Aspiration and monitoring system

Abstract

To provide an aspiration system for removing undesired matter such as thrombus from a lumen of the body such as a blood vessel.SOLUTION: A system for aspiration includes an aspiration catheter including an elongate shaft including an aspiration lumen, and an open distal end, an extension tube, a peristaltic pump, a compressible portion disposed between the distal end and the proximal end of the extension tube, the compressible portion configured to be coupled to the peristaltic pump, such that operation of the peristaltic pump drives fluid from the aspiration lumen from the distal end of the extension tube to the proximal end of the extension tube, and a controller configured to receive a first signal from a first sensor and configured to vary the operation of the peristaltic pump based at least in part on a first signal received from the first sensor coupled to the aspiration lumen or extension tube related to a change in the characteristic of flow.SELECTED DRAWING: Figure 38

Description

[Technical Field]

[0001]

[0001] The field of the invention generally relates to aspiration systems for removing undesirable material, such as blood clots, from bodily lumens, such as blood vessels, including fluid-carrying cavities, ducts, sinuses, or tubes in the brain or any space in the body, whether or not intended to carry a fluid, by aspiration. [Background technology]

[0002]

[0002] A treatment method for removing unwanted material, such as a blood clot, from a patient's blood vessel involves the use of an aspiration catheter having an elongated shaft formed with an aspiration lumen extending therethrough. The aspiration catheter may also include a guidewire lumen for placement of a guidewire used to guide the aspiration catheter to a target site within the body. By applying a vacuum or negative pressure to the proximal end of the aspiration lumen, for example, using a syringe having a hub connected to the proximal end of the aspiration catheter, material may be aspirated into an aspiration port at the distal end of the aspiration catheter and into the aspiration lumen, and thus removed from the patient. Summary of the Invention

[0003]

[0003] In one embodiment of the present disclosure, a system for catheter-based aspiration includes an aspiration catheter including an elongated shaft configured for placement within a blood vessel of a subject, the shaft including an aspiration lumen having a proximal end and an open distal end; an extension tube having a distal end and a proximal end and a lumen extending therebetween, the extension tube being configured to hydraulically connect the lumen of the extension tube to the aspiration lumen of the aspiration catheter; a peristaltic pump configured to drive fluid through the extension tube, the peristaltic pump including a pump base having a pressure shoe and a rotatable head, the rotatable head including two or more compression elements arranged around the periphery thereof; and a pump base and a rotatable head. a compressible tubular portion disposed between the pressure shoe and the rotatable head of the peristaltic pump, the compressible tubular portion configured to be connected to the pressure shoe and the rotatable head of the peristaltic pump, such that operation of the peristaltic pump rotates the rotatable head and causes two or more compression elements to drive fluid from the aspiration lumen of the aspiration catheter through the dilation tube from the distal end of the dilation tube to the proximal end of the dilation tube; a first sensor configured to measure a flow characteristic through at least one of the aspiration lumen or the lumen of the dilation tube; and a controller configured to receive a first signal from the first sensor and vary operation of the peristaltic pump based at least in part on the first signal received from the first sensor related to a change in the flow characteristic. The "flow characteristic" may include pressure, flow rate, flow velocity, or a fluctuation or disturbance of any of these. The "flow characteristic" may even be laminar or turbulent flow conditions, or a change therebetween.

[0004]

[0004] In another embodiment of the present disclosure, a method for performing a thrombectomy procedure includes the steps of providing an aspiration catheter including an elongated shaft configured for placement within a blood vessel of a subject, the shaft having an aspiration lumen and an infusion lumen, the aspiration lumen having open distal and proximal ends, the infusion lumen extending within the aspiration lumen and having distal and proximal ends, the distal end of the infusion lumen being located within the aspiration lumen near the open distal end of the aspiration lumen, the aspiration catheter further including an orifice at the distal end of the infusion lumen configured to generate one or more jets when pressurized fluid is infused through the infusion lumen; and placing at least a distal portion of the elongated shaft within the blood vessel of the subject, the elongated shaft having an orifice extending between the distal and proximal ends. the dilation tube having a lumen configured to be hydraulically connected to the suction lumen of the suction catheter within a roller pump such that a compressible portion of the dilation tube disposed between the distal and proximal ends of the dilation tube is engageable by two or more rollers of a rotatable head of the roller pump; injecting pressurized fluid through the infusion lumen of the suction catheter from the proximal end to the distal end, causing it to pass through an orifice and into the suction lumen, thereby forcing a portion of the bodily fluid into the suction lumen of the suction catheter; and operating the roller pump such that the bodily fluid forced into the suction lumen of the suction catheter passes through the dilation tube from the distal end of the dilation tube to the proximal end of the dilation tube.

[0005] In yet another embodiment of the present disclosure, a system for catheter aspiration includes an aspiration catheter including an elongate shaft configured for placement within a blood vessel of a subject, the shaft having an aspiration lumen and an infusion lumen, the aspiration lumen having open distal and proximal ends, the infusion lumen extending into the aspiration lumen and having distal and proximal ends, the distal end of the infusion lumen being located within the aspiration lumen near the open distal end of the aspiration lumen, an orifice in the distal end of the infusion lumen configured to generate one or more jets when pressurized fluid is infused through the infusion lumen, and a catheter assembly having the distal and proximal ends and the a dilation tube having a lumen extending therebetween, the distal end of the dilation tube being configured to be hydraulically connected to the aspiration lumen of the aspiration catheter, the dilation tube further having a compressible portion disposed between the distal and proximal ends of the dilation tube, the compressible portion being configured to be disposed within a peristaltic pump such that operation of the peristaltic pump moves fluid from the aspiration lumen of the aspiration catheter through the dilation tube from the distal end of the dilation tube to the proximal end of the dilation tube; and a return conduit hydraulically connected to the dilation tube and configured to return to the vascular system of a subject fluid that has passed through the dilation tube from its distal to its proximal end.

[0006] In yet another embodiment of the present disclosure, a system for catheter aspiration includes a peristaltic pump; an aspiration catheter including an elongated shaft configured for placement within a blood vessel of a subject, the shaft having an aspiration lumen and an infusion lumen, the aspiration lumen having open distal and proximal ends, the infusion lumen extending into the aspiration lumen and having distal and proximal ends, the distal end of the infusion lumen being located within the aspiration lumen near the open distal end of the aspiration lumen, an orifice in the distal end of the infusion lumen being configured to generate one or more jets when pressurized fluid is infused through the infusion lumen; and a lubricant comprising a pump and a lubricant extending therebetween. a dilation tube having a distal end hydraulically connected to the aspiration lumen of the aspiration catheter, the dilation tube further having a compressible portion disposed between the distal and proximal ends of the dilation tube, the compressible portion configured for placement within a peristaltic pump such that operation of the peristaltic pump moves fluid from the aspiration lumen of the aspiration catheter through the dilation tube from the distal end of the dilation tube to the proximal end of the dilation tube; and a filter disposed in a conduit including the aspiration lumen of the aspiration catheter and the lumen of the dilation tube, the filter being disposed between the orifice and the compressible portion of the dilation tube.

[0007] In yet another embodiment of the present disclosure, a system for catheter aspiration includes an aspiration catheter including an elongated shaft configured for placement within a blood vessel of a subject, the shaft having an aspiration lumen and an infusion lumen, the aspiration lumen having open distal and proximal ends, the infusion lumen extending into the aspiration lumen and having distal and proximal ends, the distal end of the infusion lumen being located within the aspiration lumen near the open distal end of the aspiration lumen, an orifice in the distal end of the infusion lumen being configured to generate one or more jets when pressurized fluid is infused through the infusion lumen, and an extension tube having distal and proximal ends and a lumen extending therebetween, the distal end of the extension tube extending from the aspiration catheter the dilation tube configured to be hydraulically connected to the aspiration lumen of the aspiration catheter, the dilation tube further having a compressible portion disposed between a distal end and a proximal end of the dilation tube, the compressible portion configured to be disposed within the peristaltic pump such that operation of the peristaltic pump moves fluid from the aspiration lumen of the aspiration catheter through the dilation tube from the distal end of the dilation tube to the proximal end of the dilation tube; a controller configured to operate a piston pump configured to pressurize fluid through the infusion lumen; and a sensor configured to sense the presence of air in the pressurized fluid infused into or through the infusion lumen, the sensor configured to output a signal to the controller.

[0008] In yet another embodiment of the present disclosure, a system for catheter aspiration includes: an aspiration catheter including an elongated shaft configured for placement within a blood vessel of a subject, the shaft having an aspiration lumen with open distal and proximal ends; a dilation tube having distal and proximal ends and a lumen extending therebetween, the distal end of the dilation tube configured to be hydraulically connected to the aspiration lumen of the aspiration catheter, the dilation tube further having a compressible portion disposed between the distal and proximal ends of the dilation tube, the compressible portion configured for placement within a roller pump such that operation of the roller pump causes fluid from the aspiration lumen of the aspiration catheter to move through the dilation tube from the distal end of the dilation tube to the proximal end of the dilation tube; a pressure sensor configured for placement in fluid communication with a conduit including the lumen of the dilation tube and the aspiration lumen of the catheter; a measurement device connected to the pressure sensor and configured to measure a deviation in fluid pressure; and a communication device connected to the measurement device and configured to generate a signal related to the deviation in fluid pressure.

[0009] In yet another embodiment of the present disclosure, a system for catheter aspiration includes: an aspiration catheter including an elongated shaft configured for placement within a blood vessel of a subject, the shaft having an aspiration lumen with open distal and proximal ends; a dilation tube having distal and proximal ends and a lumen extending therebetween, the distal end of the dilation tube configured to be hydraulically connected to the aspiration lumen of the aspiration catheter, the dilation tube further having a compressible portion disposed between the distal and proximal ends of the dilation tube, the compressible portion configured for placement within a peristaltic pump such that operation of the peristaltic pump causes fluid from the aspiration lumen of the aspiration catheter to move through the dilation tube from the distal end of the dilation tube to the proximal end of the dilation tube; a pressure sensor configured for placement in fluid communication with a conduit including the lumen of the dilation tube and the aspiration lumen of the catheter; a measurement device connected to the pressure sensor and configured to measure a deviation in fluid pressure; and a communication device connected to the measurement device and configured to generate a signal related to the deviation in fluid pressure.

[0010]

[0010] In yet another embodiment of the present disclosure, a method for performing a thrombectomy procedure includes the steps of providing an aspiration catheter including an elongated shaft configured for placement within a blood vessel of a subject, the shaft having an aspiration lumen with open distal and proximal ends; placing at least a distal portion of the elongated shaft within the blood vessel of the subject; and placing a dilation tube having distal and proximal ends and a lumen extending therebetween, the dilation tube configured to be hydraulically connected to the aspiration lumen of the aspiration catheter within a roller pump such that a compressible portion of the dilation tube disposed between the distal and proximal ends of the dilation tube is engageable by two or more rollers of a rotatable head of the roller pump; and operating the roller pump such that bodily fluid forced into the aspiration lumen of the aspiration catheter passes through the dilation tube from the distal end of the dilation tube to the proximal end of the dilation tube.

[0011]

[0011] In yet another embodiment of the present disclosure, a system for catheter aspiration includes: an aspiration catheter including an elongated shaft configured for placement within a vasculature of a subject, the shaft having an aspiration lumen with open distal and proximal ends; a dilation tube having distal and proximal ends and a lumen extending therebetween, the distal end of the dilation tube configured to be hydraulically connected to the aspiration lumen of the aspiration catheter, the dilation tube further having a compressible portion disposed between the distal and proximal ends of the dilation tube, the compressible portion configured for placement within a peristaltic pump such that operation of the peristaltic pump causes fluid from the aspiration lumen of the aspiration catheter to move through the dilation tube from the distal end of the dilation tube to the proximal end of the dilation tube; and a return conduit hydraulically connected to the dilation tube and configured to return to the vasculature of the subject fluid that has passed through the dilation tube from the distal to proximal end.

[0012]

[0012] In yet another embodiment of the present disclosure, a system for catheter aspiration includes a centrifugal pump, an aspiration catheter including an elongated shaft configured to be placed within a blood vessel of a subject, the shaft having an aspiration lumen with an open distal end and a proximal end, and a controller configured to operate the centrifugal pump.

[0013]

[0013] In yet another embodiment of the present disclosure, a system for real-time monitoring of catheter aspiration includes an ultrasonic sensor configured to be placed in fluid communication with a lumen that at least partially comprises the aspiration lumen of the catheter, the aspiration lumen configured to connect to a negative pressure source and the ultrasonic sensor configured to output a signal; a measuring device connected to the ultrasonic sensor and configured to count the number of times N during a predetermined time period P that the signal output by the ultrasonic sensor exceeds a predetermined threshold amplitude A, the measuring device further configured to determine whether the number of times N is less than or equal to a predetermined value V, or whether the number of times N exceeds or is equal to or greater than the predetermined value V; and a communication device connected to the measuring device and configured to enter a first communication mode when the number of times N is less than or equal to the predetermined value V, and to enter a second communication mode when the number of times N exceeds the predetermined value V or is equal to or greater than the predetermined value V.

[0014]

[0014] In yet another embodiment of the present disclosure, a system for catheter aspiration includes an aspiration catheter including an elongated shaft configured for placement within a blood vessel of a subject, the shaft including an aspiration lumen having open distal and proximal ends; an extension tube having distal and proximal ends and a lumen extending therebetween, the distal end of the extension tube configured to be hydraulically connected to the proximal end of the aspiration lumen of the aspiration catheter; a receptacle having an internal volume, the proximal end of the extension tube configured to deliver a substance flowing from the lumen of the extension tube to the internal volume of the receptacle; a scale configured to weigh at least the substance contained within the receptacle; and a communication element configured to indicate to a user the change in mass of the substance contained within the receptacle over time.

[0015]

[0015] In yet another embodiment of the present disclosure, a method for performing a thrombectomy procedure includes the steps of providing a system for aspiration including an aspiration catheter including an elongated shaft configured to be placed within a blood vessel of a subject, the shaft having an aspiration lumen with open distal and proximal ends, an extension tube having distal and proximal ends and a lumen extending therebetween, the distal end of the extension tube configured to be hydraulically connected to the proximal end of the aspiration lumen of the aspiration catheter, a receptacle having an internal volume, the proximal end of the extension tube configured to deliver material flowing from the lumen of the extension tube to the internal volume of the receptacle, and a scale configured to weigh at least the material contained within the receptacle; placing at least a distal portion of the elongated shaft within the blood vessel of the subject; causing at least a portion of the thrombus to be aspirated from the blood vessel of the subject, through the aspiration lumen of the aspiration catheter, through the lumen of the extension tube, and into the internal volume of the receptacle; and monitoring changes in the mass of the material within the receptacle over time.

[0016]

[0016] In yet another embodiment of the present disclosure, a system for catheter aspiration includes: an aspiration catheter including an elongated shaft configured for placement within a blood vessel of a subject, the shaft having an aspiration lumen, the aspiration lumen having an open distal end and a proximal end; an injection tube having an injection lumen extending therethrough, the injection tube configured to extend within the aspiration lumen and having a distal end and a proximal end, the distal end of the injection tube configured to be located within the aspiration lumen near the open distal end of the aspiration lumen; a micromachined cap externally covering the outer periphery of the distal end of the injection tube to provide a seal; and an orifice in at least one of the micromachined cap or the injection tube proximal to the micromachined cap, the orifice configured to generate one or more jets in the aspiration lumen when pressurized fluid is injected through the injection lumen.

[0017] In yet another embodiment of the present disclosure, a method for aspirating a thrombus includes the steps of providing an aspiration catheter having an elongated shaft with an aspiration lumen having a proximal end and an open distal end, and an infusion tube extending within the aspiration lumen and having an infusion lumen with a proximal end, a closed distal end, and an orifice at or adjacent to the closed distal end; attaching a pressurizable fluid source to the proximal end of the infusion lumen; connecting a pump to the proximal end of the aspiration lumen configured to aspirate fluid through the aspiration lumen in a distal-to-proximal direction; and positioning the aspiration catheter so that the open distal end of the aspiration lumen is at or adjacent to the thrombus. The method includes inserting a distal region of the shaft into the patient's vasculature; determining that a combination of injecting pressurized fluid through the infusion lumen and suction by the pump through the aspiration lumen is not sufficient to cause aspiration of the thrombus; advancing the aspiration catheter until the open distal end of the aspiration lumen is distal to the thrombus; injecting pressurized fluid through the infusion lumen without activating the pump at the aspiration lumen so that the pressurized fluid passes through and enters the aspiration lumen and enters the space distal to the thrombus from the open distal end of the aspiration lumen; and aspirating at least a portion of the thrombus by injecting pressurized fluid while activating the pump at the aspiration lumen.

[0018]

[0018] In yet another embodiment of the present disclosure, a system for catheter aspiration includes an aspiration catheter having an elongate shaft configured for placement within a blood vessel of a subject, the shaft having an aspiration lumen, the aspiration lumen having an open distal end and a proximal end; an injection tube having an infusion lumen extending therethrough, the injection tube extending within the aspiration lumen and being longitudinally adjustable relative to the elongate shaft, the injection lumen having an open distal end and a proximal end, the open distal end of the injection lumen being configured to extend distally from the open distal end of the aspiration lumen; and an orifice through a wall of the injection tube proximal to the open distal end of the injection lumen, the orifice configured to generate one or more jets in the aspiration lumen when pressurized fluid is injected through the injection lumen and when the injection lumen of the injection tube is occluded distal to the orifice through the wall of the injection tube. [Brief explanation of the drawings]

[0019] [Figure 1] FIG. 1 is a plan view of a system for aspiration according to one embodiment of the present disclosure.

[0020] [Figure 2A] FIG. 1 is a diagram of a suction monitoring system according to a first embodiment of the present disclosure.

[0021] [Figure 2B] FIG. 10 is a diagram of a suction monitoring system according to a second embodiment of the present disclosure.

[0022] [Figure 3] FIG. 10 is a diagram of a suction monitoring system according to a third embodiment of the present disclosure.

[0023] [Figure 4A] FIG. 1 is a cross-sectional view of an aspiration catheter within a blood vessel prior to contact with a thrombus.

[0024] [Figure 4B] FIG. 1 is a cross-sectional view of an aspiration catheter within a blood vessel when in contact with a thrombus.

[0025] [Figure 4C] FIG. 1 is a cross-sectional view of the aspiration catheter during vacuum reduction.

[0026] [Figure 4D] FIG. 1 is a cross-sectional view of a thrombus being aspirated through an aspiration catheter.

[0027] [Figure 5A] 4B is a graph of pressure versus time for the condition of FIG. 4A.

[0028] [Figure 5B] 4C is a graph of pressure versus time for the condition of FIG. 4B.

[0029] [Figure 5C] 4D is a graph of pressure versus time for the condition of FIG. 4C.

[0030] [Figure 5D] 4D is a graph of pressure versus time for the condition of FIG. 4D.

[0031] [Figure 6] 1 is a graph of pressure and output sound amplitude versus time for one embodiment of a suction monitoring system.

[0032] [Figure 7] 1 is a graph of pressure and output sound amplitude versus time for one embodiment of a suction monitoring system.

[0033] [Figure 8] 1 is a graph of pressure and output sound frequency versus time for one embodiment of a suction monitoring system.

[0034] [Figure 9] 1 is a graph of pressure and output sound frequency versus time for one embodiment of a suction monitoring system.

[0035] [Figure 10] FIG. 10 is a plan view of a system for aspiration according to another embodiment of the present disclosure.

[0036] [Figure 11] FIG. 10 is a plan view of a system for aspiration according to another embodiment of the present disclosure.

[0037] [Figure 12] FIG. 12 is a detailed view of the suction monitoring system of the system for suction of FIG. 11.

[0038] [Figure 13] FIG. 10 is a plan view of a system for aspiration according to another embodiment of the present disclosure.

[0039] [Figure 14] FIG. 14 is a detailed view of the suction monitoring system of the system for suction of FIG. 13.

[0040] [Figure 15] FIG. 1 is a schematic diagram of a system for aspirating thrombi, according to one embodiment of the present disclosure.

[0041] [Figure 16] 16 is a schematic diagram showing the proximal portion of the system for aspirating thrombi of FIG. 15 in more detail.

[0042] [Figure 17] 16 is a schematic diagram of the distal end portion of the system for aspirating thrombus of FIG. 15.

[0043] [Figure 18] FIG. 1 is a plan view of a portion of a multi-purpose system according to one embodiment of the present disclosure.

[0044] [Figure 19] FIG. 19 is a perspective view of a proximal portion of the multi-purpose system of FIG. 18.

[0045] [Figure 20] FIG. 1 is a plan view of a portion of a multi-purpose system according to one embodiment of the present disclosure.

[0046] [Figure 21] FIG. 21 is a detailed view of the distal end of the multi-purpose catheter of the multi-purpose system of FIG. 20.

[0047] [Figure 22] FIG. 21 is a perspective view of a proximal portion of the multi-purpose system of FIG. 20.

[0048] [Figure 23] FIG. 21 is a plan view of the proximal portion of the multi-purpose system of FIG. 20.

[0049] [Figure 24] FIG. 21 is a perspective view of a portion of the multi-purpose system of FIG. 20.

[0050] [Figure 25] FIG. 1 is a plan view of an aspiration catheter according to an embodiment of the present disclosure.

[0051] [Figure 26] FIG. 1 is a top view of a tubing set according to one embodiment of the present disclosure.

[0052] [Figure 27] FIG. 1 is a plan view of a stopcock according to one embodiment of the present disclosure.

[0053] [Figure 28] FIG. 1 is a plan view of a stopcock according to one embodiment of the present disclosure.

[0054] [Figure 29] FIG. 1 is a plan view of a vacuum source according to one embodiment of the present disclosure.

[0055] [Figure 30] FIG. 1 is a plan view of a suction system according to one embodiment of the present disclosure.

[0056] [Figure 31] FIG. 1 is a plan view of a suction system according to one embodiment of the present disclosure.

[0057] [Figure 32] FIG. 1 is a plan view of a suction system according to one embodiment of the present disclosure.

[0058] [Figure 33] FIG. 1 is a plan view of a suction system according to one embodiment of the present disclosure.

[0059] [Figure 34] FIG. 1 is a partial cross-sectional view of an embodiment of a saline infusion aspiration (thrombectomy) catheter with a guidewire in place, according to an embodiment of the present disclosure.

[0060] [Figure 35] FIG. 1 is a plan view of the proximal end of a guide catheter having an aspiration catheter disposed therein.

[0061] [Figure 36] FIG. 1 is a perspective view of an aspiration system according to one embodiment of the present disclosure.

[0062] [Figure 37] FIG. 1 is a perspective view of a subject being reinfused with blood according to one embodiment of the present disclosure.

[0063] [Figure 38] FIG. 1 is a perspective view of an aspiration system according to one embodiment of the present disclosure.

[0064] [Figure 39] FIG. 1 is a perspective view of an aspiration system according to one embodiment of the present disclosure.

[0065] [Figure 40] FIG. 1 is a perspective view of an ultrasonic sensor for use with an aspiration system according to one embodiment of the present disclosure;

[0066] [Figure 41] FIG. 41 is a plan view of a suction system having a y-connector with the ultrasonic sensor of FIG. 40 disposed therein.

[0067] [Figure 42] FIG. 42 is a perspective view of the console of the aspiration system of FIG. 41.

[0068] [Figure 43] FIG. 1 is a plan view of a suction system according to one embodiment of the present disclosure.

[0069] [Figure 44] FIG. 44 is a detailed view of the weight-based suction monitoring system of the system of FIG. 43.

[0070] [Figure 45] FIG. 1 is a perspective view of an aspiration system according to one embodiment of the present disclosure.

[0071] [Figure 46] FIG. 10 is a detailed view of another weight-based suction monitoring system of the system.

[0072] [Figure 47] FIG. 1 is a plan view of a suction system according to one embodiment of the present disclosure.

[0073] [Figure 48] FIG. 1 is a perspective view of an aspiration system according to one embodiment of the present disclosure.

[0074] [Figure 49] FIG. 1 is a cross-sectional view of a distal end of an aspiration catheter according to an embodiment of the present disclosure.

[0075] [Figure 50] FIG. 1 is a cross-sectional view of a distal end of an aspiration catheter according to an embodiment of the present disclosure.

[0076] [Figure 51] FIG. 1 is a cross-sectional view of a distal end of an aspiration catheter according to an embodiment of the present disclosure.

[0077] [Figure 52] FIG. 1 is a cross-sectional view of a distal end of an aspiration catheter according to an embodiment of the present disclosure.

[0078] [Figure 53] FIG. 1 is a plan view of a microcatheter being tracked over a guidewire in a first step.

[0079] [Figure 54] FIG. 10 is a plan view of the insertion of an insertable infusion tube and cap being inserted into a microcatheter in a second step according to an embodiment of the present disclosure.

[0080] [Figure 55] FIG. 10 is a plan view of the insertable infusion tube and cap advancing through the lumen of the microcatheter in a third step.

