower magnitude pressure pulses may be generated by oscillating between less extreme high pressures and low pressures. For instance, the low end of the pressure pulse may not reach near full vacuum, the high end of the pressure pulse may not reach ambient pressure, or both, thereby resulting in a lower magnitude pressure pulse, which may be desirable in some scenarios. The time units of <FIG> may be in second, milliseconds, microseconds.

In some examples, an extraction cycle uses a predetermined series of pressure pulses with near full vacuum aspiration before the extraction cycle, between individual pulses of relative positive pressure, and after the extraction cycle. The pressure pulses may be selected from a library of pressure pulses having amplitudes and frequencies that facilitate the extraction of clot and other occlusive material. A series of pressure pulses may vary from one another in terms of frequency, amplitude, or both. For instance, a pulsation protocol may use a series of pressure pulses with a trend where one of the amplitude or frequency rises while the other diminishes, where both the amplitude and frequency rise or diminish, or where one of the amplitude or frequency rises or diminishes while the other remains constant.

In some examples, an extraction cycle provides specific pressure pulses based on pressure sensor readings. One such responsive extraction cycle measures pressure within the catheter and then selects one or more pressure pulses optimized for a catheter with those pressure readings. In another responsive extraction cycle, the system cycles through a library of pressure pulse protocols, with time periods of static or full aspiration and occlusion detection after each individual pressure pulse. After the library has been cycled, the system repeats the pressure pulses that were measured to be most successful. The degree of success of a specific pressure pulse is typically commensurate with the amount of increased flow rate after the pressure pulse. The system will continue to cycle down until only a few pressure pulse protocols are in the loop. If the efficacy of the loop begins to diminish, the system will return to the full library and start a fresh cycle.

In an alternative responsive system, a responsive extraction cycle has three modes: Cycling up, where successive pressure pulses are stronger in terms of amplitude and/or frequency, cycling down, where successive pressure pulses are weaker in terms of amplitude and/or frequency, and maintenance pressure pulses, where pressure pulses have a consistent frequency and amplitude. When the system detects a clogged state, it enters the cycling up mode. When the system detects restricted flow state, it enters the maintenance mode. When the system detects an unrestricted flow state, it enters the cycling down mode. In this way, the system trends towards pressure pulses with an amplitude and frequency that facilitates restricted flow, which is beneficially removing clot and other occlusive material.

In situations where maximizing the removal of occlusive material eclipses concerns of blood loss, such as in neurovascular stroke procedures, an alternative embodiment according to the invention may be useful. Under these circumstances, as an example, an optimal technique may include positioning the distal end of a catheter in clot, applying full vacuum, and waiting a predetermined period of time before advancing to a next step. The objective may be complete or nearly complete catheter tip engagement of a mass of occlusive material, engagement which essentially clogs the distal end of the catheter and is sometimes referred to as "corking the catheter". If a clinician has successfully "corked the catheter", the catheter system may be removed from the vessel, withdrawing the mass of clot or occlusion with it. Alternatively, an extraction cycle may be used to draw an occlusion through the catheter lumen or cause the clot to become deeply latched, or corked, within the catheter attached to the present invention. After the completion of the extraction cycle, the clot should be removed or corked in the attached catheter so that the catheter together with the clot can safely be removed from the patient.

In some instances, an extraction cycle may automatically stop or be manually stopped when a clot or other occlusive material clogs a catheter and corks it. For instance, the clot or occlusive substance might be too large or tough to traverse an aspiration catheter, but nonetheless become partially entrained in the aspiration catheter. In such instance, the system may transition to full aspiration to allow the user to remove the corked catheter while dragging the clot or occlusive material out with the catheter. In one example, an extraction cycle is initiated, and the clot or occlusive material still clogs the catheter. The controller may then revert to full aspiration and notify the user of the corking event, whereby the system may prompt the user to remove the catheter. Alternatively, the user may manually turn off an extraction cycle, causing the system to return to full vacuum, and remove the catheter.