[0081] [Figure 56] FIG. 10 is a plan view of the insertable infusion tube and cap in a fully inserted position within the microcatheter in a fourth step.

[0082] [Figure 57] FIG. 10 is a perspective cross-sectional view of the distal end of an insertable infusion tube and cap with splines inserted into a microcatheter according to one embodiment of the present disclosure.

[0083] [Figure 58] FIG. 58 is a perspective view of the insertable fill tube and cap with splines of FIG. 57.

[0084] [Figure 59] FIG. 10 is a perspective cross-sectional view of the distal end of an insertable infusion tube and cap with splines inserted into a microcatheter according to one embodiment of the present disclosure.

[0085] [Figure 60] 1A-1C are diagrams illustrating one form of a method for treating a patient using an aspiration catheter and system according to one embodiment of the present disclosure. [Figure 61] 10A-10C are diagrams illustrating another form of a method for treating a patient using a suction catheter and system according to an embodiment of the present disclosure. [Figure 62] FIG. 10 is yet another diagram illustrating a method for treating a patient using an aspiration catheter and system according to an embodiment of the present disclosure. [Figure 63] FIG. 10 is yet another diagram illustrating a method for treating a patient using an aspiration catheter and system according to an embodiment of the present disclosure.

[0086] [Figure 64] 1A-1C are diagrams illustrating one form of a method for treating a patient using an aspiration catheter and system according to one embodiment of the present disclosure. [Figure 65] 10A-10C are diagrams illustrating another form of a method for treating a patient using a suction catheter and system according to an embodiment of the present disclosure.

[0087] [Figure 66] 1A-1C are diagrams illustrating one form of a method for treating a patient using an aspiration catheter and system according to one embodiment of the present disclosure. [Figure 67] 10A-10C are diagrams illustrating another form of a method for treating a patient using a suction catheter and system according to an embodiment of the present disclosure. [Figure 68] FIG. 10 is yet another diagram illustrating a method for treating a patient using an aspiration catheter and system according to an embodiment of the present disclosure. [Figure 69] FIG. 10 is yet another diagram illustrating a method for treating a patient using an aspiration catheter and system according to an embodiment of the present disclosure.

[0088] [Figure 70]FIG. 69 is a cross-sectional view of a translatable occluder of the suction system of FIGS. 66-69 in a first position according to an embodiment of the present disclosure.

[0089] [Figure 71] FIG. 70 is a cross-sectional view of the translatable occluder of the suction system of FIGS. 66-69 in a second position.

[0090] [Figure 72] FIG. 70 illustrates an optional blocking step in the method of FIGS. 66-69, according to one embodiment of the present disclosure.

[0091] [Figure 73] FIG. 1 is a perspective view of an aspiration system according to one embodiment of the present disclosure.

[0092] [Figure 74] FIG. 1 is a perspective view of an aspiration system according to one embodiment of the present disclosure. DETAILED DESCRIPTION OF THE INVENTION

[0093] This disclosure relates to an aspiration catheter system, including an aspiration system, for removing blood clots from a patient's vasculature, and a monitoring, alert, and communication system for the aspiration catheter system. Such vasculature may include veins and arteries, including coronary arteries, carotid arteries, cerebral arteries, and other arteries of the head and neck. Clogged aspiration catheters, for example, by large blood clots, is a common concern for users. Techniques for avoiding material clogging / occlusion within the catheter often involve quickly and aggressively advancing the aspiration catheter or gently picking at the edge of the clot to ensure that only a small piece or portion is introduced at a time, the piece being small enough not to clog or obstruct the aspiration lumen. If the device becomes clogged during use, the likelihood of accidental dislodgement of the clot downstream increases; this is called distal embolization. Because this type of aspiration procedure is often used in highly technical emergency settings, early detection of a clogged aspiration catheter for the user during aspiration can contribute to the success of the procedure and clinical outcome. Some sources report that up to 50% of used suction catheters become clogged during use.

[0094]

[0094] A user may have difficulty determining whether a vacuum or negative pressure is present in the system. For example, a user may have difficulty determining whether a vacuum or negative pressure is present (e.g., whether the vacuum source is on or off). Furthermore, a user may have difficulty determining whether a vacuum loss has occurred in the system due to, for example, a fluid-filled syringe (or other vacuum source) or a leak in the system. Blood is relatively opaque and can coat the walls of the syringe, making it difficult to determine when the syringe is filled. This makes it difficult to determine whether sufficient vacuum or negative pressure is being applied to the aspiration catheter. The negative pressure gradient may change to an unacceptable level even before the syringe is filled. Extension or other tubing may also cause a vacuum loss or negative pressure loss in the system. Certain tubing kinks may be difficult for a user to see or identify. It may also be difficult to determine whether there is an air leak in the system, which could be another cause of a vacuum loss or negative pressure loss, even before the syringe is filled with aspiration fluid.

[0095] During aspiration of a thrombus using a suction catheter, it is difficult to determine when the thrombus is being actively aspirated or when blood is simply being aspirated. Because maintaining normal blood volume and blood pressure is important, it is generally desirable to avoid aspirating large amounts of normal blood from a blood vessel. However, when tracking the tip of the suction catheter near a thrombus, it is difficult to know whether the suction catheter has actively engaged the thrombus, whether the suction catheter has aspirated at least a portion of the thrombus, or whether the suction catheter has not engaged the thrombus but merely aspirated blood. While some suction catheters, such as those used in peripheral blood vessels or arteriovenous fistulas, may be approximately 50 cm or less, the tip of the suction catheter may, in the same case, be more than 90 cm from the user's hand, as far as 135 cm, or even as far as 150 cm from the user's hand. The specific state of the suction capability at the tip of the catheter is often not apparent to the user. Thus, the user may essentially be poking the catheter blindly without any significant, useful sensory feedback. The outer diameter of the catheter may be up to 6 French or larger, and the height may be 10 French or larger. The increased catheter outer diameter raises concerns about potential intravascular trauma. The use of a suction catheter is therefore inefficient, does not minimize the length of the user's treatment as desired, and may result in blood loss, requiring transfusion in severe cases. Additionally, the increased volume of blood being aspirated means that the vacuum source (e.g., syringe) fills in a shorter time, thus necessitating more frequent replacement of the vacuum source. If the negative pressure gradient is insufficient and the user is unaware, peripheral embolism may occur.

[0096] In some cases, a syringe completely or nearly full of blood and / or clot may continue to be used, but this condition results in an inefficient use of time and a prolonged procedure due to the lack of sufficient pressure to effectively aspirate the clot or unwanted material. In some cases, a user may mistakenly fail to realize that the syringe plunger was not pulled back (to vent the syringe). In other cases, the syringe itself may be malfunctioning, preventing the user from achieving sufficient negative pressure without realizing it. In other cases, a kinked tube, line, or catheter may go unnoticed due to poor visibility in the procedure room or simply due to the amount of concurrent activity. Often, the user's eyes are directed, or focused, on a monitor, such as a fluoroscopy monitor or other imaging monitor, or a monitor containing vital patient data. While a user can see flow through a clear or partially clear lumen (e.g., an extension tube) with dim lighting associated with intermittent observation, it is difficult for the user to manipulate the flow of an opaque fluid (e.g., blood / clot) at will. Even with good lighting and focused eyes, the movement of fluid through the dilation tube may not provide an accurate picture of the aspiration status because the visual flow effect may lag relative to the applied vacuum or negative pressure. Multiple medical equipment personnel may share sensory information with each other to build a mutually conscious picture of the current state of the aspiration procedure. When one user relies on another's interpretation, especially if one is multitasking, a false sense of status may occur. Syringes attached to aspiration catheters may become kinked, for example, if placed on an uneven surface. The distal opening in the aspiration lumen of a suction catheter tends to draw suction directly against the vessel wall and thus may temporarily impinge on the vessel wall, stopping flow throughout the aspiration lumen. In some cases, excessively large negative pressure gradients may be applied to the aspiration lumen of a suction catheter, limiting its effectiveness (e.g., if it collapses the wall surrounding the aspiration lumen, thereby significantly reducing flow through the aspiration lumen).Syringes sometimes used as vacuum sources for connecting to the aspiration lumen of aspiration catheters can malfunction and fail to fully activate or evacuate. However, even when the syringe is functioning properly, it tends to fill at moments that are difficult to predict and therefore typically has periods when a negative pressure gradient is not applied. If a portion of a clot / thrombus is being aspirated through the aspiration lumen, a significant pressure drop can occur at the current location of the clot, and therefore sufficient negative pressure may exist only distally from the proximal end of the aspiration lumen to the point of the clot. Therefore, insufficient negative pressure may exist at the distal end of the aspiration lumen, such as the distal end of the aspiration catheter, resulting in insufficient aspiration. The same situation can occur if there is an actual blockage at some intermediate point within the aspiration lumen. In either of these situations, insufficient aspiration at the distal end of the aspiration lumen risks sending thrombi or emboli distal to the vasculature, which may result in blockage, stroke, pulmonary embolism, or other injury, depending on the location of the intervention or procedure being performed. With current equipment and techniques, these conditions are very difficult to detect when they occur. It is estimated that as many as 50% of thrombus aspiration procedures fail.

[0097] An aspiration system 2 is shown in FIG. 1 and is configured to enable real-time monitoring of catheter aspiration. The aspiration system 2 includes an aspiration catheter 4, a vacuum source 6, a valve 8, an extension tube 10, and an aspiration monitoring system 48 with an in-line pressure transducer 12. The aspiration catheter 4 has a proximal end 14 and a distal end 16 and an aspiration lumen 18 extending from the proximal end 14 to the distal end 16. The aspiration lumen 18 can be sized for aspiration of thrombus; in some embodiments, the aspiration lumen 18 can have an inner diameter of about 0.38 millimeters (0.015 inches) to about 2.54 millimeters (0.100 inches). The aspiration catheter 4 includes a hub 20 at its proximal end, which can include a female Luer connector 22. At the distal end 16 of the aspiration catheter 4, the aspiration lumen 18 can include a beveled opening 24 to aid in tracking through tortuous or occluded vasculature. In some embodiments, the guidewire lumen 26 is connected to the distal end 16 of the aspiration catheter 4 and is configured to be tracked by a guidewire 28. The vacuum source 6 may include a syringe and may be sized from 5 ml to 100 ml, or from 20 ml to 60 ml. The vacuum source 6 may include a VacLok® syringe manufactured by Merit Medical, Inc., South Jordan, Utah. The vacuum source 6 may include a barrel 30 and plunger 32 with a lock 34 configured to hold the plunger 32 in a position relative to the barrel 30, e.g., when the plunger 32 is retracted in direction D, a negative pressure (vacuum) is created within the barrel 30. In some embodiments, the vacuum source 6 may include any other type of evacuable container or may include a vacuum pump. The vacuum source 6 is connected to the aspiration lumen 18 of the aspiration catheter 4 via an extension tube 10 and a valve 8. In some embodiments, the vacuum source 6 can be directly connected to the aspiration lumen 18 of the aspiration catheter 4. A male luer connector 36 and a female luer connector 38 are shown in FIG. 1. As shown, the valve 8 may be a standard two-way stopcock.

[0098] The pressure transducer 12 of the suction monitoring system 48 is configured to be fluidly connected between the vacuum source 6 and the suction catheter 4. In FIG. 2A, the suction monitoring system 48 is shown as a first embodiment of a self-contained device. The pressure transducer 12 includes a housing 40 having a cavity 42 extending between a first port 44 and a second port 46. In some embodiments, the first port 44 includes a female luer and the second port 46 includes a male luer. In some embodiments, the first port 44 includes a female luer lock and the second port 46 includes a male luer lock, each of which is detachable with a corresponding luer lock of the opposite gender. The first port 44 is configured to be connected to the vacuum source 6, either directly or with a valve 8 and / or extension tube 10 connected therebetween. The second port 46 is configured to be connected to the suction lumen 18 of the suction catheter 4, for example, by connecting the second port 46 directly or indirectly to the hub 20 of the suction catheter 4. When the aspiration system 2 is used to aspirate bodily fluids and / or substances, such as blood and / or blood clots, the bodily fluids and / or substances are aspirated from the angled opening 24 at the distal end 16 to the female Luer connector 22 at the proximal end 14 through the aspiration lumen 18 of the aspiration catheter, then first through the second port 46 of the pressure transducer 12, through the cavity 42, and then through the first port 44. The pressure within the cavity 42 will vary depending on the amount of vacuum or negative pressure applied by the vacuum source 6 and the amount of flow resistance and resulting pressure drop along the aspiration system 2. For example, a highly viscous fluid, such as blood, or a fluid with solid, semi-solid, or gel-like particles or portions will generate a higher resistance to flow through the relatively small aspiration lumen 18 of the aspiration catheter 4 than will water or saline. Thus, the pressure within the cavity 42 of the pressure transducer 12 will decrease (i.e., a larger negative pressure gradient) as the resistance to flow within the aspiration lumen 18 increases.

[0099] For purposes of definition, when speaking of "vacuum," for example, a pressure of -15,000 Pascals (-2.18 pounds per square inch, or psi) is a "greater vacuum" than -10,000 Pascals (-1.45 psi). In reality, a true vacuum, where there are no molecules in that volume, is extremely difficult to achieve. Furthermore, -15,000 Pascals is a "lower pressure" than -10,000 Pascals. Also, since the absolute value of -15,000 is greater than the absolute value of -10,000, -15,000 Pascals has a greater "absolute vacuum pressure" than -10,000 Pascals. In FIG. 2A, vacuum sensor 50 is disposed within cavity 42 of housing 40 and is in fluid communication with the fluid passing through cavity 42. Vacuum sensor 50 can be a standard pressure sensor or transducer, including pressure sensors designed primarily to measure positive pressures. It may use any type of pressure sensing technology known in the art, including MEMS technology. In some embodiments, the vacuum sensor 50 is configured for highest precision and / or accuracy within a pressure range of about 0 Pascals to about −101,325 Pascals (−14.70 psi), or about −45,000 Pascals (−6.53 psi) to about −90,000 Pascals (−13.05 psi), or about −83,737 Pascals (−12 psi) to about −96,527 Pascals (−14 psi). In some embodiments, the power requirements for the vacuum sensor can range from 2.5 Volts DC to 10 Volts DC. In some embodiments, the vacuum sensor 50 can be an analog gauge of the output voltage. In the self-contained embodiment of FIG. 2A, the vacuum sensor 50 is powered by one or more batteries 52. Based on the power requirements of the vacuum sensor 50 described herein and the power requirements of the other components of the suction monitoring system 48, in some embodiments, the one or more batteries 52 can range from 1.5 Volts to 9 Volts. In some embodiments, a measurement device 54, which may include a microprocessor, is also included within the housing. A measuring device 54 is connected to the vacuum sensor 50 and receives a signal from the vacuum sensor 50 indicative of the real-time measured pressure.In some embodiments, the measurement device 54 includes a memory module 56 in which information is stored that can be used by the measurement device 54, for example, in calculations. The information can include, for example, an array of one or more pressure values. In some embodiments, the array of one or more pressure values ​​can be correlated with one or more different corresponding system or catheter models. The vacuum sensor 50 can, in some cases, be used to detect only the presence or magnitude of a vacuum or negative pressure for the purpose of monitoring whether the vacuum source 6 (e.g., a syringe) is sufficiently filled and therefore needs to be changed. The vacuum sensor 50 can, in some cases, be used to detect whether a vacuum or negative pressure is present in the system. For example, it can detect whether a vacuum or negative pressure has been applied (e.g., whether the vacuum source has been turned on or off).

[0100] One or more communication devices 58a, 58b, 58c are included within the suction monitoring system 48 and connected to the measurement device 54. Each of the one or more communication devices 58a-58c is configured to generate a type of alert, including an alert signal 60a-60c, in response to at least a portion of the operation and output of the measurement device 54. In some embodiments, the communication device 58a may include one or more LEDs (light-emitting diodes) configured to generate a visual alert via a visual alert signal 60a, such as a light that is illuminated continuously or in a flashing pattern. In some embodiments, the LEDs may be oriented on multiple sides of the communication device 58a so that they can be easily viewed from a variety of different positions. In some embodiments, lights other than LEDs may be used. Light pipes or other illumination conduits may also be incorporated into embodiments to further position the visual indicator in multiple positions and / or orientations. In some embodiments, communication device 58b may include one or more vibration generators configured to generate a tactile alert via tactile alert signal 60b, which may include, but is not limited to, vibration or heat. In some embodiments, the vibration generator may resemble a video game controller. In some embodiments, the vibration generator may include a piezoelectric element configured to vibrate when a voltage is applied. In some embodiments, communication device 58c may include one or more sound generating devices configured to generate an audible alert via audible alert signal 60c, such as a continuous or repetitive noise. In some embodiments, communication device 58c may include a speaker for generating any of a variety of sounds at any of a variety of frequencies (Hz) or sound pressures (dB) within the human hearing range and / or human tolerance range. Communication device 58c may be configured to generate sounds outside the human hearing range in embodiments where the signal is intended to be perceived as a vibration or other tactile sensation instead of an audible sensation. In some embodiments, the sound generating device may include a buzzer configured to emit one or more audible pitches when a voltage is applied.In some embodiments, a piezoelectric element such as that described in connection with communication device 58b can also function as a sound generating device such as that included in communication device 58c. Alert signals 60a-60c can function as a "wake up" warning to the user if the user becomes too focused on other factors during the procedure.

[0101] A user of the aspiration system 2 may wish to be notified of several conditions that may arise during use of the aspiration system 2. These potential conditions include, but are not limited to, a loss of vacuum or negative pressure due to a clog, a break, crack, or puncture in the vacuum source 6 and / or the aspiration system 2, and the involvement or aspiration of a non-liquid, solid, or semi-solid material, such as a blood clot. The aspiration monitoring system 48 of FIG. 2A is configured to alert a user of the aspiration system 2 about the real-time status of the aspiration system 2, including operational status: whether or not a vacuum or negative pressure is applied; flow status, including whether or not a blood clot is involved, whether or not a blood clot is being actively aspirated, whether or not the system is leaking air, whether or not the system is clogged, whether the vacuum source 6 is full and / or needs to be changed; or other potential configuration issues. The real-time feedback provided frees the user or operator from the need for excessive personal monitoring of the vacuum source 6, the extension tube 10, or other parts of the aspiration system 2 for improper or undesirable flow or operating conditions, thereby allowing the user to focus more on the patient receiving treatment. The user knows whether a clot is being aspirated or has already been aspirated, or if there is a blockage. Additionally, the user knows whether too much blood is being drawn from the patient, or if there is a fault condition such as a leak or tubing kinks in the system. Tubing kinks distal to the vacuum sensor 50 can be identified (e.g., by an increase in the measured negative pressure), and tubing kinks proximal to the vacuum sensor 50 can be identified (e.g., by a drop or decrease in the negative pressure gradient). In some cases, the user can attempt to operate the catheter with a vacuum source 6 that is already full (and therefore does not have a significant negative pressure gradient). In some cases, the user may forget to open valve 8 to initiate suction, but the suction monitoring system 48 will be able to identify that the system is still not functioning and communicate a list of potential or specific errors (for the particular pressure waveform measured).Real-time awareness of the many factors related to operating conditions may result in safer procedures, shorter procedure times, and reduced blood loss.

[0102] The pressure transducer 12 of the aspiration monitoring system 48 is configured to continuously measure and monitor absolute pressure amplitude within the closed system of the aspiration system 2, and also to measure and monitor relative pressure over time to detect notable flow changes within the flow circuit of the aspiration system 2. While some changes can be identified through absolute pressure measurements, more subtle pressure variations can be compared to a library stored in memory. Notable conditions can be notified to the user in a timely manner. In some embodiments, the unfiltered signal may be amplified by an amplifier and filtered by a filter, for example, to increase the signal-to-noise ratio. Examples of (background) noise 57 in the unfiltered signal can be seen in Figures 5A-5D (labeled in Figure 5A). In some embodiments, one or more algorithms, as described herein, can be used to identify specific conditions of interest.

[0103] FIG. 2B illustrates a second embodiment of a suction monitoring system 62 having a pressure transducer 12 with a vacuum sensor 50 disposed within the cavity 42 of the housing 40. The vacuum sensor 50 may be powered by at least one battery 52. ​​In some embodiments, the pressure transducer 12 is reusable and may be configured to allow charging of the battery 52 or a capacitor (not shown) via direct charging methods or via inductive power transfer methods and devices known in the art. Unlike the suction monitoring system 48 of FIG. 2A, the suction monitoring system 62 of FIG. 2B includes a measurement device 64, a memory module 66, and a communication device 68 that are external to the pressure transducer 12. A power supply module 72 is also external and can be used to power either the measurement device 64, the memory module 66, or the communication device 68. The communication device 68 may be any of the communication devices 58a, 58b, or 58c described in connection with the suction monitoring system 48 of FIG. 2A and is configured to generate an alert via an alert signal 70. The communication device 68 may be portable so that it can be located near the user.

[0104] In some embodiments, the communication device 68 may be user-wearable. FIG. 3 illustrates an aspiration monitoring system 78 including an antenna 80 connected to a measurement device 76. The measurement device 76 is similar to the measurement device 54 of the previous embodiment, except that the measurement device 76 wirelessly transmits a communication signal 84 via the antenna 80 to a corresponding antenna 82 of the communication device 74. In some embodiments, the communication device 74 includes a wristband worn by the user, which may include a vibration or heat generator. In some embodiments, the communication device 74 includes an audio speaker that can be attached to the device or to the patient or user. In some embodiments, the communication device 74 includes an audio speaker with an earpiece or earphone that can be worn by the user. In some embodiments, Bluetooth® communication technology may be used. The real-time feedback provided by the aspiration monitoring system 62 can reduce the time the aspiration system 2 is actively aspirating without engaging a clot, thereby minimizing the amount of non-thrombogenic blood lost through aspiration. This may be particularly beneficial in larger bore catheters, e.g., catheters with a diameter of 7 French or greater. Real-time feedback can also minimize the total time the catheter is tracked back and forth through the vessel, minimizing potential damage to the vessel intima, vessel dissection, or distal embolization. By reducing the risk of the aspiration catheter tip becoming trapped against the vessel wall (due to suction), the distal end of the aspiration lumen can be more aggressively designed for optimal aspiration characteristics. Furthermore, techniques using aspiration catheters can be performed in a more sophisticated manner, with intermittent or continuous knowledge of the aspiration status or sufficiency of the negative pressure gradient. For example, a thrombus fragment may be aspirated, followed by a blood aspiration "chaser," followed by another thrombus fragment, and so on.

[0105] FIG. 4A shows the distal end 16 of the aspiration catheter 4 within a blood vessel 86 having at least one thrombus 88. The aspiration catheter 4 is advanced in a forward direction F, but the distal end 16 of the aspiration catheter 4 has not yet reached the proximal end 94 of the thrombus 88. The vacuum source 6 (FIG. 1) is connected to the aspiration lumen 18 of the aspiration catheter 4 and is activated (i.e., valve 8 opens) to draw blood 96 into the aspiration lumen 18 (arrow A). Referring to FIG. 5A, a corresponding curve 98 is depicted for a vacuum or negative pressure of a typical fluid (e.g., blood) over time relative to the conditions of FIG. 4A. The curve 98 depicts the vacuum or negative pressure sensed over time by the vacuum sensor 50 of any of the embodiments presented. With no leaks and no thrombus expelled, the curve 98 includes a downward slope 99 as the vacuum source 6 reduces the pressure within the cavity 42 of the pressure transducer 12 to a relatively steady state. A stable pressure curve 97 continues while blood 96 is being aspirated. When vacuum source 6 is disconnected from aspiration lumen 18, for example, by closing valve 8 or by disconnecting any two ports (e.g., luers), or when vacuum source 6 is completely filled with blood 96, then an upslope 95 is measured.

[0106] To identify this condition, the measurement device 54, 64 is configured to compare the curve 97 with information stored in the memory module 56, 66. In some embodiments, the measurement device 54, 64 uses an algorithm to make the comparison. In some embodiments, the measurement device 54, 64 then sends a signal to the communication device 58a-58c, 74, which generates an appropriate alert. For example, the communication device 58a may illuminate a particular color LED, or the LED may flash in a particular pattern or number of times. The communication device 58b may create a distinctive sound or generate an audio message in several languages. For example, the audio message may state "thrombus encountered" or "thrombus not encountered." Different types of sounds may be used for each of the multiple "modes" of "thrombus encountered," "active flow," and "vacuum not present." For example, a buzz may be used for "thrombus encountered" and a beep may be used for "vacuum not present." Characteristics of the sound that may be varied include, but are not limited to, timbre, quality, spectrum, envelope, duration, phase, pitch (frequency), number of sounds (repetitions), etc. The communication device 58c may vibrate or heat in a characteristic pattern, for example, for a specific number of repetitions or at a specific frequency between repetitions. The user may determine that additional fluoroscopic images (e.g., angiography) or other imaging modalities may be required to better identify the location of the thrombus 88.

[0107] FIG. 4B shows the distal end 16 of the aspiration catheter 4 advanced to a position where the distal end 16 contacts the proximal end 94 of the thrombus 88. The corresponding curve 93 in FIG. 5B represents the vacuum or negative pressure sensed over time by the vacuum sensor 50 of any of the presented embodiments. As shown in FIG. 4B and graphed in FIG. 5B, curve 93 initially has a downward slope 99 followed by a stable pressure curve 97; however, when the distal end 16 of the aspiration catheter 4 contacts the proximal end 94 of the thrombus 88, if the suction causes a portion of the thrombus 88 (e.g., a large or relatively rigid portion) to enter and become trapped in the aspiration lumen 18, a clog condition then occurs. If the distal end 16 of the aspiration catheter 4 becomes lodged on the thrombus 88 due to the suction effect, a similar condition occurs, with virtually no fluid flowing through the aspiration lumen 18. In either condition, curve 93 includes a deviation (or blockage) in the fluid pressure 91. If the blockage (or stuck condition) continues, a flat, reduced pressure 89 is measured.

[0108] The measurement device 54, 64 is configured to compare the curve 93 with information stored in the memory module 56, 66 to identify this condition. In some embodiments, the measurement device 54, 64 uses an algorithm to make the comparison. In some embodiments, a preset pressure difference ΔP1 can be stored in the memory module 56, 66 as a threshold value, such that measuring a pressure difference 81 below this threshold results in the measurement device 54, 64 not instructing the communication device 58a-58c, 74 to send an alert signal 60a-60c, 70. In some embodiments, if the pressure difference 81 exceeds (or is greater than or equal to) the preset pressure difference ΔP1, then the measurement device 54, 64 sends a signal to the communication device 58a-58c, 74, which generates an appropriate alert. For example, the communication device 58a may be illuminated, e.g., a particular color LED, or the LED may flash in a particular pattern or number of flashes. Communication device 58b may create a distinctive sound or generate an audio message in several languages. For example, the audio message may state "Locking Condition." Communication device 58c may vibrate or heat in a distinctive pattern, for example, for a specific number of repetitions or at a specific frequency between repetitions. Once the user recognizes that a blocking condition exists, the user may pull and retract aspiration catheter 4 in an attempt to contact a portion of thrombus 88 that can be aspirated. If a portion of thrombus has lodged in aspiration lumen 18 and repositioning aspiration catheter 4 does not produce successful results, aspiration catheter 4 may be removed and aspiration system 2 may be re-purged, for example, by positive pressure.

[0109] 4C illustrates the distal end 16 of the aspiration catheter 4 in a typical situation when a break occurs in the aspiration system 2. For example, a crack, leak, puncture, pinhole, looseness, or break may draw air into the aspiration lumen 18 of the aspiration catheter 4, the cavity 42 of the pressure transducer 12, the interior of the dilation tube 10, the valve 8, or the vacuum source 6. As graphed by curve 85 in FIG. 5C, a downward slope 99 followed by a stable pressure curve 97 is measured, but at the time of break 87, an upward slope 83 begins.

[0110] The measuring device 54, 64 is configured to compare the curve 85 with information stored in the memory module 56, 66 to identify this condition. In some embodiments, the measuring device 54, 64 uses an algorithm to make the comparison. In some embodiments, the measuring device 54, 64 then sends a signal to the communication device 58a-58c, 74, which generates an appropriate alert. For example, the communication device 58a may illuminate a specific color LED, or the LED may flash in a specific pattern or number of times. The communication device 58b may create a distinctive sound or generate an audio message in several languages. For example, the audio message may state "system leak." The communication device 58c may vibrate in a distinctive pattern, for example, for a specific number of repetitions or at a specific frequency for a specific number of repetitions, or may heat up. Upon receiving the alert, the user is prompted to check the components of the aspiration system 2 and repair any damage or replace one or more of the components of the aspiration system 2. For example, in some cases, when the measuring device 54, 64 identifies a decrease in the applied vacuum or negative pressure, the communication devices 58a-58c, 74 can alert the user so that the user can change or recharge the depleted vacuum source 6 (e.g., by filling it with blood and / or blood clots).

[0111] 4D shows the distal end 16 of the aspiration catheter 4 upon successful aspiration of a piece or portion 90 of the thrombus 88. In some cases, the piece or portion 90 may travel a tortuous path 92 due to obstructions or collisions with the inner wall of the aspiration lumen 18 while being pulled through the aspiration lumen 18. In some cases, the piece or portion 90 may catch on or slip within the inner wall of the aspiration lumen 18 due to, for example, variations in the inner diameter of the aspiration lumen 18 along its length. Either of these situations may cause a corresponding series of increases and decreases in pressure detected by the pressure transducer 12 while the piece or portion 90 is moving through the aspiration lumen 18. As shown by curve 79 in FIG. 5D, a downward slope 99 followed by a stable pressure curve 97 is measured. As a piece or portion 90 of thrombus 88 moves down the aspiration lumen 18 of the aspiration catheter 4, a fluid pressure deviation 77, including one or more increases or decreases in pressure (increases or decreases in vacuum or negative pressure), is measured. Once the piece or portion 90 of thrombus 88 exits the proximal end of the aspiration lumen 18 of the aspiration catheter 4, a second stable pressure curve 75 is measured. The duration 67 of the deviation 77 is the transit time of the particular significant piece or portion 90 of thrombus 88. The duration 67 can range significantly, but in some cases may be less than one second or up to approximately 30 seconds. A single thrombus being aspirated may cause a single pressure drop (blip) identified by the measurement devices 54, 64. This occurrence may then be communicated to the user via the communication devices 58a-58c, 74. Repeatedly, as additional pieces or portions 90 of the thrombus 88 are aspirated and move down the aspiration lumen 18 of the aspiration catheter 4, another deviation 73 in fluid pressure is measured, including one or more increases or decreases in pressure (increases or decreases in vacuum or negative pressure). At the end of the curve 79, the vacuum source 6 is shown to be completely filled with blood 96 and pieces or portions 90 of the thrombus 88, and an upward slope 95 is measured.

[0112] To distinguish between when a piece or portion 90 of thrombus 88 is being actively aspirated, as in deviations 77 and 73, and when a piece or portion 90 of thrombus 88 is not being actively aspirated or is not substantially aspirated, as in stable pressure curve 97, stable pressure curve 75, and stable pressure curve 71, measurement device 54, 64 is configured to compare curve 79 with information stored in memory module 56, 66. In some embodiments, measurement device 54, 64 uses an algorithm to make the comparison. In some embodiments, a predetermined pressure difference ΔP2 can be stored in memory module 56, 66 as a threshold value, such that measuring a pressure difference 69 below this threshold results in measurement device 54, 64 not instructing communication device 58a-58c-74 to send a first type of alert via alert signal 60a-60c-70. In some embodiments, if the pressure differential 69 exceeds (or is greater than or equal to) the preset pressure differential ΔP2, then the measurement device 54, 64 sends a signal to the communication device 58a-58c, 74, which generates an appropriate alert. The communication device 58a may be illuminated, e.g., a particular color LED, and the LED may flash in a particular pattern or number of flashes. In some embodiments, the communication device 58a may include a light, the intensity of which increases proportionally to the pressure. The communication device 58b may create a distinctive sound or generate an audio message in several languages. For example, the audio message may state, "The clot is being aspirated." In some embodiments, the communication device 58b may include one or more noises or beeps. In some embodiments, the communication device 58b may include a particular sequence of beeps, each corresponding to a different condition. For example, three short beeps may correspond to the clot not being aspirated, while five long, loud beeps may correspond to a system leak. In some embodiments, several different tones (pitches) may be used to alert the user about different conditions.As an example, a low-pitched tone can be used for a first condition (e.g., clot not being aspirated), and a second, higher-pitched tone can be used for a second condition (e.g., a system leak). In some embodiments, a different set of tones can be used to alert the user about a first condition, and a second set of tones (e.g., in a different combination or with additional tones) can be used to alert the user about a second condition. The communication device 58c can vibrate or heat in a distinctive pattern, for example, for a specific number of repetitions or at a specific frequency between repetitions. Once the user recognizes that the clot is being aspirated, the user can choose to advance (or retract) the aspiration catheter 4 along the length of the clot 88 in an attempt to continue aspirating the clot 88, for example, through fluoroscopic visualization. In some cases, the user can choose to stop advancing or retracting the aspiration catheter 4 a certain amount of time after the alert is generated to allow a piece or portion 90 of the clot 88 to completely exit the aspiration lumen 18. When the measurement device 54, 64 identifies a stable pressure curve 75, 71 following a deviation 77, 73, the measurement device 54, 64, in some embodiments, transmits a signal that causes the communication device 58a-58c, 74 to generate a second type of alert via the alert signal 60a-60c, 70. For example, in some embodiments, the communication device 58b can transmit an audio message stating, "No more clots are being aspirated." Once the user realizes that no more clots are being aspirated, the user can advance or retract the aspiration catheter in an attempt to contact another portion of the clot 88 that can be aspirated. In some embodiments, the deviation 77 can be reliably identified as a true deviation indicating that the clot is being actively aspirated, and the pressure differential 69 is between about 700 Pascals and about 1700 Pascals. In some embodiments, the deviation 77 can be reliably identified as a true deviation indicating that the clot is being actively aspirated, and the pressure differential 69 is between about 1000 Pascals and about 1300 Pascals.In some embodiments, deviation 77 can be reliably identified as a true deviation indicating that a clot is being actively aspirated, with pressure differential 69 being approximately 1138 Pascals. Pressure differential 69 can be measured by determining baseline pressure 63 and peak pressure 61 and determining the difference in absolute values.

[0113] For example: Absolute Value Difference (AVD) = |(-89631 Pascals)-(-90769 Pascals)| = 1138 Pascals Or, for example: Absolute Value Difference (AVD) = |(-43710 Pascals)-(-45102 Pascals)| = 1281 Pascals

[0114]

[0114] Additionally, the pressure differential 81 (Fig. 5B) may represent a deviation that the communication devices 58a-58c, 74 may identify in a similar manner after which they may generate an appropriate alert, such as a "blockage condition."

[0115] Because the vacuum or negative pressure has a nominal value less than zero, the peak pressure 61 is actually lower than the reference pressure 63, as shown in FIG. 5D. In some embodiments, the measurement device 54, 64 may be configured to compare, for example, by using an algorithm, the stored difference time t1 with the duration 65 of only one of the one or more increases or decreases in pressure of the deviation 77. For example, in some embodiments, if the duration is between about 0.001 seconds and about 0.50 seconds, the deviation may be positively identified as a true deviation indicating that a clot is being actively aspirated. In some embodiments, if the duration is between about 0.005 seconds and about 0.10 seconds, the deviation may be positively identified as a true deviation indicating that a clot is being actively aspirated. In some embodiments, if the duration is between about 0.05 seconds and about 0.20 seconds, the deviation may be positively identified as a true deviation indicating that a clot is being actively aspirated. In some embodiments, the measurement device 54, 64 is configured to recognize the deviation 77 after measuring two or more increases or decreases in pressure. In some embodiments, the measurement device 54, 64 is configured to recognize a deviation 77 after measuring five or more increases or decreases in pressure. In some embodiments, the measurement device 54, 64 is configured to recognize a deviation 77 after measuring ten or more increases or decreases in pressure.

[0116] In some embodiments, the reference pressure 63 may be predetermined or stored in the memory module 56, 66. In some embodiments, the reference pressure 63 may be stored in the memory module 56, 66 during manufacture of the suction monitoring system 48, 62, 78, or the reference pressure 63 may be input by a user before or during a particular procedure. In some embodiments, the reference pressure 63 may be determined or otherwise defined by the measurement device 54, 64, 76 based on averaging a specific number of measured pressure samples. The reference pressure 63 may be configured as a moving average, such as a running or rolling average. Several types of moving averages may be used, including a simple moving average, a cumulative moving average, a weighted moving average, or an exponential moving average. In any of these cases, a threshold value may be determined by the measurement device 54, 64, 76 based on the determined reference pressure 63 and a known pressure difference ΔP. In some cases, the pressure difference ΔP may also be calculated by the measurement device 54, 64, 76 based on the determined reference pressure 63 and a known threshold value.

[0117] Insertion of a pressure transducer 12 consistent with either the embodiment of FIG. 2A or the embodiment of FIG. 2B does not significantly alter the performance characteristics of the aspiration system 2 because the cavity 42 is relatively short and has a relatively large inner diameter, and is therefore not a significant source of fluid flow resistance. In some embodiments, the inner diameter may be approximately 2.2 mm (0.086 in.) to approximately 3.2 mm (0.125 in.). In some embodiments, the measurement device 54, 64, 76 need not include a microprocessor, as predefined set points (e.g., at specific thresholds) may be included in firmware, a microcontroller, or other locations. In some embodiments, without limitation to the embodiment of FIG. 2B, the pressure transducer 12 may be an off-the-shelf blood pressure monitor system modified or extended with other components. In some embodiments, an off-the-shelf blood pressure monitor system may be used as the output of the aspiration monitoring system 48, 62, 78. In some embodiments, the aspiration catheter 4 may have a pressure transducer at its distal end 16. This pressure transducer may be used as the pressure transducer 12 for the aspiration monitoring system 48, 62, 78. In some embodiments, the pressure sensor may be located within the introducer sheath, guide catheter, or other component of the system that is in fluid communication with the Tuohy-Borst valve and aspiration lumen 18. In some embodiments, the pressure sensor can be located anywhere within the aspiration lumen of the aspiration catheter.

[0118] In some embodiments, instead of LEDs, visual alerts can be provided by a communication device 58a with a display that displays a visual message in a specific language, such as "thrombus encountered," "thrombus not encountered," "clogged condition," "system leak," "low vacuum," "thrombus being aspirated," or "no more thrombus aspirated." The visual message can be combined with any of the other alert signals 60a-60c, 70 described herein. The aspiration monitoring systems 48, 62, 78 described herein provide real-time awareness to a user performing an aspiration procedure, such as removing a thrombus with the aspiration system 2. One skilled in the art will recognize that knowing the real-time status of the aspiration system 2 allows a user to immediately modify the procedure to optimize results, increase safety for the patient and / or medical personnel, reduce costs (e.g., the number of vacuum sources 6 required), and reduce procedure time (and cost-effectiveness). Because users typically perform multiple tasks during a suction procedure, the sensory assistance provided by the suction monitoring system 48, 62, 78 allows the user to focus on these tasks without constantly trying to monitor conditions that are often difficult to monitor visually. The user can also modify and control the suction monitoring system 48, 62, 78 through an input 59 (FIG. 2B), which may be a data entry module, a keyboard, or a series of buttons associated with a display. In some embodiments, the input 59 may include an auditory input that accepts voice commands. Alternatively, the user may enter information and control the suction monitoring system 48, 62, 78 remotely.Some alerts that a user can select or deselect in the aspiration monitoring system 48, 62, 78 include, but are not limited to: whether the aspiration system 2 is potentially blocked or clogged or is flowing normally; whether a clot has been contacted; whether a clog has occurred; whether the vacuum source 6 is adequate or whether the vacuum source 6 is worn out and requires replacement; whether a leak is present in the aspiration system 2; whether the aspiration system 2 components are configured or connected correctly or incorrectly; whether to advance the catheter distally; whether to reverse the catheter; whether to continue moving the catheter at the same speed; whether to increase or decrease the speed of catheter advancement; whether a clot is being actively aspirated; and whether to stop actively aspirating a clot. As a user becomes more familiar with the aspiration monitoring system 48, 62, 78, the user may also unconsciously initiate specific responses to the system. For example, a user may automatically retract the catheter upon hearing a clot warning signal (e.g., three beeps), automatically initiate catheter advancement upon hearing a free flow signal (e.g., two beeps), and / or initiate fluoroscopic visualization. By "being one" with the suction monitoring system 48, 62, 78 and the catheter, the user optimizes their reactions and actions. This can help improve the skill of having the catheter take a small "bite" of a clot, flushing / opening the lumen following the bite associated with some fast-flowing blood "chaser." This also helps minimize the opportunity for clogging, reducing system maintenance or correction (catheter removal, lumen flushing outside the patient, catheter replacement). The overall user experience is improved because the user gets immediate gratification and is immediately notified of any errors or instances of concern.

[0119] In some embodiments, alternative power sources may be used, such as standard AC power with or without an AC / DC converter; direct connection to existing equipment (e.g., a vacuum pump); or solar power. The suction monitoring systems 48, 62, 78 may be packaged sterile or re-sterilizable by techniques known to those skilled in the art. In some embodiments, a flow meter or volume meter may be used in conjunction with or in place of the pressure gauge 12, for example, to determine clogs or changes in the magnitude of vacuum or negative pressure. In some embodiments, the input 59, power module 72, measurement device 64, memory module 66, and communication device 68 (e.g., of FIG. 2B) may all be incorporated into a single external device, which may in some cases be sold separately. In some embodiments, the external device may also have other functions, such as providing suction and / or infusion (negative and / or positive pressure) to the catheter. In other embodiments, the external device may include some, but not all, of the input 59, power module 72, measurement device 64, memory module 66, and communication device 68. For example, in some embodiments, communication device 58 (FIG. 2A) can replace external communication device 68 and can be mounted on suction monitoring system 48, while input 59, power module 72, measurement device 64, and memory module 66 (FIG. 2B) are incorporated into a single external device. Many combinations are possible, as described in more detail herein.

[0120] Although aspiration of thrombi has been described in detail, the aspiration monitoring systems 48, 62, 78 have utility in any aspiration application in which a heterogeneous medium is being aspirated. This may include aspiration of emboli (not including thrombotic emboli) from ducts, vessels, or cavities of the body, or from solid or semi-solid parts of the body, including, but not limited to, fat, breast, and parts of cancerous tissue.

[0121] In some embodiments, the aspiration system 2 will be provided to the user as a kit having all or some of the described components, while in other embodiments, only the aspiration monitoring system 48 is provided. While the discussion herein includes embodiments for aspirating clots and blood, the definition of the term "fluid" should be understood throughout to include liquids and gases.

[0122] In some embodiments, additional or alternative sensors may be used to monitor flow conditions for notification to the user, including, but not limited to, a Doppler sensor, an infrared sensor, or a laser flow detector. In some embodiments, an external Doppler sensor may be used. In some embodiments, an infrared sensor or a laser flow detector may be used around the dilation tube 10.

[0123] Further embodiments allow for real-time communication of the specific value of fluid pressure (e.g., vacuum level or negative pressure level) measured by sensor 50. For example, as the negative pressure gradient increases, the audible tone may increase in proportion to the sound intensity or sound pressure level (dB). Alternatively, the pitch (frequency) of the audible tone can increase as the negative pressure gradient increases and decrease as the negative pressure gradient decreases (similar to a siren). By controlling either the signal amplitude or the signal frequency proportionally to the fluid pressure, the system can give the user a real-time sense of whether the negative pressure gradient is increasing, decreasing, or remaining constant, as well as whether the pressure is near or quite different from zero. When an audible tone is used as a signal, the user's eyes can remain focused on the procedure by looking at a fluoroscopic monitor, the patient, or another piece of equipment.

[0124] FIG. 6 illustrates a graph 800 of time (x-axis) and multiple variables (y-axis). A pressure curve 802 illustrates the application of vacuum or negative pressure with a pressure drop 808, followed by a maintenance of vacuum 810a with a decrease in vacuum or negative pressure 812 and an increase in vacuum or negative pressure 814. A removal of vacuum or negative pressure 816 is shown at the end of the pressure curve 802. In some cases, the decrease in vacuum or negative pressure 812 may be caused by a temporary or permanent leak or detachment in the system or by the loading of a vacuum source (e.g., a syringe). In FIG. 6, the decrease in vacuum or negative pressure 812 is shown temporarily, followed by a maintenance of vacuum 810b. The increase in vacuum or negative pressure 814 may in some cases be caused by a clot being aspirated through the system and may occur over a short or long period of time and may be steady or intermittent. While the amount of reduced pressure applied to the pressure curve 802 varies, in some embodiments, it may be desirable to generally indicate to the user only whether or not vacuum or negative pressure is being applied. The measurement device 54, 64, 76 may be configured to apply an algorithm to the signal from the vacuum sensor 50 (pressure sensor) that calculates the inverse value represented by dashed curve 804. The measurement device 54, 64, 76 may further apply an algorithm to increase, amplify, or otherwise enhance the signal to facilitate discrimination, for example, within the range of human audible discrimination (hearing). For example, a modified signal curve 806 may be created that has the following general mathematical relationship to the signal from the vacuum sensor 50 represented by pressure curve 802:

[0125] Sound pressure level (dB) = A + B × (1 / fluid pressure) where A is the first constant, B is the second constant.

[0126]

[0126] In one particular example, a modified signal curve 806 can be created that has the following mathematical relationship with the signal from the vacuum sensor 50 represented by the pressure curve 802:

[0127] Sound pressure level (dB) = 70 + 20 × (1 / fluid pressure (kPa)) where dB is the decibel unit, kPa is the unit of kilopascal.

[0128]

[0128] The modified signal curve 806 can be configured by an algorithm so that the sound pressure level drops below the audible level of human hearing at relatively small vacuum or negative pressure magnitudes, giving the user an "on / off" perception of the vacuum or negative pressure being applied.

[0129] FIG. 7 illustrates a graph 820 of time (x-axis) and multiple variables (y-axis). A pressure curve 822 illustrates the application of vacuum or negative pressure with a pressure drop 828, followed by a maintenance of vacuum or negative pressure 830a with a decrease in vacuum or negative pressure 832 and an increase in vacuum or negative pressure 834. A removal of vacuum or negative pressure 836 is illustrated at the end of the pressure curve 822. In some cases, the decrease in vacuum or negative pressure 832 may be caused by a temporary or permanent leak or detachment in the system or by the loading of a vacuum source (e.g., a syringe). In FIG. 7, the decrease in vacuum or negative pressure 832 is illustrated temporarily, followed by a maintenance of vacuum or negative pressure 830b. The increase in vacuum or negative pressure 834 may in some cases be caused by a clot being drawn through the system and may occur over a short or long period of time and may be steady or intermittent. In some cases or configurations, it may be desirable for a user to have very specific real-time or approximate real-time characteristics of the magnitude or level of the applied vacuum (generally, negative pressure gradient). The measurement device 54, 64, 76 may be configured to apply an algorithm to the signal from the vacuum sensor 50 (pressure sensor) that calculates an absolute value represented by dashed curve 824. The measurement device 54, 64, 76 may further apply an algorithm that increases, amplifies, or otherwise enhances the signal to facilitate discrimination, for example, within the range of human audible discrimination (hearing). For example, a modified signal curve 826 may be created that has the following general mathematical relationship to the signal from the vacuum sensor 50 represented by pressure curve 822:

[0130]

[0130] Sound pressure level (dB) = A + B × |(fluid pressure)| where A is the first constant, B is the second constant.

[0131]

[0131] In one particular example, a modified signal curve 826 can be created that has the following mathematical relationship with the signal from vacuum sensor 50 represented by pressure curve 822:

[0132]

[0132] Sound pressure level (dB) = 2 × |(fluid pressure (kPa))| where dB is the decibel unit, kPa is the unit of kilopascal.

[0133]

[0133] The modified signal curve 826 may be configured with an algorithm such that the sound pressure level follows the magnitude of the vacuum or negative pressure being applied, and therefore appears to the user to increase as the vacuum or negative pressure increases.

[0134] FIG. 8 illustrates a graph 840 of time (x-axis) and multiple variables (y-axis). A pressure curve 842 illustrates a vacuum or negative pressure being applied with a pressure drop 848, followed by a maintenance of vacuum or negative pressure 850a with a decrease in vacuum or negative pressure 852 and an increase in vacuum or negative pressure 854. A removal of vacuum or negative pressure 856 is illustrated at the end of the pressure curve 842. In some cases, the decrease in vacuum or negative pressure 852 may be caused by a temporary or permanent leak or detachment in the system or by the loading of a vacuum source (e.g., a syringe). In FIG. 8, the decrease in vacuum or negative pressure 852 is illustrated temporarily, followed by a maintenance of vacuum or negative pressure 850b. The increase in vacuum or negative pressure 854 may in some cases be caused by a clot being drawn through the system and may occur over a short or long period of time and may be steady or intermittent. As mentioned above, in some cases or configurations, it may be desirable for a user to have very specific real-time or approximate real-time characteristics of the magnitude or level of the applied vacuum (generally, negative pressure gradient). The measurement device 54, 64, 76 may be configured to apply an algorithm to the signal from the vacuum sensor 50 (pressure sensor) that calculates an absolute value represented by dashed curve 844. The measurement device 54, 64, 76 may further apply an algorithm to determine the frequency (or pitch) of an audible sound varying within the human audible frequency range, e.g., within the human audible discrimination (hearing) range. For example, a modified signal curve 846 may be created that has the following general mathematical relationship to the signal from the vacuum sensor 50 represented by pressure curve 842:

[0135]

[0135] Sound frequency (Hz) = A + B × |(fluid pressure)| where A is the first constant, B is the second constant.