To indicate that the present invention is doing work to remove clots or other occlusive material, one embodiment includes visual and/or auditory signals that indicate the progress of a given extraction cycle. In one example, the start of an extraction cycle is signaled by a flashing blue light, which flashes until the cycle is completed, and, at completion, the light turns to green to indicate completion. In another example, base unit <NUM> may include a light bar. The light bar fills up incrementally, whereby the light bar progressively "fills up" with light in proportion to the cycle's progress. Alternatively, base unit <NUM> may include a small screen for displaying images. The small screen may display an animation indicative of loading. Loading animations may execute a repetitive pattern (e.g. spinning circular object) or may execute a single cycle of a prolonged animation (e.g. slowly filling circle). Either in conjunction with visual progress indication or as an alternative to visual progress indication, the system may use auditory cues to signify the extraction cycle's initiation, pulsating phase, and completion. Such auditory cues may include musical notes, beeps, and/or speech. Auditory cues may include updates (e.g. "extracting") or suggestions (e.g. "advance/retract the catheter").

An algorithm may also control a lighting mechanism, e.g. indicator light <NUM> (<FIG>), to convey to the user whether the system is in a full aspiration state, an unrestricted flow state, a restricted flow state, a clogged state, a sampling state, or an extracting state. Specific lights may be illuminated to indicate bubbles or that the override switch has been triggered. Additionally, the algorithm may control a piezo acoustic chip that conveys audible information to the physician regarding the state of the effluent and override switch. In one embodiment, the piezo is a surface mounted <NUM> single tone at 65dB at <NUM>. The signals may include sounds and phrases such as tone/pitch changes, beeping patterns, "clogged", "occluded", "clot", "blood", "open flow", etc. One example utilizes a dynamic beeping cadence, where a beeping pattern is steadily increased when an unrestricted flow state is increasing in duration. The speed of the beeps indicates the length of time the system has been in unrestricted flow, alerting the physician to the increasingly problematic nature of the system's positioning. The system may also include a multi-position switch or button to specifically activate different algorithms, mute audio cues, or to prime the system with fluid. Such a feature could be activated by inserting a pin in the base unit <NUM>, which will activate this customizable feature.

In one embodiment, the system may be manually powered on and conduct aspiration for a predetermined period of time. If the system detects unrestricted flow, then the on-off valve is turned off to stop flow. The attending physician then must reposition the catheter tip into clot and manually trigger a mechanism (such as a foot pedal or manual switch) to initiate further aspiration. This manual trigger overrides the algorithm and allows aspiration to continue. Once the manual trigger is released, the algorithm again monitors flow to allow aspiration so long as the flow is acceptable. If and when the system again detects unrestricted flow, the on-off valve is again closed until the physician repositions the aspiration catheter and manually overrides the controller. This protocol is repeated until the physician completes the procedure.

Before an aspiration catheter can be used to remove clot and other occlusive material it must be primed with an uncompressible fluid. For instance, a catheter may be filled with saline fluid to remove all the air from the lumen of the catheter. In some embodiments, the present invention automatically primes a catheter, whereby the catheter is filled with fluid to expel all compressible fluids, like air. In one example, the sensors of the present invention monitor catheter contents during use. If compressible fluids are detected, like bubbles, the system may alert the user. In some instances, the system may indicate that the procedure needs to stop so that the catheter can be again primed to remove the air bubbles.

Claim 1:
A vacuum aspiration control system for use with a vacuum source (<NUM>) and an aspiration catheter (<NUM>, <NUM>), said system comprising:
a connecting tube (<NUM>, <NUM>) configured to connect the vacuum source with the aspiration catheter or component thereof;
an on-off valve (<NUM>, <NUM>, <NUM>, <NUM>, <NUM>, <NUM>, <NUM>, <NUM>, <NUM>) configured to be operatively coupled to the connecting tube;
a sensing unit (<NUM>, <NUM>, <NUM>, <NUM>) configured to detect flow within the connecting tube and to produce a signal representative of such flow; and
a controller (<NUM>) configured to receive the signal representative of flow through the connecting tube and to open and close the on-off valve,
wherein the controller is configured to automatically close the valve to stop flow through the connecting tube when the signal indicates unrestricted flow.