[0136]

[0136] In one particular example, a modified signal curve 846 can be created that has the following mathematical relationship to the signal from vacuum sensor 50 represented by pressure curve 842:

[0137]

[0137] Sound frequency (Hz) = 50 × |(fluid pressure (kPa))| where Hz is hertz (1 / second) kPa is the unit of kilopascal.

[0138]

[0138] The modified signal curve 846 may be configured with an algorithm such that the sound frequency appears to the user to follow the amount of vacuum or negative pressure being applied. In this embodiment, the pitch of the sound becomes "higher" as the vacuum or negative pressure increases (fluid pressure decreases) and "lower" as the vacuum or negative pressure decreases. Alternatively, the opposite may be chosen, such that the pitch of the sound becomes lower as the vacuum or negative pressure increases.

[0139] FIG. 9 illustrates a graph 860 of time (x-axis) and multiple variables (y-axis). A pressure curve 862 illustrates a vacuum or negative pressure being applied with a pressure drop 868 and a maintenance 870 of the vacuum or negative pressure with one or more pressure decreases and increases 872. These one or more pressure decreases and increases 872 (or vacuum or negative pressure increases and decreases) can, in some cases, represent a clot being aspirated through the aspiration lumen of the aspiration catheter. In some cases, a single decrease 873 of pressure (increase in vacuum or negative pressure) can occur. Similar to any one or more pressure decreases and increases 872, the single decrease in pressure 873 can, in some cases, be of extended duration, as shown in FIG. 9. In some cases or configurations, it may be desirable for a user to have very specific real-time or approximate real-time characteristics as these minor perturbations occur, as these may correspond to the catheter finding and aspirating a portion of the clot. Measurement devices 54, 64, 76 are configured to apply an algorithm that determines the frequency (or pitch) of audible sounds that vary within the human audible frequency range, e.g., within the human audible discrimination (hearing) range. For example, a modified signal curve 866 can be created that has the following general mathematical relationship with the signal from vacuum sensor 50 represented by pressure curve 862:

[0140] Sound frequency (Hz) = A + B × (fluid pressure) where A is the first constant, B is the second constant.

[0141]

[0141] In one particular example, a modified signal curve 866 can be created that has the following mathematical relationship to the signal from vacuum sensor 50 represented by pressure curve 862:

[0142] Sound frequency (Hz) = 40 × (fluid pressure (kPa)) where Hz is hertz (1 / second) kPa is the unit of kilopascal.

[0143]

[0143] Note that in this equation, the absolute value is not used, but the actual value of the fluid pressure. Alternatively, the absolute value (or negative value) may be used in some cases.

[0144] The modified signal curve 866 may be configured with an algorithm such that the sound maintains a steady pitch until the clot is aspirated through the catheter, at which point the pitch changes slightly but noticeably from the steady pitch. For example, in some embodiments, the pitch may change from about 20 Hz to about 2000 Hz, corresponding to a pressure change of about 1 kPa to about 2 kPa, or about 40 Hz to about 80 Hz.

[0145] In any example, signal modification can include any type of signal conditioning or modification, including, but not limited to, filtering, amplification, or isolation. The modified signal curves 806, 826, 846, and 866 are used to determine the output signal generated by the communication device 58, 68, or 74. As described above, if the output signal of the communication device 58, 68, or 74 is configured to be audible, the sound pressure level may be varied or the sound frequency may be varied. In some embodiments, the output signal of the communication device 58, 68, or 74 can vary both its sound pressure level and sound frequency. In one embodiment, the sound frequency varies continuously in proportion to the fluid pressure, but at one or more specific thresholds of fluid pressure, the sound pressure level may change very suddenly and noticeably. Therefore, communication occurs in two parts: a continuous real-time status indicator and an intermittent alert indicator (e.g., fault, danger, etc.). In some cases, the continuous real-time status indicator can represent a first continuous signal, and the alert indicator can represent a second alert signal. In other cases, continuous real-time status indicators and alert indicators may be combined and integrated into the same signal. In some embodiments, other psychoacoustic characteristics may be altered using a variable sound generator. In some embodiments, the spectral envelope may be altered. In some embodiments, the timbre may be altered to vary levels between bright and dark, warm and harsh, or different noise "colors" (pink, white, blue, black, etc.).

[0146] While audible outputs from communication devices 58, 68, 74 have been described in the examples of FIGS. 6-9, other communication signals, including visual or tactile signals, can also be used. Tactile signals can also include vibrational or heat-generating devices, either of which can be varied (as described) in relation to the measured fluid pressure. The amplitude of either frequency can be similarly varied in communication signals, including signals other than the audible signals already described. For example, the intensity of a light can be varied, or the frequency (e.g., color) of the light can be varied. The amplitude of the displacement of a vibrational device can be varied (or other techniques for varying vibration intensity), or the frequency of the vibration can be varied.

[0147] In some cases, a pseudo-continuous analog can be used in place of a true variable output. For example, instead of a single light with continuously varying intensity, an array of lights, such as an array containing multiple LEDs, can be used, with more LEDs illuminating as the level of vacuum or negative pressure increases and fewer LEDs illuminating as the level of vacuum or negative pressure decreases. The same can be done with an array containing multiple vibrating elements, with more elements beginning to vibrate as the fluid pressure increases or decreases depending on the application.

[0148] 6-9, the equations for sound pressure level or sound frequency that depend on fluid pressure as a variable can depend on the actual measured fluid pressure or the absolute value of the actual measured fluid pressure, but it is also possible to use the measured fluid pressure in an alternative manner. For example, a reference pressure 63 that is preset, predetermined, or determined or calculated by any other method (such as averaging) can be used, and the difference between the measured pressure and the reference pressure 63 can be used as a variable, where the variable is based on a particular dependency (e.g., a proportional relationship).

[0149]

[0149] Thus, the basic mathematical relationships used in conjunction with the proportional relationships described with respect to the embodiment of Figure 6 can be expressed as follows:

[0150] Sound pressure level (dB) = A + B × (1 / ΔP) where A is the first constant, B is a second constant, ΔP is the difference between the reference pressure and the measured fluid pressure.

[0151] Similarly, the basic mathematical relationships used in conjunction with the proportional relationships described with respect to the embodiment of FIG. 7 can be expressed as follows:

[0152]

[0152] Sound pressure level (dB) = A + B × |(ΔP)| where A is the first constant, B is a second constant, ΔP is the difference between the reference pressure and the measured fluid pressure.

[0153] Similarly, the basic mathematical relationships used in the proportionality described with respect to the embodiment of FIG. 8 can be expressed as follows:

[0154]

[0154] Sound frequency (Hz)=A+B×|(ΔP)| where A is the first constant, B is a second constant, ΔP is the difference between the reference pressure and the measured fluid pressure.

[0155] Similarly, the basic mathematical relationships used in the proportionality described with respect to the embodiment of FIG. 9 can be expressed as follows:

[0156]

[0156] Sound frequency (Hz)=A+B×(ΔP) where A is the first constant, B is a second constant, ΔP is the difference between the reference pressure and the measured fluid pressure.

[0157] A pressure transducer 912 of a suction monitoring system 900 for connection to a suction system including a suction catheter 4 is shown in FIG. 10. The pressure transducer 912 includes a housing 40, a first port 44, a second port 46, and a cable 902 for transmitting signals. The cable 902 includes an interface 904 or plug configured to connect to a port 906 of a console 908 of the suction monitoring system 900. The housing 40 of the pressure transducer 912 includes a cavity 42 extending between the first port 44 and the second port 46. The console 908 is powered by a power module 972 connected to the console 908 and may include an AC or DC power source. The console 908 may include a measurement device 964, a memory module 966, and a communication device 968, which may be connected to each other as described in the previous embodiments and configured such that the communication device 968 can generate a signal 970, which may be an alert signal, a continuous signal, a composite signal, or other type of signal. The console 908 may also include wired or wireless connections to other interfaces or displays found at the healthcare site, such as a monitor 931. In some embodiments, the monitor 931 may be a monitor that also displays fluoroscopic or angiographic images, electrocardiogram or blood pressure graphics, or other information. The monitor 931 may have a portion that maintains the status of aspiration. For example, it may read "thrombus being aspirated" or "no thrombus detected." The pressure transducer 912 (housing 40, ports 44, 46, cable 902, interface 904) may be sold sterile and may be configured to output a signal that is received by the console 908, such as the measurement device 964 of the console 908. The pressure transducer 912 may have its own internal power source (e.g., battery 52 in FIG. 2A ) or may be powered by a connection to the console 908 or by a connection to the aspiration catheter 4 or dilation tube 10. In some embodiments, the console 908 may be configured to identify and / or recognize the pressure transducer 912, for example, to recognize a particular model of the pressure transducer 912.In some embodiments, console 908 may be configured to measure the resistance between two electrical contacts in pressure transducer 912 to identify the type (e.g., model) of the pressure transducer. In some embodiments, console 908 may be configured to read an RFID chip on pressure transducer 912. Console 908 may also be configured to connect to two or more different models of pressure transducers. Ports 906 may comprise at least one port that may include two or more ports, and each port may be configured to allow connection of a different model of pressure transducer.

[0158] The suction system 1000 of FIG. 11 includes a suction console 1001 having a connector 1002 or hub (e.g., a male luer) for connecting to a suction catheter 4, for example, to the connector 22 (e.g., a female luer) of the suction catheter 4. The suction console 1001 is powered by a power module 972 connected to the suction console 1001 and which may include an AC or DC power source. The suction console 1001 may include a canister 1006 for collecting aspirated material and may include a vacuum pump 1004 for generating a vacuum to generate suction. A tube 1008 may be connected between the canister 1006 and the connector 1002. In some embodiments, the canister 1006 is removable or replaceable. The suction monitoring system 900 includes a pressure sensor 1010 (e.g., a vacuum sensor) in fluid communication with the tube 1008. The tube 1008 may alternatively comprise a lumen formed within a manufactured part. Aspiration monitoring system 900 is shown in more detail in FIG. 12 and can include some or all of the features described in connection with FIG. 10. Aspiration console 1001 can also include wired or wireless connections to other interfaces or displays found at a healthcare site, such as monitor 931. In some embodiments, monitor 931 can be a monitor that also displays fluoroscopic or angiographic images, or electrocardiogram or blood pressure graphics or other information. Combining all communications related to the procedure on a single monitor or at a single monitor location allows the user to achieve uninterrupted focus, freeing them to concentrate on the safe advancement and placement of the aspiration catheter near the clot.

[0159] 13 includes an aspiration / infusion console 1101 having a first connector 1016 or hub (e.g., a male luer) for connecting to the infusion lumen 1020 of a forced suction catheter 1013 and a second connector 1012 or hub (e.g., a male luer) for connecting to the aspiration lumen 1018 of the forced suction catheter 1013. The first connector 1016 at the proximal end 14 of the forced suction catheter 1013 is configured to connect to a connector 1024 (e.g., a female luer) of a y-connector 1022, and the second connector 1012 is configured to connect to a connector 1026 of the y-connector 1022. The aspiration / infusion console 1101 is powered by a power module 972 connected to the aspiration console 1101 and which may include an AC or DC power source. The suction console 1101 can include a canister 1106 for collecting aspirated material and can include a vacuum pump 1104 for generating a vacuum or negative pressure to generate suction. Tube 1108 can be connected between the canister 1106 and the connector 1012. The positive pressure pump 1014 is connected to a fluid source 1032 (e.g., a saline bag) and is configured to infuse infusion fluid at high pressure through the connector 1016. The suction monitoring system 900 includes a pressure sensor 1110 (e.g., a vacuum sensor) in fluid communication with the tubing 1108. Alternatively, the tubing 1108 can include a lumen formed within a manufactured part. The suction monitoring system 900 is shown in further detail in FIG. 14 and can include some or all of the features described in connection with FIG. 10. At the distal end 16 of the forced aspiration catheter 1013, the infusion lumen 1020 terminates in an orifice 1028 and is configured to generate a jet 1030 formed from the high pressure infusate exiting the orifice 1028. The jet 1030 creates a suction force at the distal end 16 of the forced aspiration catheter 1013 that enters the aspiration lumen 1018 and forces material (e.g., blood clots) into the aspiration lumen 1018 and into the canister 1106. The aspiration / infusion console 1101 may also include wired or wireless connections to other interfaces or displays found at the healthcare site, such as a monitor 931.In some embodiments, monitor 931 may be a monitor that also displays fluoroscopic or angiographic images, or may be a monitor that also displays electrocardiogram or blood pressure graphics or other information.

[0160] In another embodiment, the forced suction catheter 1013 of the suction catheter 4 may have an additional lumen or guide channel for placement of an additional device or tool. In some embodiments, the guidewire lumen 26 can be used as this additional lumen and can extend the entire length or most of the length of the catheter so that the lumen is accessible from the proximal end 14. The additional device or tool can include a laser fiber, a machine screw, a vibrating wire, or various other modalities for disrupting thrombus or other material.

[0161] In any of the presented embodiments, the system may be configured so that most or all of the components are supplied together. For example, a catheter and a suction monitoring system may be permanently attached to one another. In some embodiments, the aspiration catheter and / or aspiration monitoring system may include configurations that intentionally make them difficult to reprocess (e.g., clean or resterilize), thereby preventing uses that may not be recommended or warranted, which may risk patient infection and / or device malfunction. For example, the sensor or parts adjacent to the sensor may be intentionally difficult to access or clean. Alternatively, one or more batteries may be inaccessible or inaccessible.

[0162] In some embodiments, it may be desirable to have other descriptive warnings that can be tied to the pressure measurement or to the pressure measurement in combination with another measured characteristic. For example, if a sensor (such as an accelerometer or temperature sensor) in the aspiration catheter is used to detect catheter movement, changes in this sensor can be tied to the pressure sensor. In this way, a catheter that engages a clot at its tip and is moved (e.g., begins to be withdrawn from the patient) may trigger a warning: "Warning: Do not move the catheter. Risk of thromboembolism."

[0163] FIG. 15 is a schematic diagram illustrating an auxiliary aspiration system 510. The aspiration system 510 includes a remote handpiece 512 with a fluid pump 526 and an operator control interface 506. In one possible embodiment, the system 510 is a single-use, disposable unit. The aspiration system 510 also includes an extension tube 514 with a fluid irrigation lumen 502 and an aspiration lumen 504, allowing for independent operation of the catheter 516 without the need for repositioning the handpiece 512 during a procedure performed with the aspiration system 510. The extension tube 514 can also function as a pressure accumulator. The high-pressure fluid flow from the pump 526, which can include a positive displacement pump, generates pulses with each stroke of the pump 526, generating a sinusoidal pressure map with distinct variations between the peaks and valleys of each sine wave. The extension tube 514, in sync with the pump 526, expands and contracts in unison with each pump pulse, reducing the pressure changes caused by the pump pulses and creating a smoother or smoother fluid flow at the tip of the catheter 516. Any tubing with suitable compliance characteristics can be used. The dilation tube 514 may be permanently attached to the pump 526 or may be attached to the pump 526 by a connector 544. The connector 544 is configured to ensure that the dilation tube 514 cannot be accidentally attached to the pump 526.

[0164] An interface connector 518 couples the dilation tube 514 and the catheter 516 together. In one possible embodiment, the interface connector 518 can include a filter assembly 508 between the high-pressure fluid infusion lumen 502 of the dilation tube 514 and the high-pressure infusion lumen 536 of the catheter 516 ( FIG. 17 ). The catheter 516 and dilation tube 514 can be permanently coupled by the interface connector 518. Alternatively, the interface connector 518 can include a standardized connection so that a selected catheter 516 can be attached to the dilation tube 514. In some embodiments, the filter assembly 508 can be removably connected to the dilation tube 514 by a quick-disconnect connection. The pressure transducer of the embodiments of the aspiration monitoring system presented herein can be located at a point along the aspiration lumen 504 or at any dilation of the aspiration lumen 504.

[0165] Attached to the handpiece 512 are a fluid source 520 and a vacuum source 522. A standard hospital saline bag can be used as the fluid source 520; such a bag is readily available to the physician and provides the volume necessary to perform the procedure. A vacuum bottle may provide the vacuum source 522, which may be provided by a syringe, vacuum pump, or other suitable vacuum source. The filter assembly 508 serves to filter particulates from the fluid source 520 to avoid clogging of the high-pressure infusion lumen 536 and orifice 542 (FIG. 17). As described herein, the distal section of the high-pressure infusion lumen 536 can be configured with a small inner diameter, and the filter assembly 508 serves to protect its continuous function. By incorporating one of various catheters 516 into the auxiliary aspiration system 510, for example, with various lumen configurations (inner diameter, length, etc.), various aspiration qualities (aspiration rate, jet velocity, jet pressure) can be applied to one or more patients. These suction qualities can be further achieved by adjusting the pump 526 to change the pump characteristics (flow rate, pump pressure). In some embodiments, the catheter 516 may be used manually, for example, without the pump 526, and controlled by manual injection. Manual use of the catheter 516 may be appropriate for certain patient conditions and may help reduce the cost of the procedure.

[0166] In one possible embodiment, the catheter 516 can have varying stiffness, being stronger at the proximal end and more flexible at the distal end. The varying stiffness of the catheter 516 can be achieved with a single tube with no radial bond between two adjacent pieces of tube. For example, the shaft of the catheter 516 can be made from a single length of metal tubing, with the length of the tubing helically cut to provide shaft flexibility. The varying stiffness can be created by varying the pitch of the helical cut along different lengths of the metal tubing. For example, the pitch of the helical cut can be smaller (the turns of the helical cut can be closer together) at the distal end of the device to provide greater flexibility. Conversely, the pitch of the helical cut can be larger (the turns of the helical cut can be farther apart) at the proximal end to increase stiffness. A single jacket covers the length of the metal tubing, providing a vacuum-tight catheter shaft. Other features of the catheter 516 are described below with reference to FIG. 17.

[0167] FIG. 16 is a schematic diagram showing the proximal portion of the handpiece 512 and auxiliary catheter aspiration system 510 in more detail. The handpiece 512 includes a control box 524 in which the power and control systems are located. The pump 526 may be a motor-driven positive displacement pump with a constant output. This pump displacement relative to the catheter volume, coupled with the position of the orifice 542 (outlet) of the catheter high-pressure lumen 536 within the aspiration lumen 538 (FIG. 17), ensures that all pressurized fluid is evacuated by the aspiration lumen, thereby ensuring that no energy is transferred from the saline pump to the patient. A master button 528 is mechanically connected to the master valve 530. When preparing the device for use, it is preferable to evacuate all air from the pressurized fluid system to reduce the possibility of air embolism. By pressing the master button 528, the user connects the fluid source 520 to the vacuum source 522 via the pump 526. This forcefully draws fluid (e.g., 0.9% NaCl solution, i.e., "saline," or heparinized saline, not "normal saline") through the entire pump system, removing all air and actively priming the system for safe operation. A pressure / vacuum valve 532 is used to turn the vacuum or negative pressure on and off in synchronization with the fluid pressure system. One possible valve 532 is a ported one-way valve. Such a valve is preferable to a manual or electronic valve system because it operates as a tamper-resistant safety feature by mechanically and automatically combining the operation of the two primary systems. Having a pressure / vacuum valve 532 eliminates the possibility of turning on the vacuum or negative pressure without operating the fluid system.

[0168] The operator control interface 506 may include an electronic control board 550 powered by a power system 548 (such as a battery or power line) and operable by a user using one or more switches 552 and one or more indicator lights 554. The control board 550 also monitors and controls several device safety functions, including overpressure and air bubble detection and vacuum or negative pressure charging. A pressure sensor 564 monitors pressure and senses the presence of air bubbles. Alternatively, air bubbles can be detected using an optical device 566. In one possible embodiment, pump pressure is proportional to the current required to generate that pressure. Thus, if the current required by the pump 526 exceeds a preset limit, the control board disables the pump by cutting power to the pump. Air bubble detection can also be monitored by monitoring the current required to drive the pump at a particular moment. In order for the positive displacement pump 526 to reach high fluid pressures, little or no air (which is highly compressible) should be present within the pump 526 or the connection system (including the catheter 516 and dilation tube 514). The fluid volume is small enough that air in the system does not create pressure at the pump head. The control board monitors the pump current for a sudden downward change that could indicate air has entered the system. If the rate of decline is faster than a preset limit, the control board disconnects power to the pump, rendering it inoperable until the problem is corrected. Similarly, blockages in the high-pressure lumen 536, which may be caused by tissue or fibrous thrombus intrusion or solid emboli, can be detected by monitoring the current through the pump 526. In normal use, the current flux of the pump 526 is relatively high. For example, the pump may be configured so that the current fluctuates by more than 200 milliamps during normal operation; air is identified when the current flux drops below 200 milliamps, causing the system to shut down. Alternatively, a current flux in the range of, for example, 50 milliamps to 75 milliamps can be used to identify air in the system.Additionally, an increase in current or current flux can indicate the presence of a clot or thrombus within high pressure lumen 536. For example, a current of greater than 600 milliamps can indicate a thrombus partially or completely blocking high pressure lumen 536, or aspiration lumen 538.

[0169] The vacuum line 556 connected to the vacuum source 522 can be connected to a negative pressure sensor 558. If the vacuum or negative pressure of the vacuum source 522 is low or if a leak is detected in the vacuum line 556, the control board 550 disables the pump 526 until the problem is corrected. The negative pressure sensor 558 can be part of a safety circuit 560 that prevents the pump 526 from operating if no vacuum is present. A comprehensive safety system 562, including the safety circuit 560, pressure sensor 564 and / or optical device 566, and negative pressure sensor 558, thereby requires both pump pressure and vacuum or negative pressure for the system to operate. If a problem exists (e.g., if there is an unacceptably low pump pressure or no significant vacuum or negative pressure), the control board 550 will not allow the user to operate the aspiration system 510 until all problems are corrected. This prevents air from being infused into the patient and ensures that the aspiration system 510 does not operate under incorrect parameters.

[0170] FIG. 17 is a schematic diagram of the distal end portion 568 of the auxiliary catheter aspiration system 510, showing the catheter 516 in more detail. The catheter 516 is a single-operator exchange catheter and includes a short guidewire lumen 534 attached to the distal end of the device. The guidewire lumen 534 may be about 1 cm to about 30 cm in length, about 5 cm to about 25 cm in length, about 5 cm to about 20 cm in length, or about 13.5 cm in length. The aspiration lumen 538 includes a distal opening 540 that allows vacuum or negative pressure (e.g., from the vacuum source 522) to draw thrombus material into the aspiration lumen 538. The high-pressure lumen 536 includes a distal orifice 542 that is set a set amount proximal to the distal opening 540. For example, the distal orifice 42 can be set proximal to the distal opening 540 by approximately 0.020 inches, or by 0.020 inches ±0.003 inches, or another desired amount. The orifice 542 is configured to spray across the aspiration lumen to macerate and / or dilute thrombus material for transport to the vacuum source 522, for example, by reducing the effective viscosity of the thrombus material. Axial placement of the fluid orifice 542 ensures that the spray pattern interaction with the opposing lumen wall creates a spray mist and not a swirl pattern that can push embolic material out of the distal opening 540. The system may be configured so that the irrigation fluid exits the pump at a pressure of approximately 500 psi to approximately 1500 psi. In some embodiments, after pressure head loss along high-pressure lumen 536, irrigation fluid exits orifice 542 at a pressure of about 600 psi to about 1200 psi, or about 650 psi to about 850 psi. In some cases, it is possible (and desirable) to use auxiliary catheter aspiration system 510 without operating pump 526, thus allowing catheter 516 to be used while manually injecting saline via a syringe, for example.Alternatively, in some cases, auxiliary catheter aspiration system 510 can be used without pump 526 attached, while manually injecting saline using a syringe through high pressure lumen 536. In the event of a clog, for example, the syringe can be removed and pump 526 attached and started to unclog high pressure lumen 536.

[0171] When normal blood flow is achieved after the release of an atherosclerotic lesion and / or thrombosis, there is occasionally a risk of reperfusion injury. This may be particularly important after thrombectomy of a vessel supplying the brain for the treatment of embolic stroke or after thrombectomy of a coronary artery supplying the myocardium. This also includes the case of myocardial revascularization after coronary intervention (e.g., thrombectomy). Reperfusion injury and microvascular damage may be mechanisms that limit significant or complete recovery of revascularized myocardium. Sudden reperfusion of a previously unperfused portion of myocardium can trigger a series of physiological processes that paralyze or damage the myocardium. Distal coronary emboli, such as small thrombus segments, platelets, and atheromas, may also be involved. Controlled preconditioning of at-risk myocardium has been proposed to limit the effects of reperfusion injury and microvascular damage. The embodiments of the thrombectomy systems 100, 300 presented herein can be combined with additional features intended to enable flow control to limit the potential risks of reperfusion after thrombectomy.

[0172] FIG. 18 shows a multi-purpose system 1200 including a multi-purpose catheter 1202 having an injection port 1204 and a suction port 1206. The injection port 1204 and the suction port 1206 can each include a Luer connector, such as a female Luer lock connector. A tubing set 1208 and a pressure sensor 1210 are connected in-line with a vacuum source 1212. A cable 1214 carries the signal from the pressure sensor 1210 to a suction monitoring system 1216 (FIG. 19) and connects to the suction monitoring system 1216 via an interface 1218 or plug configured to connect to a port 1220 of a console 1222 of the suction monitoring system 1216. The devices and methods described herein can be used to monitor suction using the suction monitoring system 1216. In one method of use, a syringe 1224 (FIG. 18) can be used to manually inject fluid through the injection port 1204 and the infusion lumen 1225 (e.g., a high-pressure lumen) of the multi-purpose catheter 1202. Syringe 1224 may have an injectable volume of about 5 ml or less, or in some embodiments, about 1 ml or less. Infusion lumen 1225, in some embodiments, may be configured to inject saline at relatively high pressure, or at either high or low pressure. When valve 1226 (e.g., a stopcock) is closed to prevent vacuum source 1212 from applying a reduced pressure or negative pressure to aspiration lumen 1227 via aspiration port 1206, infusion through infusion lumen 1225 can deliver infusate to a site within a blood vessel (at the distal end of multipurpose catheter 1202) near the distal outlet of infusion lumen 1225. Alternatively, when vacuum source 1212 is detached from or simply disconnected from aspiration lumen 1227, infusion through infusion lumen 1225 delivers infusate to a site within a blood vessel near the distal outlet of infusion lumen 1225. Any of these techniques can be used to administer drugs to the vessel wall, or to the atherosclerotic plaque, or to the thrombus. In some cases, clot-busting drugs (tissue plasminogen activator (tPA), thrombokinase, urokinase, thrombin, plasmin) are injected into the clot or thrombus and allowed to act over a period of time.One goal is to soften the clot over time. Solubilizing agents, glycoprotein inhibitors (GPIs), vasodilators, and other medications can be used to dilate blood vessels or treat disease in the area. Controlled, precise, localized delivery allows for effective use of the medication, with the desired amount delivered to the tissue being treated with minimal spillage or waste. This efficiency reduces procedural costs, as many of these medications are very expensive. Due to the precise diameter of the infusion lumen 1225 and its known length, the infusion lumen 1225 contains a known volume or dead space. This further allows for a known, controlled, and precise infusion of medication. A typical infusion lumen 1225 is 150 cm long and has an inner diameter of 0.038 cm (0.015 inches), thus resulting in a total volume of only 0.17 ml. The volume of the infusion lumen 1225 can be varied by controlling the inner diameter of the infusion lumen 1225 and / or the length of the infusion lumen 1225. For example, the volume of the infusion lumen 1225 may be between about 0.08 ml and about 0.26 ml, or between about 0.14 ml and about 0.20 ml. Injecting through the infusion lumen 1225 with a small-bore syringe (e.g., 1 ml) or a precision pump allows for precise measurement of the delivered agent. However, when the valve 1226 or stopcock is opened, connecting the vacuum source 1212 to the aspiration port 1206 and applying a vacuum or negative pressure to the aspiration lumen 1227, forced aspiration is initiated, as described herein. As discussed above, the infusion lumen 1225 can be used in either a closed system (aspiration) or an open system (infusion of infusate). Because it is not always known at the beginning of a procedure what different actions will be required, the use of the multipurpose catheter 1202 and multipurpose system 1200 can eliminate the need for multiple catheters (e.g., a microcatheter and a single-function aspiration catheter).

[0173] 20-24 show a multi-purpose system 1240 with a multi-purpose catheter 1242 having an infusion port 1244 and a suction port 1246. Chilled saline can be infused from a saline bag 1248 (FIG. 23) through a tubing set 1250 attached to the saline bag 1248 via a spike 1252. A pump 1254 (FIG. 24), which may include a positive displacement pump such as a piston pump, includes an interface 1256 for attaching a cassette 1258 (FIG. 20). In some embodiments, the pump 1254 has a moving part that connects to a moving piston 1255 in the cassette 1258 to infuse a controlled amount of fluid. As described in connection with the multipurpose system 1200 of FIG. 18 , infusion can serve as either a closed system (aspiration) or an open system (infusion of infusate), depending on whether the valve 1260 connecting the vacuum source 1262 to the aspiration port 1246 via the extension tube 1264 is open or closed, or simply whether the vacuum source 1262 is attached or not. The pressure sensor 1266 is in communication with the interior of the extension tube 1264, but may also be in communication with the interior of other portions of the fluid path. A cable 1268 carries the signal from the pressure sensor 1266 to the aspiration monitoring system 1270 ( FIG. 22 ) and connects to the aspiration monitoring system 1270 via an interface 1272 or plug configured to connect to a port 1274 on the aspiration monitoring system's 1270 console 1276. The utility of the multipurpose systems 1200, 1240 in multiple modes is facilitated by a sterile fluid path combined with precise volume control (either by a miniature syringe 1224 or a precision pump 1254). Additionally, the suction monitoring systems 1216, 1270 allow for real-time feedback to the user, further facilitating controlled delivery and / or suction.

[0174] The multipurpose system 1200, 1240 optimizes interventional procedures, such as percutaneous coronary intervention (PCI), for simplicity, case flow, and cost. Injecting a drug into a coronary artery results in clot aspiration by placing a high concentration of drug directly at the lesion site, which may typically be more distal (e.g., more superselective) than the location accessible by the tip of a guide catheter. This minimizes the amount of drug used. Limiting the amount of a particular drug can minimize or eliminate systemic complications (e.g., bleeding). Drugs can be applied directly to the thrombus itself, for example, to soften or dissociate the thrombus. Maceration of the thrombus with a saline jet 1278 ( FIG. 21 ) injected through the infusion lumen 1257 of the multipurpose catheter 1242 keeps the catheter aspiration lumen 1259 constantly patent without interruption, allowing for a standardized catheter advancement technique, for example, by slowly moving the catheter from a proximal to a distal position within the vessel (relative to the thrombus). Maceration also dilutes the proximally flowing aspirate for optimal aspiration efficiency. In certain circumstances, suction can be applied until normal blood flow is restored (at least to a significant level), after which the vacuum source 1262 can be closed via valve 1260, and chilled infusate can be infused into the vessel. This resulting selective cooling of the area helps reduce reperfusion injury by potentially slowing ischemic cellular metabolism. The chilled infusate infusion can be used any time after aspiration and before stent insertion without removing the aspiration device or advancing a new infusion device. With the multipurpose catheter 1202, 1242 already in place, this important procedure can begin immediately. Having all of this functionality in one catheter also saves the user money.

[0175] In aspiration mode, the aspiration monitoring system 1216, 1270 can constantly monitor the proper functioning of the aspiration circuit. The user knows when a critical event occurs, when an alert is transmitted, or when the system (e.g., motor) shuts down, requiring their attention. This knowledge helps the user avoid stabbing the catheter too far and potentially causing distal embolism. In infusion / infusate cooling mode, the pump 1254 pumps at a predetermined constant volume or rate to deliver a constant-temperature cooling infusate. Core body temperature feedback (e.g., via a rectal, esophageal, ear, or other temperature probe) can be used to indicate to the system that further cooling should be stopped. For example, a core body temperature below 35°C or below 34°C. Feedback of a temperature below a threshold can be used to stop the pump and / or send a warning. A precise and direct infusate path to the catheter tip and / or ischemic area provides focused cooling and minimal systemic hypothermia. Bypassing the aspiration lumen (e.g., with valve 1260 closed), there is less chance of unintended emboli being refluxed into the vessel and therefore sent downstream into a dangerous area, thereby eliminating the need to replace the device after flow is restored.

[0176] Optionally, in the infusion mode, infusate is injected into the fluid infusion lumens 1225, 1257 at a relatively low pressure. Optionally, maceration is performed at a relatively high pressure. Optionally, the multipurpose system 1240 can be used without the pump 1254 attached, with saline injection performed manually using a syringe attached to the infusion port 1244. In the event of a clog, for example, the syringe can be removed and the pump 1254 attached and initiated to unclog the infusion lumen 1257. In an exemplary procedure, a user places a catheter similar to the multipurpose catheter 1202 of FIG. 18 or the multipurpose catheter 1242 of FIGS. 20-21 into the vasculature. Initially, the user can choose not to have the pump 1254 or the syringe 1224 (FIG. 18) attached to the multipurpose catheter 1202, 1242. The user can then begin suction through the suction lumens 1227, 1259 via the vacuum sources 1212, 1262, thus utilizing the multi-purpose catheters 1202, 1242 as simple (vacuum or negative pressure only) suction catheters. If the user determines that additional positive pressure injection of saline and / or medication is needed, for example to overcome a blockage, overcome slow suction, or increase maceration or dilution of the clot, the user can attach the pump 1254 or syringe 1224 to the injection port 1204, 1244 and begin injecting the saline and / or medication.

[0177] In one embodiment, the aspiration system includes an elongated catheter having a proximal end and a distal end, the catheter including: an aspiration lumen having a proximal end and a distal end; a high-pressure infusion lumen having a proximal end and a distal end and extending from the proximal end of the catheter to a location adjacent the distal end of the aspiration lumen; and at least one orifice at or near the distal end of the high-pressure infusion lumen configured to allow high-pressure liquid infused through the high-pressure infusion lumen to be released into the aspiration lumen, the proximal end of the high-pressure infusion lumen being configured to be repeatedly connectable and disconnectable to one or more infusion modules. In some embodiments, the one or more infusion modules include a first infusion module and a second infusion module. In some embodiments, the first infusion module includes a pump and the second infusion module includes a syringe. In some embodiments, the second infusion module includes a syringe having a volume of about 5 ml or less. In some embodiments, the second infusion module includes a syringe having a volume of about 1 ml or less. In some embodiments, the second infusion module includes a syringe containing a medication.

[0178] 25-33 illustrate several different embodiments of a device having a pressure sensor 1300 configured to function as a component in a suction monitoring system that shares some or all of the functionality of any one of the suction monitoring systems 48, 62, 78, 900, 1216, and 1270 presented herein. FIG. 25 illustrates a suction catheter 1302 having a distal end 1304 and a proximal end 1306, the proximal end 1306 including a female luer connector 1308. The pressure sensor 1300 is in fluid communication (e.g., fluidly connected) with the lumen of the suction catheter 1302. FIG. 26 illustrates a tubing set 1310 having a male luer 1312 and a female luer 1314, an extension tube 1316, and a stopcock 1318. The pressure sensor 1300 is in fluid communication with the lumen of the extension tube 1316. FIG. 27 shows a stopcock 1320 having a male luer 1322, a female luer 1324, and a valve 1326, where the valve 1326 is disposed proximal to a pressure sensor 1300. The pressure sensor 1300 is in fluid communication with the interior cavity of the stopcock 1320. FIG. 28 shows a stopcock 1328 having a male luer 1330, a female luer 1332, and a valve 1334, where the valve 1334 is disposed distal to the pressure sensor 1300. The pressure sensor 1300 is in fluid communication with the interior cavity of the stopcock 1328. FIG. 29 shows a syringe 1336 having a male luer 1342, a barrel 1338, and a plunger 1340. The syringe 1336, such as a VacLok® syringe, can include a locking mechanism 1344 that allows the plunger 1340 to be locked relative to the barrel 1338. The pressure sensor 1300 is disposed distally of the barrel 1338 and is in fluid communication with the interior cavity of the barrel 1338 .

[0179] FIG. 30 shows a syringe 1346 having a male luer 1352 (i.e., luer connector, luer lock), a barrel 1348, and a plunger 1350. The syringe 1346 may include a locking mechanism 1344. The pressure sensor 1300 is in fluid communication with the interior cavity of the barrel 1348 and may be connected directly to either the barrel 1348 or the male luer 1352, or directly to the hollow transition 1351 therebetween. FIG. 31 shows an aspiration system 1354 with a syringe 1356 having a male luer 1357, a barrel 1358, and a plunger 1360. The syringe 1356 may include a locking mechanism 1344. The aspiration system 1354 also includes a connector assembly 1361 including a male luer 1362, a valve 1364, and a female luer 1365 (connected below the male luer 1357 in FIG. 31). The pressure sensor 1300 is in fluid communication with the internal lumen or cavity between the barrel 1358 of the syringe 1356 and the male luer 1362 of the connector assembly 1361. FIG. 32 shows an aspiration system 1366 including a syringe 1368 having a male luer 1369, a barrel 1370, and a plunger 1372. The syringe 1368 may include a locking mechanism 1344. The aspiration system 1366 also includes a connector assembly 1373 including a male luer 1374, a valve 1376, and a female luer 1377 (connected below the male luer 1369 in FIG. 32). The pressure sensor 1300 is in fluid communication with the internal lumen or cavity between the barrel 1370 of the syringe 1368 and the male luer 1374 of the connector assembly 1373. 33 shows an aspiration system 1378 including a syringe 1380 having a male luer 1382, a barrel 1384, and a plunger 1386. The syringe 1380 may include a locking mechanism 1344. The aspiration system 1378 further includes a tubing set 1388 having a male luer 1390 and a female luer 1392. A valve 1394 is positioned either proximal or distal to the pressure sensor 1300. An extension tube 1396 may be utilized to connect one or more components of the tubing set 1388, although in some cases the components may be directly connected.The pressure sensor 1300 is in fluid communication with the internal lumen of the tubing set 1388. The stopcock or valve in any of these embodiments may be a one-way stopcock, a three-way stopcock, a one-way valve, or a three-way valve. Other embodiments may exist that combine one or more elements of each of the embodiments presented herein. These embodiments are also within the scope of this disclosure. In any of the embodiments in which a male luer is used, it can be replaced with a female luer or another liquid-tight connector. In any of the embodiments in which a female luer is used, it can be replaced with a male luer or another liquid-tight connector. In this manner, either of the connector assemblies 1361, 1373 may be connected to the syringes 1356, 1368 in an inverse manner, i.e., the distal end becomes the proximal end and thus connected to the syringes 1356, 1368, and the proximal end can become the distal end.

[0180] 34 illustrates a thrombectomy system 300 incorporating high-pressure injection of a fluid, such as sterile saline, to macerate and aspirate the thrombus 104. The guide catheter 108 has an inner lumen 110 extending between a proximal end 144 and a distal end 120. As described with respect to the previous embodiment, a y-connector 148 connected to the proximal end 144 of the guide catheter 108 includes a proximal seal 150 and a side port 152 and is configured to connect the inner lumen 110 of the guide catheter 108 to a vacuum source 146. As described with respect to the previous embodiment, the thrombectomy catheter 306 includes a distal tube 314 having a distal end 316 and a proximal end 318, the proximal end 318 incorporating one or more sealing members 324 for sealing an annulus 342 between the guide catheter 108 and the distal tube 314. The distal tube 314 has an aspiration lumen 330. A support / supply tube 368 having a lumen 370 is connected to the distal tube 314. The support / supply tube 368 serves as a support member for pushing and pulling the thrombectomy catheter 306, but also serves as a conduit (via the lumen 370) for high-pressure saline, which is pumped from the proximal end 372 to the distal end 374. The saline is supplied from a saline source 376 (e.g., a saline bag, bottle), pressurized by a pump 378, and passed through a supply tube 380 and a luer connector 382 connected to a luer hub 384 connected to the support / supply tube 368. In some embodiments, the support / supply tube 368 comprises a hypotube. In some embodiments, the support / supply tube 368 comprises stainless steel or nitinol. The distal end 316 of the distal tube 314 may include a skive 358 to aid in the trackability of the distal tube 314 through the patient's vasculature. In some embodiments, the inner diameter of the aspiration lumen 330 of the distal tube 314 may be approximately 1 French size smaller than the inner diameter of the inner lumen 110 of the guide catheter 108. In some embodiments, the thrombectomy catheter 306 includes a support tube or support shaft to replace the support / delivery tube, which does not include the lumen 370.Thus, aspiration is controlled solely by suction of the inner lumen 110 of the guide catheter 108 in combination with the aspiration lumen 330 of the distal tube 314, and no high-pressure fluid injection is required. Other embodiments of the thrombectomy catheter 306 are described in U.S. Patent No. 9,433,427, entitled "System and Method for the Management of Thrombosis," issued September 6, 2016.

[0181] FIG. 35 shows the proximal end of a guide catheter 108 used with an aspiration catheter, such as the thrombectomy catheter 306 of FIG. 34. A hemostatic valve 389 in the y-connector 390 seals off both the support / supply tube 391 and the guidewire 28. The hemostatic valve 389 (e.g., Touhy-Borst, longitudinally spring-loaded seal, etc.) must be adjusted to allow movement (translation, rotation) of the catheter and / or guidewire 28, but must prevent air from being drawn into the lumen during aspiration. Due to the continuous adjustments often required of the hemostatic valve 389, e.g., to aid in catheter and / or guidewire movement, the hemostatic valve 389 can create wide variability in the amount of air that can leak. Leakage (e.g., at location 393) can be rapid and may not be noticeable to the user. The pressure sensor 394 used in conjunction with any of the aspiration monitoring systems described herein allows a user to immediately know if the seal of the hemostasis valve 389 of the y-connector 390 is not sealing properly. Furthermore, leaks between the distal luer 388 of the y-connector 390 and the luer hub 386 of the guide catheter 108 can be detected by the aspiration monitoring system. Furthermore, leaks between the luer 392 of the pressure sensor 394 and the side port 395 of the y-connector 390, or between the luer connector 396 of the extension tube 387 and the luer fitting 397 of the pressure sensor 394, can be detected by the aspiration monitoring system. The aspiration monitoring system may be integral with or configured to be attachable to any component of the aspiration circuit (e.g., aspiration catheter, syringe / vacuum source), or may be connected in series (at any point) between these components. In some embodiments, the aspiration monitoring system may include a flow sensor or pressure sensor or detector that is in series or parallel with a component or configured to be placed in series or parallel with a component. In any of these configurations, the suction monitoring system of the embodiments disclosed herein can assess several different leak locations.The suction monitoring system may be configured to detect changes, relative changes, absolute changes, thresholds, absolute values, the presence or absence of pressure and / or flow. The suction monitoring system may be configured to determine the operational status of a system including a catheter having an aspiration lumen. In some cases, the suction monitoring system may be configured to provide information about the operation of the system that cannot be discerned from typical cues such as angiography, sound, sensation, or other visual, auditory, tactile, or other feedback from the system itself.

[0182] 36 shows an aspiration system 1400 comprising an aspiration catheter 1402 with an elongate shaft 1401 including an aspiration lumen 1404 having an open distal end 1405 and a proximal end 1406, configured to connect to a peristaltic pump 1408. The peristaltic pump 1408 may be a roller pump having a base 1426, a pressure shoe 1428 carried by the base 1426, and a rotatable head 1430 rotatably connected to the base 1426 and carrying two or more rollers 1432a-d. The rollers 1432a-d are arranged around a periphery 1434 of the rotatable head 1430. The rotatable head 1430 is configured to be rotatable in at least a first rotational direction 1436 relative to a rotation axis 1499. The rotatable head 1430 may be rotated by a motor 1497, either directly or in conjunction with a gear train 1495. The peristaltic pump 1408 may be battery-powered, and the battery may be rechargeable wired or wirelessly. The peristaltic pump 1408 may alternatively or additionally be powered by a power cord 1493 configured to connect to a power source. An extension tube 1438 having a distal end 1440 and a proximal end 1442 and a lumen 1444 extending therethrough is hydraulically connected to the proximal end 1406 of the aspiration lumen 1404 via a connector 1424. The extension tube 1438 may be supplied (e.g., sterile) with the aspiration catheter 1402 or may be supplied separately packaged. A Touhy-Borst seal 1446 mounted on the connector 1424 is configured to be loosened / opened to allow insertion of a guidewire 1448 through the connector 1424 and the aspiration lumen 1404. Thus, the aspiration lumen 1404 can be used to track the aspiration catheter 1402 over a guidewire 1448 through the subject's vasculature. The Touhy-Borst 1446 can be tightened to seal off the guidewire 1448 and maintain hemostasis. Other types of seals can be incorporated in place of the Touhy-Borst 1446, including spring-loaded, longitudinally compressible, actuatable seals.The dilation tube 1438 includes a male luer 1450 at its distal end 1440 for connecting to a female luer 1452 on the connector 1424. The male luer 1450 may include a stopcock 1454 configured to rotate to select between an open position (as shown) or a closed position. The dilation tube 1438 and its components may be supplied sterile as a single unit. Alternatively, the dilation tube 1438 may be integral with the suction lumen 1404 or may be permanently attached to the connector 1424. During use, the compressible portion 1437 of the extension tube 1438 is positioned within the pressure shoe 1428 of the peristaltic pump 1408 such that, as the rotatable head 1430 is rotated in the direction of rotation 1436, the rollers 1432 compress the compressible portion 1437, one at a time, forcing fluid through the lumen 1444 of the extension tube 1438 from the distal end 1440 to the proximal end 1442. The single insertion step for connecting the compressible portion 1437 to the peristaltic pump 1408 is simple, fast, reliable, and does not require a connection (e.g., a luer) that must be sealed. Furthermore, compared to vacuum pumps and vacuum syringes, it is easy to visualize whether a peristaltic pump is operating properly. This may be because, under relatively high vacuum or negative pressure conditions, blood tends to cavitate, thus filling the space in a container (e.g., a canister or syringe) at an accelerated rate due to excessive gas volume. Air bubbles can also make it more difficult to see inside and visually inspect conditions. Optionally, interface 1456 on peristaltic pump 1408 is configured to allow a user to input information or commands to peristaltic pump 1408 or other components of system 1400. Otherwise, the hardware or firmware may be pre-programmed with specific execution parameters (motor speed, rotational speed, etc.). In some embodiments, there are only two rollers 1432. In other embodiments, there are three rollers 1432. In yet other embodiments, there are four rollers 1432, as shown.In an alternative embodiment, instead of rollers, smooth, rounded ridges of rigid material slide over and compress the compressible portion 1437. In this alternative embodiment, the compressible portion 1437 and / or the ridges may be treated with a lubricious material or constructed from a significantly lubricious material to favor sliding friction between the compressible portion 1437 and the ridges. Returning to the embodiment of FIG. 36 , the compressible portion 1437 may comprise silicone tubing, polyurethane tubing, polyvinyl chloride tubing, or other compressible tubing. The compressible section 1437 may be a relatively short section that is attachable and detachable to the peripheral end of the dilation tube 1438, or in other embodiments, may comprise the entire dilation tube 1438 between the distal end 1440 and the proximal end 1442. The proximal end 1442 of the extension tube 1438 can be connected to a hub 1457 of a canister 1458 having an interior 1460 to allow fluid 1459 passing through the extension tube 1438 to pass into the interior 1460. An additional hub 1462 in the canister 1458 can be left open (as shown) to allow the uncharged interior 1460 to equalize to atmospheric pressure. Alternatively, the canister 1458 can be replaced with another type of receptacle, such as a bag, or more specifically, an empty infusion bag configured to collect aspirant therein.

[0183] The suction catheter 1402 further has a high-pressure infusion lumen 1410 for infusing saline from a fluid source 1479, for example, via a high-pressure pump 1412. The tubing set 1464 may include a pump cartridge 1466 having a piston, or bellows, or other moving element that the pump 1412 can operate using an internal motor 1491, thus pressurizing saline (or other fluid) from the fluid source 1479 at a significantly high pressure so that the saline is forced through the infusion lumen 1410 of the suction catheter 1402. The tubing set 1464 includes a proximal end 1468 having a spike 1489 or other connecting element for hydraulically connecting the tubing set 1464 to the fluid source 1479. The tubing set 1464 may include a male luer and further has a distal end 1470 configured to hydraulically connect the tubing set 1464 to the infusion lumen 1410 via a female luer 1472. The tubing set 1464 may be supplied sterile as a single unit or may be permanently attached to the suction catheter 1402. During use, infused saline is forced through the infusion lumen 1410 by the pump 1412 and exits an orifice 1474 at the distal end 1476 of the infusion lumen 1410. The infusion lumen 1410 may extend into a separate tube 1478 (the infusion tube) that is substantially or completely within the shaft 1401. In some embodiments, the tube 1478 is attached to the inner wall of the shaft 1401 only at the distal end portion 1403. Thus, the free-floating nature of the remaining portion of the tube 1478 within the suction lumen 1404 increases the flexibility and trackability of the shaft 1401. Additionally, because bending of the shaft 1401 is not directly applied to the tube 1478, the likelihood of the tube 1478 kinking due to bending of the shaft 1401 is reduced. High pressure saline is forced through infusion tube 1478 and out orifice 1474, creating jet 1487. Jet 1487 resides within aspiration lumen 1404 just proximal to open distal end 1405, which can create a Venturi effect to push blood or clots externally adjacent open distal end 1405 into aspiration lumen 1404.Operation of the peristaltic pump 1408, in which the rotatable head 1430 rotates in a first rotational direction 1436, continuously and forcibly moves the fluid column within the lumen 1444 of the extension tube 1438, thereby pulling the fluid column within the suction lumen 1404, thereby moving fluid and blood clots from the open distal end 1405 of the suction lumen 1404 to the proximal end 1442 of the extension tube 1438. The combination of the action of the peristaltic pump 1408 and the jet 1487 generated by the high-pressure saline causes maceration of the thrombus and movement / flow of material (saline / blood / macerated thrombus / thrombus fragments) through the suction lumen 1404 from the open distal end 1405 to the proximal end 1406, through the interior 1485 of the connector 1424, through the lumen 1444 of the extension tube 1438 from the distal end 1440 to the proximal end 1442, and finally into the interior 1460 of the canister 1458. Thus, thrombus within a subject's blood vessels can be macerated and removed using the system 1400. The blood vessels may include peripheral blood vessels, coronary blood vessels, or blood vessels within the subject's head or neck, including the carotid or cerebral arteries.

[0184] A suction monitoring system 1414 including a pressure transducer 1416 can be connected, for example, between the distal end 1440 of the dilation tube 1438 and the connector 1424 and / or between the proximal end 1406 of the suction lumen 1404 of the suction catheter 1402. The suction monitoring system 1414 can include any of the features described in connection with the other suction monitoring systems 48, 62, 78, 900, 1216, and 1270 disclosed herein. A signal from the pressure transducer 1416 is carried over an electrical cable 1480 to an input 1482 of the pump 1412. A controller 1484 within the pump 1412 is configured to control the operation of the pump 1412, including the motor 1491, but the controller 1484 can also be configured to control the operation of the peristaltic pump 1408 via a cable 1486 or wirelessly. The controller 1484 can include a microcontroller. Alternatively, the controller 1484 may be located within the peristaltic pump 1408 or elsewhere. Control using the measured pressure signal from the pressure transducer 1416 adds an additional element of safety to the system 1400. Furthermore, a non-functioning system 1400 or a particular component of the system 1400 can be quickly identified. For example, a leak, a faulty connection, incomplete priming of one of the lumens, a rupture, or a break can cause a change in the signal from the pressure transducer 1416, thus enabling their identification. Unacceptably high pressures can also be quickly identified, and the controller 1484 configured to automatically shut down the pump 1412, thus protecting the motor 1491 of the pump 1412 from burning or overheating and any associated failures or hazards. The peristaltic pump 1408 can also be shut down by the controller 1484. In some embodiments, the peristaltic pump 1408 is configured to be shut down by the controller 1484 after the pump 1412 is shut down (e.g., after a finite delay). The delay can be between about 0.01 seconds and about 1.00 seconds, or between about 0.10 seconds and about 0.25 seconds. The integrity of the tube 1478 is also protected, for example, avoiding unnaturally high pressures that could lead to rupture.In some embodiments, the peristaltic pump 1408 may be battery-powered and the controller 1484 may be located within the peristaltic pump 1408, thus providing a self-contained peristaltic pump 1408 that can be easily moved from one location to another. In some embodiments, the peristaltic pump 1408 may even be easily cleanable and sterilizable so that it can be placed in a sterile field, such as a sterile field near a patient. In some embodiments, the pump 1412 is configured to remain in a non-sterile field, and the peristaltic pump 1408 is configured for sterile use. A push button 1411 may be mounted on the peristaltic pump 1408 and configured for activation by a user, for example, a user who is scrubbed for contact with sterile items only. The push button 1411 may be configured to start or stop operation of the peristaltic pump 1408. Additionally, the push button may be configured to start or stop operation of the pump 1412 (e.g., via cable 1486). In some embodiments, the peristaltic pump 1408 and pump 1412 are combined into a single console, which allows for a smaller size that can be attached to a standard IV pole.

[0185] In some embodiments, activation of push button 1411 by a user's finger initiates operation of peristaltic pump 1408, which then initiates operation of pump 1412 a short delay after peristaltic pump 1408 has been initiated. The delay is useful to ensure that some suction or a significant amount of suction has been applied to aspiration lumen 1404 before injecting pressurized fluid (e.g., saline) through infusion lumen 1410. Thus, blood vessels or other vasculature near open distal end 1405 are spared from infusion of fluid from the high-pressure jet, as they are instead aspirated through aspiration lumen 1404, along with aspirated clots or blood. Furthermore, in some embodiments, activation of push button 1411 by a user's finger while pump 1412 and peristaltic pump 1408 are operating simultaneously stops operation of pump 1412 and peristaltic pump 1408. In other embodiments, a delay can be implemented, for example, such that the pump 1412 is stopped, followed by the peristaltic pump 1408 being stopped after a short delay. The described delay lengths can be between about 0.01 seconds and about 1.00 seconds, or between about 0.10 seconds and about 0.25 seconds. In some embodiments, the controller 1484 is configured to change the rotational speed of the rotatable head 1430 of the peristaltic pump 1408, e.g., to increase or decrease the speed. In some embodiments, the controller 1484 is configured to change the flow rate (infusion rate) of the pump 1412, e.g., to increase or decrease the infusion rate. In some embodiments, the controller 1484 is configured to change the flow rate / flow rate of both pumps 1408, 1412 simultaneously. In some embodiments, the controller 1484 is configured to change the flow rate / flow rate of one of the pumps 1408, 1412, and then change the other flow rate / flow rate of the pumps 1408, 1412 after a certain delay. Any of these commands from the controller 1484 may be responsive to a change in the signal received from the pressure transducer 1416 .The peristaltic pump 1408 at its peak pulse (e.g., sinusoidal peak amplitude) provides a significant negative pressure gradient so that the difference between the pressure transducer 1416 reading in a clogged state and the pressure transducer 1416 reading in a free-flow state is amplified. Therefore, more potential thromboembolic events, such as the release of a blood clot from the open distal end 1405 of the aspiration lumen 1404 of the aspiration catheter 1402, are avoided. Pressure fluctuations on the pressure transducer 1416 tend to be significantly larger when using a peristaltic pump 1408 than when using a vacuum pump or other vacuum source (e.g., a vacuum syringe). One important advantage is that the user can be clearly informed when a blood clot / thrombus is not being aspirated, and therefore when the aspiration is free-flowing, causing blood loss without removing the blood clot 1402. It is much easier to recognize the state of the open distal end 1405 of the aspiration catheter. Current vacuum pumps lack a similar clear way to indicate active and dormant states. Therefore, the user is notified and the pumps 1408, 1412 are stopped to minimize blood loss and allow for repositioning of the clot. Peristaltic pumps 1408 also tend to be quieter than vacuum pumps and less likely to interfere with communication or increase stress for medical personnel during the procedure.

[0186] When the peristaltic pump 1408 is stopped, at least one roller 1432 remains in a position compressing the compressible portion 1437 of the dilation tube 1438. Therefore, no on-off valve, pinch valve, stopcock, or other valve is required. The fact that the rotatable head 1430 is already moving means that when the peristaltic pump 1408 is stopped, the rollers 1432 move rapidly to an occlusion position without significant inertia requirements. This can therefore be faster than the activation of a standard electrically activated pinch valve, which is initially stationary and must be moved before it can be pinched. The motor 1497 may comprise a stepper motor that is oriented (e.g., by the controller 1484) so ​​that the rotatable head directs one of the rollers 1432 to occlude the lumen 1444 of the dilation tube 1438 with the compressible portion 1437. In FIG. 36, roller 1432c is in a position to occlude the lumen 1444 (when the motor 1497 is stopped). Thus, the peristaltic pump 1408 itself inherently minimizes the possibility of distal embolization, since immediate or near-instantaneous stopping of the pump causes stagnation. Alternatively, a non-stepping motor, such as a brushless DC motor, can be utilized in place of a stepping motor, along with an encoder (e.g., an optical encoder) or another type of position sensor. Furthermore, unmacerated clots can therefore be stopped from entering the aspiration lumen 1404. As described, in other embodiments, the rollers 1432 may be replaced by non-rotating ridges or protrusions that slide over the compressible portion 1437 of the dilation tube 1438 instead of rolling over. In some embodiments, the outer surface of the ridges / protrusions and / or compressible portion 1437 may be coated with silicone, hydrophilic, or other lubricious materials to reduce friction.

[0187] The controller 1484 may be configured to control the operation of the pump 1412 to cause the pump 1412 to inject pressurized fluid in a pulsatile manner. The high-pressure jet is applied in a pulsating manner to optimize the jet's ability to cut through portions of the thrombus. For example, a portion of the thrombus aspirated into the open distal end 1405 of the aspiration lumen 1404 of the aspiration catheter 1402 may be more easily cut by a pulsating jet, similar to a reciprocating saw. The controller 1484 is also configured to operate the pump 1412 to pressurize fluid through the infusion lumen to produce one or more pulsating jets. The controller 1484 may also be configured to operate the peristaltic pump 1408 to further assist the pressurized fluid injected through the infusion lumen in producing one or more pulsating jets. For example, the controller 1484 may send a signal to induce sinusoidal variations in the speed of the motor 1491. The degree of pulsatility (pulse rate, peak pulse, pulse waveform, rise time, on time, off time) may be adjusted and controllably applied by the controller 1484 on the pump 1412 and / or peristaltic pump 1408.

[0188]

[0188] The use of the peristaltic pump 1408 ensures that the interior of the suction lumen 1404 and lumen 1444 of the extension tube 1438 and their contents are not contacted, thus further ensuring the maintenance of sterility. The use of the peristaltic pump 1408 also minimizes or substantially eliminates cavitation of the blood being removed. If cavitation occurs during aspiration proximal to the peristaltic pump 1408, after the blood and aspirate pass through the rollers 1432, the blood is exposed to atmospheric pressure and the cavitation disappears. Therefore, it is easier to determine the amount of blood collected or being collected in the canister 1458 because the indicated amount of collected blood is clearly visible and not obscured by air bubbles or foam, making it reliable to measure. Furthermore, it is easier to quickly reuse blood, for example, if it is to be reinfused into a subject. It is also safer and more reliable to inject blood without large air bubbles. Using a vacuum source, such as a thermos or vacuum syringe, can tend to increase cavitation. Thus, the peristaltic pump 1408 can be used to achieve an efficient treatment and to maximize the amount of blood that can be reinfused. The tubing set 1464 separates the extension of the infusion lumen 1410 from the aspiration lumen 1404 with the male luer 1410 of the connector 1424, so only the compressible portion 1437 of the extension tube 1438 needs to be compressed by the rollers 1432. Therefore, other portions of the aspiration catheter 1402 are not compressed by the rollers 1432 and are therefore not in danger of being crushed or otherwise damaged. The distal end 1483 of the aspiration catheter 1402 can, in some embodiments, resemble the distal end of the catheter 516 of FIG. 17 . The aspiration catheter 1402 may, in some embodiments, be replaced by the thrombectomy system 300 of FIG. 34 or the thrombectomy catheter 306 described in U.S. Patent No. 9,433,427, issued September 6, 2016, and entitled "Systems and Methods for Management of Thrombosis." The use of a peristaltic pump 1408 has additional advantages over a vacuum pump.The peristaltic pump 1408 can be configured to be controlled by the controller 1484 so that it only operates when the pump 1412 is injecting, thus reducing noise compared to systems that use a vacuum pump because the vacuum pump is always on (operating).

[0189] FIG. 37 shows a subject 1500 on a hospital bed 1502 or table receiving blood infusion via three different modalities. During a thrombectomy procedure, a thrombus / clot is removed from the subject's 1500 blood vessels. In some cases, the patient's blood volume becomes abnormally low, requiring fluid or blood to be reinfused into the patient. In the first modality, the peristaltic pump 1408 of the system 1400 of FIG. 36 is shown. An aspiration catheter 1402 is inserted into the subject 1500, and an aspiration (thrombectomy) procedure is being performed. Instead of a canister 1458, an extension tube 1438 at its distal end 1442 is connected to an intravascular (IV) line 1504 inserted into the subject's 1500 vein. The blood is driven by rollers 1432 of the peristaltic pump 1408 through a hemofilter 1506, which removes any residual thrombus or particles before the blood is infused into the subject's vein. Heparin or other additives may also be added to the blood as it is infused into the subject 1500 through port 1481, which communicates with the intravascular (IV) line 1504. Because the blood flows only through a single, sterile, composite conduit, an efficient and clean reinfusion method is achieved. The blood may be purified, for example, to remove hemolyzed red blood cells or portions of red blood cells. One such reinfusion device is the Haemonetics Cell Saver® Elite+ Autotransfusion System. The peristaltic pump 1408 is believed to cause less damage to blood cells and therefore may require less, if any, cleaning. Therefore, due to the advantages of the peristaltic pump 1408, higher blood yields are possible after using the Cell Saver. Furthermore, blood can be easily transferred to the Cell Saver in a contactless manner directly from the extension tube 1438, which is not possible with transfer from a collection container used with a vacuum source. When sent directly to the Cell Saver, the blood can even be kept sterile. In some embodiments, the dilation tube 1438 may be significantly translucent so that the thrombus can be assessed during aspiration. A video camera or magnification element (such as a low-power microscope) can be focused on the dilation tube 1438 to better identify the condition (amount, amount of maceration) of the thrombus being aspirated.There can be near real-time feedback on the status of the clot being dislodged from within the patient's vasculature.

[0190] In the second modality, blood is collected in a canister 1458 from a previous treatment (FIG. 36). The blood can then be filtered or spun in a centrifuge to obtain specific components. Heparin or other additives can also be added to the blood. The blood is then placed in a blood bag 1508 (or blood bottle) and infused into the subject's 1500 vein using passive drip (e.g., by gravity alone) via an IV line 1510. In other cases, a pressurizable bag 1512 can be used around the blood bag 1508 to increase compression of the blood bag 1508 and thus increase flow rate to the vein. In some cases, blood can even be infused directly into the arterial system, for example, via an arterial line (a-line). The blood can be further purified as described above.

[0191] In the third modality, blood is collected in a canister 1458 from a previous procedure (FIG. 36). The blood may then be filtered or spun in a centrifuge to obtain specific components. Heparin or other additives may also be added to the blood. The blood is then placed in a blood bag 1514 and pumped into the vein of the subject 1500 using an infusion pump 1516. Insertion points 1518a, 1518b, and 1518c are shown for the first, second, and third modalities, respectively. The blood may be further purified as described above.

[0192] 38 shows an alternative suction system 1400' comprising a suction catheter 1402' with an elongate shaft 1401' including a suction lumen 1404' having an open distal end 1405' and a proximal end 1406' configured to connect to a peristaltic pump 1408. The peristaltic pump 1408 may be a roller pump having a base 1426, a pressure shoe 1428 carried by the base 1426, and a rotatable head 1430 rotatably connected to the base 1426 and carrying two or more rollers 1432a-1432d. The rollers 1432a-1432d are arranged around a periphery 1434 of the rotatable head 1430. The rotatable head 1430 is configured to be rotatable in at least a first rotational direction 1436 about a rotation axis 1499. The rotatable head 1430 can be rotated by a motor 1497, either directly or in conjunction with a gear train 1495. The peristaltic pump 1408 can be battery-powered, and the battery can be rechargeable wired or wirelessly. The peristaltic pump 1408 can alternatively, or additionally, be powered by a power cord 1493 configured to connect to a power source. An extension tube 1438 having a distal end 1440 and a proximal end 1442 and having a lumen 1444 extending therethrough is hydraulically connected to the proximal end 1406' of the aspiration lumen 1404' via a connector 1424'. The extension tube 1438 can be supplied (e.g., sterilized) with the aspiration catheter 1402' or can be supplied separately packaged. The Touhy-Borst seal 1446' is connectable and detachable to the connector 1424' (e.g., via Luer connections 1750, 1752) and is configured to be loosened / opened to allow insertion of a guidewire 1448 through the connector 1424' and aspiration lumen 1404'. Thus, the aspiration lumen 1404' can be used to track the aspiration catheter 1402' over the guidewire 1448 through the subject's vasculature. The Touhy-Borst 1446' can be tightened to seal off the guidewire 1448 and maintain hemostasis.Other types of seals can be incorporated in place of the Touhy-Borst 1446', including spring-loaded, longitudinally compressible, and actuatable seals. The distal end 1440 of the dilator tube 1438 slides over a first barb fitting 1754 of the y-connector 1756. The second dilator tube 1760 has a distal end 1761 that slides over a second barb fitting 1758 of the y-connector 1756. The third dilator tube 1762 has a proximal end 1763 that slides over a third barb fitting 1764 of the y-connector 1756. The second dilator tube 1760 and the third dilator tube 1762 are configured to operate under negative pressure without collapsing and may include standard suction tubing. The distal end 1765 of the third dilation tube 1762 is connected to the female luer 1452' side port of the connector 1424' by molding, adhesive connection, welding, or by an attachable and detachable connection such as a luer 1766. The lengths of each of the second dilation tube 1760 and the third dilation tube 1762 can vary. In some embodiments, the third dilation tube 1762 is relatively short, and the y-connector 1756 is configured to be placed in a sterile area near the patient. In other embodiments, the third dilation tube 1762 is configured to be relatively long, and the y-connector 1756 is configured to be placed in a non-sterile area away from the patient. The second dilation tube 1760 is optional, the third dilation tube 1762 can have a much longer length, and the pressure transducer 1416 / suction monitoring system 1414 can be attached directly to the y-connector 1756 at the barb fitting 1758. This connection may be a direct connection, for which reason the barb fitting 1758 is also optional. If a longer third extension tube 1762 is used, the y-connector 1756 and the suction monitoring system 1414 may both be near the pump 1412 and both may be in a non-sterile area.

[0193]

[0193] In use, the compressible portion 1437 of the dilation tube 1438 is positioned within the pressure shoe 1428 of the peristaltic pump 1408 such that, when the rotatable head 1430 is rotated in the rotational direction 1436, fluid is forced through the lumen 1444 of the dilation tube 1438 from the distal end 1440 to the proximal end 1442, one at a time, via compression of the compressible portion 1437 by the rollers 1432. Optionally, the interface 1456 on the peristaltic pump 1408 is configured to allow a user to input information or commands to the peristaltic pump 1408 or other components of the system 1400'. Otherwise, the hardware or firmware may be pre-programmed with specific execution parameters (motor speed, rotational speed, etc.). In some embodiments, there are only two rollers 1432. In other embodiments, there are three rollers 1432. In yet other embodiments, there are four rollers 1432, as shown. As described, the rollers 1432 can be replaced by ridges or protrusions. The compressible portion 1437 can include silicone tubing, polyurethane tubing, polyvinyl chloride tubing, or other compressible tubing. The compressible section 1437 can be a relatively short section that is attachable and detachable to the peripheral end of the dilation tube 1438, or in other embodiments, can include the entire dilation tube 1438 between the distal end 1440 and the proximal end 1442. The proximal end 1442 of the dilation tube 1438 can be connected to a hub 1457 of a canister 1458 having an interior 1460 to allow fluid 1459 passing through the dilation tube 1438 to pass into the interior 1460. An additional hub 1462 in the canister 1458 can be left open (as shown) to allow the uncharged interior 1460 to equalize to atmospheric pressure. Alternatively, the canister 1458 can be replaced with a bag, such as an empty infusion bag, configured to collect aspirate therein.

[0194] The suction catheter 1402' further has a high-pressure infusion lumen 1410' for infusing saline from a fluid source 1479, for example, via a high-pressure pump 1412. The tubing set 1464 may include a pump cartridge 1466 having a piston or bellows, or other moving element that the pump 1412 can operate using an internal motor 1491, thus pressurizing saline (or other fluid) from the fluid source 1479 at a significantly high pressure so that the saline is forced through the infusion lumen 1410' of the suction catheter 1402'. The tubing set 1464 includes a proximal end 1468 having a spike 1489 or other connecting element for hydraulically connecting the tubing set 1464 to the fluid source 1479. The tubing set 1464 further has a distal end 1470 (which may include a male luer) configured to hydraulically connect to the infusion lumen 1410' via a female luer 1472'. During use, infused saline is forced by pump 1412 through infusion lumen 1410' and exits orifice 1474' at distal end 1476' of infusion lumen 1410'. Infusion lumen 1410' can extend into a separate tube 1478' (infusion tube) that is substantially entirely within shaft 1401'. In some embodiments, tube 1478' is attached to the inner wall of shaft 1401' only at distal end portion 1403'. Thus, the free-floating nature of the remaining portion of tube 1478' within aspiration lumen 1404' enhances the flexibility and trackability of shaft 1401'. High-pressure saline is forced through infusion tube 1478' and out orifice 1474', creating a jet (similar to jet 1487 in FIG. 36 ). The jet is directed into the aspiration lumen 1404' just proximal to the open distal end 1405', which can create a Venturi effect and push blood or clots externally adjacent the open distal end 1405' into the aspiration lumen 1404'.The combination of the action of the peristaltic pump 1408 and the jets generated by the high-pressure saline causes maceration of the thrombus and movement / flow of material (saline / blood / macerated thrombus / thrombus fragments) through the suction lumen 1404' from the open distal end 1405' to the proximal end 1406', through the female luer 1452' of the connector 1424', through the lumen 1444 of the extension tube 1438 from the distal end 1440 to the proximal end 1442, and finally into the interior 1460 of the canister 1458. Thus, thrombus within a subject's blood vessels can be macerated and removed using the system 1400'. The blood vessels may include peripheral blood vessels, coronary blood vessels, or blood vessels within the subject's head or neck, including the carotid or cerebral arteries.

[0195] The suction monitoring system 1414 including the pressure transducer 1416 may be connected, for example, proximal to the connector 1424' and / or proximal to the proximal end 1406' of the suction lumen 1404' of the suction catheter 1402' so that the pressure transducer 1416 is hydraulically connected to the suction lumen 1404'. In the suction system 1400' of FIG. 38, the suction monitoring system 1414 is spaced from the y-connector 1756 by a relatively long second extension tube 1760 (or, as in the case of the suction system 2100 of FIG. 74, by a relatively long third extension tube 1762) so that the suction monitoring system 1414 resides in a non-sterile field. Thus, the suction monitoring system 1414 may be set up, prepared, calibrated, and operated by a technician, sales representative, nurse, or other medical personnel who are not "scrubbed" and therefore do not need to maintain sterility. For example, the suction monitoring system 1414 may be located near the pump 1412 or on the same table as the pump 1412. The suction monitoring system 1414 may include any of the features described in connection with the other suction monitoring systems 48, 62, 78, 900, 1216, and 1270 disclosed herein. A signal from the pressure transducer 1416 is carried over an electrical cable 1480 to an input 1482 of the pump 1412. A controller 1484 within the pump 1412 is configured to control the operation of the pump 1412, including the motor 1491, but the controller 1484 may also be configured to control the operation of the peristaltic pump 1408 via a cable 1486 or wirelessly. The controller 1484 may comprise a microcontroller. Alternatively, the controller 1484 may be located within the peristaltic pump 1408 or elsewhere. Control using the measured pressure signal from the pressure transducer 1416 adds an additional element of safety to the system 1400'. Additionally, non-functioning equipment (due to leaks, poor connections, poor priming, ruptures, or blockages) can be quickly identified. Unacceptably high pressures can also be quickly identified, protecting the motor 1491 of the pump 1412 from the risk of burning out or overheating. The integrity of the tubing 1478' is also protected, avoiding unnaturally high pressures that could lead to rupture, for example.

[0196] The aspiration catheter 1402' is similar to the aspiration catheter 1402 of FIG. 36, except that the female luer 1452' is located distal to the connector 1424' from the female luer 1472'. Thus, the aspirated blood / thrombus / saline enters the female luer 1452' without having to contact any internal irregularities 1425' (in geometry, shape) within the connector 1424' that might otherwise cause flow resistance or trap thrombus (e.g., between the tubing 1478' and the interior of the connector 1424').

[0197] The foot pedal 1451 has a base 1453 and a pedal 1455 connected to the base 1453 and movable or actuable by application of a user's foot. The pedal 1455 may be spring-loaded, depressed by application of a moment or compressive force, or alternatively may comprise a membrane switch. When activated, the pedal 1455 can switch on and off in some embodiments, and in other embodiments, can be actuable when a force, pressure, or moment is applied and deactivated when no force, pressure, or moment is applied. A first cable 1461 carries a signal from the foot pedal 1451 to the pump 1412 via a plug 1465 connected to an input jack 1467. In some embodiments, activation of pedal 1455 by the user's foot causes a signal via first cable 1461 to be received by controller 1484 commanding pump 1412 to start and via cable 1486 commanding peristaltic pump 1408 to start, thereby simultaneously initiating operation of pump 1412 and peristaltic pump 1408. In some embodiments, activation of pedal 1455 by the user's foot initiates operation of peristaltic pump 1408, which then initiates operation of pump 1412 a short delay after peristaltic pump 1408 is initiated. The delay is useful to ensure that some suction or a significant amount of suction has been applied to aspiration lumen 1404′ before infusing pressurized fluid (e.g., saline) through infusion lumen 1410′. Thus, blood vessels or other vasculature near open distal end 1405′ are spared from infusion of fluid from the high-pressure jet, as they are instead aspirated through aspiration lumen 1404′, along with any blood clots or blood. In some embodiments, the plug 1465 of the foot pedal 1451 may include a resistor 1759, and the pump 1412 may include an identification circuit 1757 configured to read the resistance of the resistor 1759. For example, the resistor 1759 may complete a partial Wheatstone bridge mounted on the identification circuit 1757 so that the pump 1412 can recognize the foot pedal 1451 and act accordingly.Alternatively, resistor 1759 may be present on foot pedal 1451 itself, instead of plug 1465. Cable 1461 may provide an electrical connection to resistor 1759 in that particular case. Alternatively, resistor 1759 may be replaced by an RFID chip configured to be powered and read by identification circuit 1757.

[0198] Additionally, in some embodiments, activation of the pedal 1455 by the user's foot while the pump 1412 and peristaltic pump 1408 are operating simultaneously stops the operation of the pump 1412 and the peristaltic pump 1408. In other embodiments, a delay can be implemented, for example, such that the pump 1412 is stopped, followed by a short delay in stopping the peristaltic pump 1408. The length of the described delay can be between about 0.01 seconds and about 1.00 seconds, or between about 0.10 seconds and about 0.25 seconds. Activating (on / off) the pump 1412 and / or peristaltic pump 1408 via the foot pedal 1451 allows for hands-free activation, allowing a single user to operate the suction catheter 1402′ and guidewire 1448 with both hands. The location of the foot pedal 1451 can be tactilely located with the user's foot while maintaining visual contact with the patient and / or any monitors or other medical personnel. Alternatively, second cable 1463 carries a signal directly from foot pedal 1451 to peristaltic pump 1408 via plug 1469 connected to input jack 1471. Thus, operation of foot pedal 1451 can be configured to control operation of peristaltic pump 1408, for example, in embodiments without cable 1486. ​​However, in the embodiment of FIG. 38 which includes cable 1486, cable 1463 is not required.

[0199] In other embodiments, the foot pedal 1451 may be replaced with another type of switch, including, but not limited to, a toggle on / off push button or hand switch, a voice-activated switch (voice-activated, clap-activated, click-activated), a light switch (beam / light sensor for hand or foot interruption), or any other type of switch that can be activated by medical personnel. The switch may be located in a remote location (e.g., a control room) or near the treatment area. The switch may also be a sterile switch or may be sterilizable for location on the sterile field.

[0200] In some cases, activating and deactivating (turning on and off) the suction flow applied by peristaltic pump 1408 to suction lumen 1404′ can be accomplished by leaving peristaltic pump 1408 running while a user opens and closes stopcock 1454. In some embodiments, controller 1484 controls the initiation of both peristaltic pump 1408 and pump 1412 substantially simultaneously. In some embodiments, controller 1484 controls the initiation of peristaltic pump 1408 and, following a particular delay, controls the initiation of pump 1412. The delay can be within the ranges described above.

[0201] The controller 1484 also monitors and controls several device safety features, including overpressure detection, air bubble detection, and vacuum or negative pressure charging. An additional pressure transducer 1415 mounted on the connector 1424 monitors the pressure (i.e., injection pressure) and senses the presence of air bubbles. Alternatively, or in combination, an optical device 1417 can be used to sense air bubbles. In one possible embodiment, the pump pressure is proportional to the current required by the pump 1412 to generate that particular pressure. Thus, if the current required by the pump 1412 exceeds a preset limit, the controller 1484 disables the pump 1412 by cutting off power to the pump 1412. Air bubble detection can also be monitored by monitoring the current required to drive the pump 1412 at a particular moment. In order for the pump 1412 to reach high fluid pressures, there should be little to no air (which is highly compressible) in the pump 1412 or the connecting system (including the suction lumen 1404' of the suction catheter 1402' and the tubing set 1464). The fluid volume is small enough that air in the system does not create pressure at the pump head. A sufficient amount of liquid is required proximally to allow a finite amount of air to flow. The controller 1484 monitors the pump 1412 current for a sudden downward change that may indicate air has entered the system. If the rate of decline is faster than a preset limit, the controller 1484 disables the pump 1412 by cutting power to the pump 1412 until the problem is corrected.

[0202] In some embodiments, the fluid level sensor 1473 is mounted to the side of the canister 1458 and configured to sense when the canister 1458 approaches or reaches its full level. The fluid level sensor 1473 is configured to output a signal via a cable 1475 attached via an input 1477 (plug / jack) of the pump 4112. The signal from the fluid level sensor 1473 can be received by a controller 1484, which can be configured to stop the pump 1412 and the peristaltic pump 1408 via cable 1486 simultaneously or immediately with a delay therebetween, as described above. The fluid level sensor 1473 can include an optical sensor, and the canister 1458 can have transparent walls to allow the optical sensor to measure reflective variations when no fluid is present adjacent or when fluid is present adjacent. Alternatively, fluid level sensor 1473 may include a piezoresistive pressure sensor within volume 1460 of canister 1458 at a desired height representing a "full" canister 1458. Other types of fluid sensors are also contemplated, such as floats, strain gauges, laser sensors, ultrasonic sensors, or capacitance sensors. In each of these embodiments, a signal may be transmitted wirelessly or via cable 1475 so that peristaltic pump 1408 and / or pump 1412 may shut down when the "full" level is reached.

[0203] In some embodiments, the peristaltic pump 1408 and the pump 1412 are combined into a single console. This allows for a smaller size that can be attached to a standard IV pole. FIG. 74 shows an aspiration system 2100 having all the features of the aspiration system 1400′ of FIG. 38, but with the peristaltic pump feature 2108 and the infusion pump feature 2112 both included in a single console 2102. The third extension tube 1762 is elongated, and the aspiration monitoring system 1414 is directly connected or connectable to the y-connector 1756. The aspiration monitoring system 1414 can reside in a non-sterile area. Thus, the aspiration monitoring system 1414 can be set up, prepared, calibrated, and operated by a technician, sales representative, nurse, or other medical personnel who are not “scrubbed” and therefore do not need to maintain sterility. For example, the aspiration monitoring system 1414 can be located on the same table as the console 2102. Cable 1486 of system 1400′ of FIG. 38 is not required, as a similar connection is located inside console 2100. Cable 1463 of system 1400′ of FIG. 38 is also not required, as cable 1461 can transfer all signals to and from foot pedal 1451. Luer 1766 may be attachable and detachable, or in other embodiments, may be permanently connected to female luer 1452′ of connector 1424′.

[0204] FIG. 39 shows an alternative suction system 1400″ including the suction catheter 1402′ of FIG. 38. However, a centrifugal pump 1409 replaces the peristaltic pump 1408. The proximal end 1442 of the extension tube 1438 is connected to an inlet 1413 that allows aspirant to enter the chamber 1419. An impeller 1421 is rotatably held within the chamber 1419 by a first bearing 1423 and a second bearing 1427. A first seal 1429 and a second seal 1431 allow the impeller 1421 to rotate (curved arrow) without aspirant leakage. A motor 1433 is configured to rotate the impeller 1421. Aspirant is forced out of the outlet 1435 into an outlet tube 1439 connected to the hub 1457 of the canister 1458. The user interface 1441 can be manipulated by a user to activate the centrifugal pump 1409. In some embodiments, an Angiodynamics AngioVac centrifugal pump can be used as the centrifugal pump 1409.

[0205] The suction catheters 1402, 1402' of Figures 36, 38, and 39 are shown as having pressurized fluid infusion via the infusion lumen 1410, 1410'. However, other embodiments of the suction system 1400, 1400' in which the suction catheter 1402, 1402' is replaced by a standard suction catheter, such as the suction catheter 4 of Figure 1, do not have an infusion lumen.

[0206]

[0206] Instead of collecting the aspirated material in a blood bag, blood bottle, or canister 1458, the aspirated components (blood, clot, saline, slurry, etc.) can be placed in a reinfusion device, such as the Stryker ConstaVac (CBCII) Blood Conservation System or the Haemonetics OrthoPAT Orthopedic Perioperative Autotransfusion System. The blood can be purified by the reinfusion device, for example, to remove red blood cells or portions of red blood cells that have undergone hemolysis. One such reinfusion device is the Haemonetics Cell Saver® Elite+ Autotransfusion System.

[0207] In some embodiments, the blood may be cooled before being infused. In some embodiments, the blood may be heated before being infused. In some embodiments, other drugs may be added to the blood before it is inserted. In some cases, the blood may be diluted with saline to reduce viscosity or lower the hematocrit. This may result in reduced hemolysis. In some cases, the blood collected in canister 1458, or coming from extension tube 1438, may even be used as donor blood for infusion into another patient.

[0208] In some embodiments, additional or alternative sensors may be used to monitor flow conditions for notification to the user, including, but not limited to, Doppler sensors, infrared sensors, or laser flow detection devices. In some embodiments, an externally mounted (non-contact) Doppler sensor may be used. In some embodiments, an infrared sensor or laser flow detection device may be used around the extension tube 1438. Alternative sensors (e.g., flow sensors, etc.) may be placed at several different locations along the aspiration path, including on or in the extension tube 1438, distal to the impeller 1421 of the centrifugal pump 1409, or on or in the outlet tube 1439 proximal to the impeller 1421 of the centrifugal pump 1409. Alternatively, in embodiments using a peristaltic pump 1408, an alternative sensor may be placed on or in the extension tube 1438 distal or proximal to the rotatable head 1430 of the peristaltic pump 1408.

[0209] An aspiration system 1600 utilizing an ultrasonic sensor 1602 is shown in FIGS. 40-42. The aspiration system 1600 is similar to the aspiration system 1400′ of FIG. 38, except for the addition of the ultrasonic sensor 1602 and other related components. Alternate embodiments can utilize the teachings of other aspiration system embodiments disclosed herein. The ultrasonic sensor can be configured for an analog output (e.g., with a variable voltage output), for example, in the range of 0 volts DC to 1 volt DC, or 0 volts DC to 5 volts DC, or 0 volts DC to 10 volts DC. Referring to FIG. 41, the ultrasonic sensor 1602 is inserted into a side port 1606 of a y-connector 1604. The y-connector 1604 has a distal connector 1608 attached to the proximal end 1603 of a tube 1610. The tube 1610 slides over a barb 1605 that forms the distal connector 1608. The distal end 1607 of the tubing 1610 is connected to the proximal end 1406' of the suction lumen 1404' of the suction catheter 1402' via a connector 1609 and a suction monitoring system 1414 attached to the female luer 1452' of the connector 1424'. The proximal connector 1612 of the y-connector 1604 is connected to a friction fitting 1616 of the extension tube 1614. The proximal connector 1612 also includes a barb. The extension tube 1614 is connectable to a peristaltic pump 1608, but may alternatively be connected to a centrifugal pump 1409 or one of the vacuum sources described herein. The ultrasonic sensor 1602 is positioned so that its distal end 1618 is adjacent to the aspiration flow (solid arrow). A fitting 1620 at the proximal end of the ultrasonic sensor 1602 is configured to secure the ultrasonic sensor 1602 to the side port 1606 in its desired position. This can be a friction fit, screw mount, snap, adhesive connection, thermal connection, or other fastening means. The output (e.g., voltage) of the ultrasonic sensor is transmitted through a cable 1622. A strain relief 1601 connected to the cable 1622 and fitting 1620 functions to protect the first end 1611 of the cable 1622 from damage due to bending, tension, or compression.

[0210] In one embodiment, the ultrasonic sensor 1602 has an analog channel that outputs a ground-referenced signal that varies between 0 and 5 volts DC. At very low flow rates, the signal is often sinusoidal; however, at high flow rates, typically occurring during clot / thrombus / blood aspiration, the flow rate is large enough that the channel saturates and displays as a variable digital pulse stream roughly proportional to the flow. This channel has a relatively high pulse frequency; that is, a pseudo-digital on / off occurs when the flow rate exceeds a certain value. This specific value can be adjusted by connecting appropriate electronics. Along with the pseudo-digital nature of the channel, a dedicated digital I / O pin is utilized to power a high-priority interrupt handler. This allows for very efficient counting of rising signal transitions in this pulse stream at fixed time intervals. The pulse count, above / below one or more predetermined thresholds, ultimately determines whether the overall system is in a free-flow or clot-removal state, and to what extent.

[0211] FIG. 42 shows a console 1624 having an input jack 1626 to which a plug 1628 at the second end 1613 of the cable 1622 attaches. The console 1624 includes an internal measurement device 1630 configured to count the number of times N during a predetermined time period P that the signal being output by the ultrasonic sensor 1602 exceeds a predetermined threshold amplitude A. The measurement device 1630 is further configured to determine whether the number of times N is (a) greater than (or greater than) a predetermined value V or (b) less than (or less than) the predetermined value V. For example, in one embodiment, the predetermined time period P is input into the measurement device 1630 (e.g., via a user interface 1632) as 0.33 seconds. An algorithm within the measurement device 1630 counts the number of threshold crossings output by the ultrasonic sensor 1602 during this predetermined time period P. The measurement device 1630 then applies a particular logic scheme. In some embodiments, this logic scheme may simply be "flow" or "no flow." For example, if there are 0 to 150 counts within the period P, a "no flow" condition is identified, and if there are 151 or more counts within the period P, a "flow" condition is identified. The measurement device 1630 may include a microprocessor. A communication device 1634 mounted on the console 1624 may be controlled by the measurement device 1630 or by a separate controller to identify a first communication mode for a "no flow" condition and a second communication mode for a "flow" condition. In some embodiments, the first communication mode may include the absence of a signal from the communication device 1634 (e.g., no light, no sound, no vibration, or heat), and the second communication mode may include the illumination of a light, or the display of a message (e.g., the word "flow"), or the playing of an audio message (e.g., a sound indicating "suction is occurring"), or an audio alert (e.g., a "beep"), or a mechanical alert (e.g., a vibration). The amplitude of the communication (e.g., dB of sound, light intensity, etc.) can be increased by pressing the increase button 1615 or decreased by pressing the decrease button 1617. The current level of amplitude is shown on the display 1619.The display may comprise a series of LEDs 1621 configured to light up, with higher amplitude corresponding to more LEDs being lit.

[0212] In other embodiments, the first and second communication modes may each include several perceptible signals (auditory, visual, tactile), each distinct from the others. In other embodiments, more complex logic schemes may be used. For example, for a given period P of 0.33 seconds, if there are 0 to 150 counts within period P, a "no flow" state is identified; if there are 151 to 225 counts within period P, a "low flow" state is identified; if there are 226 to 350 counts within period P, a "medium flow" state is identified; and if there are 351 or more counts within period P, a "high flow" state is identified. The "no flow" state may correspond to the first communication mode, the "low flow" state may correspond to the second communication mode, the "medium flow" state may correspond to the third communication mode, and the "high flow" state may correspond to the fourth communication mode. The first communication mode may be handled by communication device 1634, which remains silent and / or non-visual / non-vibrating / non-heating, etc. The second communication mode may be handled by the communication device beeping (via an audio speaker) or flashing (via an LED or other light) at a frequency of 2 Hz. The third communication mode may be handled by the communication device beeping (via an audio speaker) or flashing (via an LED or other light) at a frequency of 4 Hz. The fourth communication mode may be handled by the communication device beeping (via an audio speaker) or flashing (via an LED or other light) at a frequency of 10 Hz. In another embodiment, the second communication mode may be handled by the communication device beeping (via an audio speaker) or flashing (via an LED or other light) at a frequency of 0.5 Hz. The third communication mode may be handled by the communication device beeping (via an audio speaker) or flashing (via an LED or other light) at a frequency of 1 Hz. The fourth communication mode may be handled by the communication device beeping (via an audio speaker) or flashing (via an LED or other light) at a frequency of 2 Hz. Additionally or alternatively, the signal strength may increase from the second communication mode to the fourth communication mode, for example, by 10 dB from the second to the third, and another 10 dB from the third to the fourth.Or increase by 5dB each time.

[0213]

[0213] In an alternative embodiment, the ultrasonic sensor 1602 may have an analog-to-digital module and may output only a digital signal characteristic of 1 (flow above a certain threshold flow rate) or 0 (flow below a certain threshold flow rate).

[0214] The predetermined period P may be between about 0.01 seconds and about 1.00 seconds, or between about 0.10 seconds and about 0.50 seconds, or between about 0.20 seconds and about 0.40 seconds. The predetermined period P may be adjustable by a user, for example, via user interface 1632.

[0215]

[0215] In certain aspiration procedures, if the clot is not adequately aspirated but aspiration continues, an unacceptably large amount of blood may be aspirated from the patient. This can lead to dehydration, a drop in blood pressure, and even blood loss in the patient—all potentially serious events that could jeopardize the success of the procedure and put the patient at risk. The ability to constantly recognize if blood is being aspirated at an unacceptable rate is a key factor in achieving a high degree of safety and efficiency.

[0216]

[0216] Disclosed herein is a system for catheter aspiration configured to communicate flow status and / or flow rate information to a user as determined by metering fluid, blood, clots, or other material aspirated from a patient over a period of time.

[0217] FIG. 43 shows an aspiration system 200 comprising an aspiration catheter 202 with an elongate shaft 201 including an aspiration lumen 204 having an open distal end 205 and a proximal end 206 configured for connection to a peristaltic pump 208. The peristaltic pump 208 may be a roller pump having a base 226, a pressure shoe 228 carried by the base 226, and a rotatable head 230 rotatably connected to the base 226 and carrying two or more rollers 232a-232d. The rollers 232a-232d are arranged around a periphery 234 of the rotatable head 230. The rotatable head 230 is configured to be rotatable in at least a first rotational direction 236 (e.g., by a motor, directly, or using a gear train, as shown in FIG. 36). The peristaltic pump 208 may be battery-powered, and the battery may be rechargeable wired or wirelessly. The peristaltic pump 208 may alternatively, or additionally, be powered by a power cord configured to connect to a power source. An extension tube 238 having a distal end 240 and a proximal end 242 and a lumen 244 extending therethrough is hydraulically connected to the proximal end 206 of the aspiration lumen 204 of the aspiration catheter 202 via a connector 224. The extension tube 238 may be supplied (e.g., sterile) with the aspiration catheter 202 or may be supplied separately packaged. A Touhy-Borst seal 246 mounted on the connector 224 is configured to be loosened / opened to allow insertion of a guidewire 248 through the connector 224 and the aspiration lumen 204, which may be used to track the aspiration catheter 202 through the subject's vasculature. The Touhy-Borst seal 246 can be tightened to seal the guidewire 248 and maintain hemostasis. Other types of seals, including spring-loaded, longitudinally compressible, actuatable seals, can be incorporated in place of the Touhy-Borst 246. The extension tube 238 includes a male luer 250 at its distal end 240 for connecting to a female luer 252 of the connector 224. Alternatively, as shown, the suction monitoring system 214 may be attached therebetween.The male luer 250 may include a stopcock 254 configured to rotate to select an open position (as shown) or a closed position. Alternatively, the extension tube 238 may be integral with the aspiration lumen 204 or may be permanently attached to the connector 224. In use, the compressible portion 237 of the extension tube 238 is positioned within the pressure shoe 228 of the peristaltic pump 208 such that, when the rotatable head 230 is rotated in a rotational direction 236 (e.g., via user input to the interface 256), fluid is forced from the distal end 240 to the proximal end 242 of the extension tube 238, one at a time, via compression of the compressible portion 237 by the rollers 232. In some embodiments, there are only two rollers 232. In other embodiments, there are three rollers 232. In yet other embodiments, there are four rollers 232, as shown. As described, the rollers 232 can be replaced by ridges or protrusions. The compressible portion 237 may comprise silicone tubing, polyurethane tubing, polyvinyl chloride tubing, or other compressible tubing. The compressible portion 237 may be a relatively short section that is attachable and detachable to the peripheral end of the dilation tube 238, or in other embodiments, may comprise the entire dilation tube 238 between the distal end 240 and the proximal end 242. The proximal end 242 of the dilation tube 238 may be connected to a hub 257 formed on the cap 213 of the canister 258, which may have an interior 260 and allow fluid 259 passing through the dilation tube 238 to enter the interior 260. An additional hub 262 may be provided within the canister 258 and may be left open (as shown) to allow the unfilled interior 260 to equalize to atmospheric pressure.

[0218]

[0218] In use, the distal section of the aspiration catheter 202 is inserted into the subject's vasculature so that the open distal end 205 is adjacent to or within the thrombus. Fluid containing the thrombus is then aspirated into the aspiration lumen 204 by the action of the peristaltic pump 208 and removed using the aspiration system 200. The blood vessels being treated may include peripheral blood vessels, pulmonary blood vessels such as the pulmonary artery, coronary blood vessels, or blood vessels in the subject's head or neck, including the carotid or cerebral arteries.

[0219] The suction system 200 further includes a suction monitoring system 1800 configured to provide a user with information regarding the status of the suction. The suction monitoring system 1800 functions by measuring the fluid 259 accumulated at the bottom of the interior 260 of the canister 258 at multiple points in time and thus estimating the (volumetric) flow rate of the fluid 259 exiting the lumen 244 of the extension tube 238. The suction monitoring system 1800 includes a scale 1802 (or balance) having a base 1804. A weighing platform 1806 is connected to the base 1804 and is movable relative to the base 1804 (e.g., along a vertical axis V) such that the weight of the fluid 259 accumulated at the bottom of the canister 258 outputs a signal 1808 indicative of the weight. The scale may be configured to output the signal 1808 indicative of the weight, or in some embodiments, a particular altitude (above sea level) at which the scale 1802 is located may be input into the scale 1802 so that a mass value can be output. A standard setting may assume the procedure is performed at sea level and calculate the mass accordingly. In some embodiments, scale 1802 may even include an altimeter or other sensor to automatically determine altitude so that mass can be output. Regardless, even if weight is output, the change in weight of fluid 259 over time is proportional to the change in mass of fluid 259 over time at any particular altitude. Thus, signal 1808 may indicate mass or may indicate weight while remaining within a range that allows for demonstrating the change in mass of fluid 259 over time. Thus, system 200 may predict blood loss from the patient by assessment of the total cumulative weight / mass of blood captured in canister 258. The measured weight / mass of blood may be converted to the volume (ml) of blood lost by system 200.

[0220]

[0220] Signal 1808 is transmitted to processor 1810. See also FIG. 44. Processor 1810, which may comprise a microprocessor, includes a clock that allows for the combination of time data with weight or mass values ​​from the signal. In some embodiments, scale 1802 may include a tare button or control so that the tare weight of canister 258 can be subtracted from the amount weighed by scale 1802. Thus, scale 1802 is "zeroed" and only the weight or mass of fluid 259 in canister 258 is weighed at each point in time. The sample rate at which values ​​of signal 1808 are obtained along with timestamps may range from about 0.01 Hz to about 10 kHz, or from about 0.02 Hz to about 1 kHz, or from about 1 Hz to about 100 Hz. The processed signal 1812 is output to a graphic display 1814 for viewing by a user. In some embodiments, the graphic display 1814 can display an xy graph 1816, where the x-axis represents time and the y-axis represents the weight or mass of the fluid 259 in the canister 258. In other embodiments, the graphic display 1814 can display an xy graph 1816, where the x-axis represents time and the y-axis represents the flow rate. The flow rate (FR) can be calculated from the following formula:

[0221]

[0221] FR = (W c -W p ) / (T c -T p ), where W c is the current value of the weight of fluid 259 W p is the previous value of the weight of fluid 259 T c is the current timestamp value T p is the previous timestamp value.

[0222]

[0222] In another embodiment, the flow rate (FR) can be calculated from the following formula:

[0223]

[0223] FR = (W c-W pn ) / (T c -T pn ), where W c is the current value of the weight of fluid 259 W pn is the nth previous value of the weight of fluid 259 T c is the current timestamp value T pn is the nth previous timestamp value.

[0224]

[0224] In other embodiments, the flow rate may be constructed as a moving average, such as a running or rolling average. Several types of moving averages may be used, including a simple moving average, a cumulative moving average, a weighted moving average, or an exponential moving average.

[0225]

[0225] Instead of an xy graph, a visual display comprising one or more LED lights may be used. For example, higher flow rates may be indicated by a range of green shades, while lower flow rates may be indicated by a range of red shades. Alternatively, the intensity of the light may vary in response to changes in flow rate, or changes in weight or mass. For example, the light intensity may be proportional to the measured / calculated flow rate. A loudspeaker may present the change in weight / mass over time, or the change in flow rate over time, as a continuous or continuous sound with a pitch that varies proportionally to the change in value. For example, a higher pitch indicates a higher flow rate. Alternatively, the intensity of the sound may vary (higher flow rate = higher dB).

[0226] Changes in flow rate may indicate the occurrence of an operation in the aspiration system 200. For example, a flow rate that suddenly decreases by a significant amount may indicate a clot has lodged in the aspiration lumen 204 or the lumen 244 of the dilation tube 238. In some cases, a decrease in flow rate of 90% or more may indicate a blockage. When a blockage occurs, the amount of fluid that can be aspirated and delivered to the canister 258 may be severely limited. The loudspeaker 1818 is also configured to generate an audible alarm when a threshold flow rate is crossed. The threshold flow rate can be entered into the memory 1822 of the scale 1802 using the user interface 1820. When the flow rate decreases to a value below the threshold flow rate, the loudspeaker 1818 is caused to sound an alarm. In some embodiments, the controller 215 in the peristaltic pump 208 may be connected (wired or wirelessly) to the processor 1810 and configured to activate an alarm on the loudspeaker 1818. If the flow rate increases above a threshold flow rate, the loudspeaker 1818 may be deactivated so that the alarm does not sound. Alternatively, the loudspeaker 1818 may be replaced or augmented by a visual and / or tactile alarm. A visual alarm may include one or more lights, including one or more LEDs. A tactile alarm may include a vibrating device, such as a piezoelectric, or a weight-offset rotating device.

[0227] A change in flow rate may also indicate other changes in condition, such as a rupture in one wall of the tubular member or a break in one of the connections. One of these leak conditions may result in a significant decrease in flow rate and, therefore, be identified by a change in flow rate measured by the aspiration monitoring system 1800. The system 200 may be configured to activate an alarm (e.g., via the loudspeaker 1818) when free flow of blood is detected. In other words, when the system is clearly aspirating only blood and not a clot. Thus, a measured flow rate crossing above a certain threshold stored in memory 1822, indicative of free flowing blood, may cause the controller 215 to activate an alarm.

[0228] A secondary suction monitoring system 214 including a pressure transducer 216 may be connected, for example, between the distal end 240 of the extension tube 238 and the connector 224 and / or proximal end 206 of the suction lumen 204 of the suction catheter 202. Signals from the pressure transducer 216 may be carried wirelessly or by a cable (not shown) to the controller 215. The controller 215 may include a microcontroller. The controller 215 may be located within the peristaltic pump 208 or in another component or location. Using measured pressure for control adds an additional element of safety to the system 200. Furthermore, non-functioning devices (due to leaks, faulty connections, incomplete priming, ruptures, or blockages) can be quickly identified. Unacceptably high or low pressures can also be quickly identified, protecting the motor of the peristaltic pump 208 from the risk of burning out or overheating. Data from the pressure transducer 216 and the scale 1802 can be used together to optimize or create a more accurate signal indicating aspiration flow or indicating the presence of a clot / thrombus, a blockage, a rupture, or a disconnected fluid circuit.

[0229] Foot pedal 251 is shown having a base 253 and a pedal 255 connected to base 253 and movable or actuable by application of a user's foot. Pedal 255 may be spring-loaded, depressed by application of a moment or compressive force, or alternatively may comprise a membrane switch. When activated, pedal 255 can switch on and off in some embodiments; in other embodiments, pedal 255 can be actuable when a force, pressure, or moment is applied and deactivated when no force, pressure, or moment is applied. Cable 263 carries signals from foot pedal 251 to peristaltic pump 208 via plug 269 connected to input jack 271. Pedal 255 can be activated by the user's foot to start or stop operation of peristaltic pump 208.

[0230] In other embodiments, the foot pedal 251 may be replaced with another type of switch, including, but not limited to, a toggle on / off push button or hand switch, a voice-activated switch (voice-activated, clap-activated, click-activated), a light switch (beam / light sensor for hand or foot interruption), or any other type of switch that can be activated by medical personnel. The switch may be located in a remote location (e.g., a control room) or near the treatment area. The switch may also be a sterile switch or may be sterilizable for location on the sterile field.

[0231] In some cases, activating and deactivating (turning on and off) the suction flow applied to suction lumen 204 by peristaltic pump 208 can be done by leaving peristaltic pump 208 running while a user opens and closes stopcock 254. Alternatively, a pinch valve (not shown) connected to extension tube 238 can be used to open and close lumen 244, and thus start and stop suction. The pinch valve can be actuated by a foot pedal (similar to foot pedal 251) or by a separate control (e.g., on interface 256 of peristaltic pump 208).

[0232]

[0232] After collecting the aspirated material in a blood bag, blood bottle, or canister 258, the aspirated components (blood, clot, saline, slurry, etc.) can be placed into a reinfusion device such as the Stryker ConstaVac (CBCII) Blood Conservation System or the Haemonetics OrthoPAT Orthopedic Perioperative Autotransfusion System.

[0233] In some embodiments, the blood may be cooled before being infused. In some embodiments, the blood may be heated before being infused. In some embodiments, other drugs may be added to the blood before it is inserted. In some cases, the blood may be diluted with saline to reduce viscosity or lower the hematocrit. This may result in reduced hemolysis. In some cases, the blood collected in canister 258 or coming from extension tube 238 may even be used as donor blood for infusion into another patient.

[0234] In some embodiments, additional or alternative sensors may be used to monitor flow conditions for notification to the user, including, but not limited to, Doppler sensors, infrared sensors, or laser flow detection devices. In some embodiments, an externally mounted (non-contact) Doppler sensor may be used. In some embodiments, an infrared sensor or laser flow detection device may be used around the extension tube 238. Alternative sensors (e.g., flow sensors, etc.) may be placed at several different locations along the aspiration path, including on or within the extension tube 238, either proximal or distal to the rotatable head 230 of the peristaltic pump 208.

[0235] FIG. 45 shows a forced suction system 400 comprising a suction catheter 402 with an elongate shaft 401 including a suction lumen 404 having an open distal end 405 and a proximal end 406 configured for connection to a peristaltic pump 408. The peristaltic pump 408 may be a roller pump having a base 426, a pressure shoe 428 carried by the base 426, and a rotatable head 430 rotatably connected to the base 426 and carrying two or more rollers 432a-432d. The rollers 432a-432d are arranged around a periphery 434 of the rotatable head 430. The rotatable head 430 is configured to be rotatable in at least a first rotational direction 436 (e.g., by a motor, directly, or using a gear train, as shown in FIG. 36). The peristaltic pump 408 may be battery-powered, and the battery may be rechargeable wired or wirelessly. The peristaltic pump 408 may alternatively, or additionally, be powered by a power cord configured to connect to a power source. An extension tube 438 having a distal end 440 and a proximal end 442 and a lumen 444 extending therethrough is hydraulically connected to the proximal end 406 of the aspiration lumen 404 of the aspiration catheter 402 via a connector 424. The extension tube 438 may be supplied (e.g., sterile) with the aspiration catheter 202 or may be supplied separately packaged. A Touhy-Borst seal 446 mounted on the connector 424 is configured to be loosened / opened to allow insertion of a guidewire 448 through the connector 424 and the aspiration lumen 404, which may be used to track the aspiration catheter 402 through the subject's vasculature. The Touhy-Borst seal 446 can be tightened to seal the guidewire 448 and maintain hemostasis. Other types of seals, including spring-loaded, longitudinally compressible, actuatable seals, can be incorporated in place of the Touhy-Borst 246. The extension tube 438 includes a male luer 450 at its distal end 440 for connecting to a female luer 452 of the connector 424. Alternatively, as shown, the suction monitoring system 414 may be attached therebetween.The male luer 450 may include a stopcock 454 configured to rotate to select an open position (as shown) or a closed position. Alternatively, the extension tube 438 may be integral with the aspiration lumen 404 or may be permanently attached to the connector 424. In use, the compressible portion 437 of the extension tube 438 is positioned within the pressure shoe 428 of the peristaltic pump 408 such that, when the rotatable head 430 is rotated in a rotational direction 436 (e.g., via user input to the interface 456), fluid is forced from the distal end 440 to the proximal end 442 of the extension tube 438, one at a time, via compression of the compressible portion 437 by the rollers 432. In some embodiments, there are only two rollers 432. In other embodiments, there are three rollers 432. In yet other embodiments, there are four rollers 432, as shown. As described, the rollers 432 can be replaced by ridges or protrusions. The compressible portion 437 may comprise silicone tubing, polyurethane tubing, polyvinyl chloride tubing, or other compressible tubing. The compressible portion 437 may be a relatively short section that is attachable and detachable to the peripheral end of the dilation tube 438, or in other embodiments, may comprise the entire dilation tube 438 between its distal end 440 and proximal end 442. The proximal end 442 of the dilation tube 438 may be connected to a hub 457 of a canister 458 having an interior 460 to allow fluid 459 passing through the dilation tube 438 to pass into the interior 460. An additional hub 462 in the canister 458 may be left open (as shown) to allow the uncharged interior 460 to equalize to atmospheric pressure. A filter 443 (optional) is positioned in line between the dilation tube 438 and the canister 458 to capture blood clots aspirated from the patient. The filter 443 may have a transparent sidewall to allow a physician or other medical staff to visually assess the clot, such as the size of each piece, the number of pieces, the total amount of clot (e.g., in terms of volume), or the condition of the clot or remaining clot (organized / fibrous, or soft).The buildup of thrombus in the filter 443, or lack thereof, can be used as a cue to move the open distal end 405 of the aspiration catheter 402 to a different position, or to temporarily or permanently stop treatment, or to increase or decrease the pump speed.

[0236] The suction catheter 402 further has a high-pressure infusion lumen 410 for infusing saline from a fluid source 499, for example, via a high-pressure pump 412. The tubing set 464 may include a pump cartridge 466 having a piston or bellows, or other moving element that the pump 412 can operate using an internal motor (not shown), which applies high pressure to saline from the fluid source 499 such that the saline is forced through the infusion lumen 410 of the suction catheter 402. The tubing set 464 includes a proximal end 468 having a spike 497 or other element for hydraulically connecting it to the fluid source 499. The tubing set 464 further has a distal end 470 (which may include a male luer) configured to hydraulically connect to the infusion lumen 410 via a female luer 472. The infused saline is forced through the infusion lumen 410 by the pump 412 and exits an orifice 474 at the distal end 476 of the infusion lumen 410. The infusion lumen 410 may be within a tube 478 that is substantially or completely within the shaft 401. In some embodiments, the tube 478 is attached to the inner wall of the shaft 401 only at the distal end portion 403. Thus, the free-floating nature of the remainder of the tube 478 within the aspiration lumen 404 increases the flexibility and trackability of the shaft 401. High-pressure saline is forced through the orifice 474, creating a jet. The jet is directed into the aspiration lumen 404 just proximal to the open distal end 405, which may create a Venturi effect, pushing blood or clots externally adjacent the open distal end 405 into the aspiration lumen 404. The combination of the action of peristaltic pump 408 and the jets generated by the high-pressure saline causes maceration of the thrombus and movement / flow of material (saline / blood / macerated thrombus / thrombus fragments) through suction lumen 404 from open distal end 405 to proximal end 406, through connector 424, through lumen 444 of dilation tube 438 from distal end 440 to proximal end 442, and finally into interior 460 of canister 458. Thus, thrombus within a subject's blood vessels can be macerated and removed using system 400.The vessels treated may include peripheral vessels, pulmonary vessels such as the pulmonary artery, coronary vessels, or vessels within the subject's head or neck, including the carotid or cerebral arteries.

[0237] The forced suction system 400 further includes a suction monitoring system 1800 configured to provide a user with information regarding the status of the suction. The suction monitoring system 1800 functions by measuring the fluid 459 accumulated at the bottom of the interior 460 of the canister 458 at multiple points in time and, therefore, estimating the flow rate of the fluid 459 exiting the lumen 444 of the extension tube 438. The suction monitoring system 1800 includes a scale 1802 (or balance) having a base 1804. A weighing platform 1806 is connected to the base 1804 and is movable relative to the base 1804 (e.g., along a vertical axis V) such that the weight of the fluid 459 accumulated at the bottom of the canister 458 outputs a signal 1808 indicative of the weight. The scale may be configured to output the signal 1808 indicative of the weight, or in some embodiments, a particular altitude (above sea level) at which the scale 1802 is located may be input into the scale 1802 so that a mass value can be output. In some embodiments, scale 1802 may even include an altimeter or other sensor to automatically determine altitude so that mass can be output. Regardless, even if weight is output, the change in weight of fluid 459 over time is proportional to the change in mass of fluid 459 over time at any particular altitude. Thus, signal 1808 may indicate mass or indicate weight while remaining within a range that allows for the change in mass of fluid 459 over time to be demonstrated. Thus, system 400 may predict blood loss from a patient by assessment of the total cumulative weight / mass of blood captured in canister 458. The measured weight / mass of blood may be converted to the volume (ml) of blood lost by system 400.

[0238] Signal 1808 is transmitted to processor 1810. See also FIG. 44. Processor 1810, which may comprise a microprocessor, includes a clock that allows for the combination of time data with weight or mass values ​​from the signal. In some embodiments, scale 1802 may include a tare button or control so that the tare weight of canister 458 can be subtracted from the amount being weighed by scale 1802. Thus, scale 1802 is "zeroed" and only the weight or mass of fluid 459 in canister 458 is weighed at each point in time. The sample rate at which values ​​of signal 1808 are obtained along with timestamps may range from about 0.01 Hz to about 10 kHz, or from about 0.02 Hz to about 1 kHz, or from about 1 Hz to about 100 Hz. The processed signal 1812 is output to a graphic display 1814 for viewing by a user. In some embodiments, the graphic display 1814 can display an xy graph 1816, where the x-axis represents time and the y-axis represents the weight or mass of the fluid 459 in the canister 458. In other embodiments, the graphic display 1814 can display an xy graph 1816, where the x-axis represents time and the y-axis represents the flow rate. The flow rate (FR) can be calculated from the following formula:

[0239]

[0239] FR = (W c -W p ) / (T c -T p ), where W c is the current value of the weight of fluid 459 W p is the previous value of the weight of fluid 459 T c is the current timestamp value T p is the previous timestamp value.

[0240]

[0240] In another embodiment, the flow rate (FR) can be calculated from the following formula:

[0241]

[0241] FR = (W c-W pn ) / (T c -T pn ), where W c is the current value of the weight of fluid 459 W pn is the nth previous value of the weight of fluid 459 T c is the current timestamp value T pn is the nth previous timestamp value.

[0242]

[0242] In other embodiments, the flow rate may be constructed as a moving average, such as a running or rolling average. Several types of moving averages may be used, including a simple moving average, a cumulative moving average, a weighted moving average, or an exponential moving average.

[0243]

[0243] Instead of an xy graph, a visual display comprising one or more LED lights may be used. For example, higher flow rates may be indicated by a range of green shades, while lower flow rates may be indicated by a range of red shades. Alternatively, the intensity of the light may vary in response to changes in flow rate or changes in weight or mass. For example, the light intensity may be proportional to the measured / calculated flow rate. A loudspeaker may present the change in weight / mass over time, or the change in flow rate over time, as a continuous or continuous sound with a pitch that varies proportionally to the change in value. For example, a higher pitch indicates a higher flow rate. Alternatively, the intensity of the sound may vary (higher flow rate = higher dB).

[0244] Changes in flow rate may indicate the occurrence of an operation in the forced aspiration system 400. For example, a flow rate that suddenly decreases by a significant amount may indicate a clot has lodged in the aspiration lumen 404 or the lumen 444 of the dilation tube 438. In some cases, a decrease in flow rate of 90% or more may indicate a blockage. When a blockage occurs, the amount of fluid that can be aspirated and delivered to the canister 458 may be severely limited. The loudspeaker 1818 is also configured to generate an audible alarm when a threshold flow rate is crossed. The threshold flow rate may be entered into the memory 1822 of the scale 1802 using the user interface 1820. If the flow rate decreases to a value below the threshold flow rate, the loudspeaker 1818 may sound an alarm. In some embodiments, the controller 484 on the pump 412, or a different controller on one of the other components, may be connected (wired or wirelessly) to the processor 1810 and configured to activate an alarm on the loudspeaker 1818. If the flow rate increases above a threshold flow rate, the loudspeaker 1818 may be deactivated so that the alarm does not sound. Alternatively, the loudspeaker 1818 may be replaced or augmented by a visual and / or tactile alarm. A visual alarm may include one or more lights, including one or more LEDs. A tactile alarm may include a vibrating device, such as a piezoelectric, or a weight-offset rotating device.

[0245] A change in flow rate may also indicate other changes in condition, such as a rupture in one wall of the tubular member or a break in one of the connections. One of these leak conditions may result in a significant decrease in flow rate and, therefore, be identified by a change in flow rate measured by the aspiration monitoring system 1800. The system 400 may be configured to activate an alarm (e.g., via the loudspeaker 1818) when free flow of blood is detected. In other words, when the system is clearly aspirating only blood and not a clot. Thus, a measured flow rate crossing above a certain threshold stored in memory 1822, indicative of free flowing blood, may cause the controller 484 to activate an alarm.

[0246] A secondary suction monitoring system 414 including a pressure transducer 416 may be connected, for example, between the distal end 440 of the dilation tube 438 and the connector 424 and / or proximal end 406 of the suction lumen 404 of the suction catheter 402. A signal from the pressure transducer 416 is carried over an electrical cable 480 to an input 482 of the pump 412. A controller 484 within the pump 412 is configured to control the operation of the pump 412, but may also be configured to control the operation of the peristaltic pump 408 via a cable 486 or wirelessly. The controller 484 may comprise a microcontroller. Alternatively, the controller 484 may be located within the peristaltic pump 408 or may be located in another component or location. Control using measured pressure adds an additional element of safety to the system 400. Furthermore, non-functioning devices (due to leaks, faulty connections, incomplete priming, ruptures, or blockages) can be quickly identified. Unacceptably high pressures can also be quickly identified, protecting the motor of the pump 412 from the risk of burning out or overheating. The integrity of the tubing 478 is also protected, avoiding unnaturally high pressures that could lead to, for example, rupture of the tubing 478. Data from the pressure transducer 416 and the scale 1802 can be used together to optimize or create a more accurate signal indicating aspiration flow or indicating the presence of a clot / thrombus, the presence of a blockage, the presence of a rupture, or a disconnected fluid circuit.

[0247] Female luer 452 is located distally on connector 424 from female luer 472. Thus, aspirated blood / thrombus / saline enters female luer 452 without having to contact internal irregularities 425 (in geometry, shape) within connector 424 that might otherwise cause flow resistance or trap thrombus (e.g., between tubing 478 and the interior of connector 424).

[0248] Foot pedal 451 is shown having a base 453 and a pedal 455 connected to base 453 and movable or actuable by application of a user's foot. Pedal 455 may be spring-loaded, depressible by application of a moment or compressive force, or alternatively comprise a membrane switch. When activated, pedal 455 can switch on and off in some embodiments; in other embodiments, pedal 455 can be actuable when a force, pressure, or moment is applied and deactivated when no force, pressure, or moment is applied. A first cable 461 carries signals from foot pedal 451 to pump 412 via plug 465 connected to input jack 467. A second cable 463 carries signals from foot pedal 451 to peristaltic pump 408 via plug 469 connected to input jack 471. In some embodiments, activation of pedal 455 by the user's foot initiates operation of pump 412 and simultaneously initiates operation of peristaltic pump 408. In some embodiments, activation of pedal 455 by the user's foot initiates operation of peristaltic pump 408, which then initiates operation of pump 412 a short delay after peristaltic pump 408 has been initiated. Controller 484 is programmed or programmable to impose the delay, or lack thereof. The delay is useful to ensure that some suction, or a significant amount of suction, has been applied to aspiration lumen 404 before infusing pressurized fluid (e.g., saline) through infusion lumen 410. All can be controlled by controller 484 of pump 412 in response to a signal via cable 463 from foot pedal 451. Thus, blood vessels or other vasculature near open distal end 405 are spared from infusion of fluid from the high-pressure jet, as they are instead aspirated through aspiration lumen 404.

[0249] Additionally, in some embodiments, activation of pedal 455 by the user's foot while pump 412 and peristaltic pump 408 are operating simultaneously stops operation of pump 412 and peristaltic pump 408. In other embodiments, a delay can be implemented (e.g., by controller 484) such that pump 412 is stopped, followed by a short delay before peristaltic pump 408 is stopped. The length of the described delay can be between about 0.01 seconds and about 1.00 seconds, or between about 0.10 seconds and about 0.25 seconds. Activation (on / off) of pump 412 and / or peristaltic pump 408 via foot pedal 451 allows for hands-free activation, allowing a single user to operate aspiration catheter 402 and guidewire 448 with both hands.

[0250] In other embodiments, the foot pedal 451 may be replaced with another type of switch, including, but not limited to, a toggle on / off push button or hand switch, a voice-activated switch (voice-activated, clap-activated, click-activated), a light switch (beam / light sensor for hand or foot interruption), or any other type of switch that can be activated by medical personnel. The switch may be located in a remote location (e.g., a control room) or near the treatment area. The switch may also be a sterile switch or may be sterilizable for location on the sterile field.

[0251] In some cases, activating and deactivating (turning on and off) the suction flow provided by peristaltic pump 408 to suction lumen 404 can be done by leaving peristaltic pump 408 running while a user opens and closes stopcock 454. Alternatively, a pinch valve (not shown) connected to extension tube 438 can be used to open and close lumen 444, and thus start and stop suction. The pinch valve can be actuated by a foot pedal (similar to foot pedal 451) or by another control device (e.g., on interface 456 of peristaltic pump 408 or on the interface of pump 412).

[0252] The controller 484 also monitors and controls several device safety features, including overpressure detection, air bubble detection, and vacuum or negative pressure charging. An additional pressure transducer 415 monitors the pressure (i.e., the infusion pressure) and detects the presence of air bubbles. Alternatively, or in combination, an optical device 417 can be used to detect air bubbles. In one possible embodiment, pump pressure is proportional to the current required to generate that pressure. Thus, if the current required by the pump 412 exceeds a preset limit, the controller 484 disables the pump 412 by cutting power to the pump 412. Air bubble detection can also be monitored by monitoring the current required to drive the pump 412 at a particular moment. For the pump 412 to reach high fluid pressures, there should be little or no air (which is highly compressible) in the pump 412 or the connecting system (including the aspiration lumen 404 and tubing set 464 of the aspiration catheter 402). The fluid volume is small enough that air in the system does not create pressure at the pump head. A sufficient amount of liquid is required proximally to allow a finite amount of air to flow. The controller 484 monitors the pump 412 current for a sudden downward change that may indicate air has entered the system. If the rate of decline is faster than a preset limit, the controller 484 disables the pump 412 by cutting power to the pump until the problem is corrected.

[0253]

[0253] After collecting the aspirated material in a blood bag, blood bottle, or canister 458, the aspirated components (blood, clot, saline, slurry, etc.) can be placed into a reinfusion device such as the Stryker ConstaVac (CBCII) Blood Conservation System or the Haemonetics OrthoPAT Orthopedic Perioperative Autotransfusion System.

[0254] In some embodiments, the blood may be cooled before being infused. In some embodiments, the blood may be heated before being infused. In some embodiments, other drugs may be added to the blood before it is inserted. In some cases, the blood may be diluted with saline to reduce viscosity or lower the hematocrit. This may result in reduced hemolysis. In some cases, the blood collected in canister 458 or coming from extension tube 438 may even be used as donor blood for infusion into another patient.

[0255] In some embodiments, additional or alternative sensors may be used to monitor flow conditions for notification to the user, including, but not limited to, Doppler sensors, infrared sensors, or laser flow detection devices. In some embodiments, an externally mounted (non-contact) Doppler sensor may be used. In some embodiments, an infrared sensor or laser flow detection device may be used around the extension tube 438. Alternative sensors (e.g., flow sensors, etc.) may be placed at several different locations along the aspiration path, including on or within the extension tube 438, either proximal or distal to the rotatable head 430 of the peristaltic pump 408.

[0256] FIG. 46 illustrates an alternative suction monitoring system 1900 that shares features with the suction monitoring system 1800 of FIG. 44, but is configured to meter a fluid 259, 459 contained in a canister 258, 458 by suspending the canister 258, 458 from hooks 1902, 1904 extending from a frame 1906 supported by a weighing platform 1806. The frame 1906 includes two vertical legs 1910, 1912 and a crossbar 1908 connected to each of the vertical legs 1910, 1912. The crossbar 1908 is configured to support the hooks 1902, 1904 and the canister 258, 458 (when suspended). The canister 258, 458 may include hooks, recesses, or loops configured to engage and interface with one or both of the hooks 1902, 1904.

[0257] While the foregoing describes embodiments of the present disclosure, other and further embodiments may be devised without departing from the basic scope of the present invention. Alternatively, instead of using an extension tube 238, 438 configured for use with a peristaltic pump 208, 408, the extension tube 238, 438 may include a luer connector (or other sealing connector) at its proximal end and be configured to attach to an evacuable syringe (e.g., 20 ml or 30 ml). The syringe may be hung from a hook 1902, 1904 (or equivalent), and the weight of the syringe and extension tube 238, 438 may be tared from the scale 1802. Thus, as the syringe is filled, the increase in weight / mass of aspirate collecting in the syringe is measured over time in the same manner as the contents of the canister 258, 458 are weighed. The evacuable syringe can also be replaced by a bell jar connected to a vacuum pump, with the bell jar and connecting tubing being tared from the measured weight / mass. FIG. 47 shows an aspiration system 1928 similar to the aspiration system 200 of FIG. 43, except that the peristaltic pump 208 and canister 258 are replaced by a vacuum pump 1930 and vacuum chamber 1934, or a bell jar having a base 1936 and a lid 1938 sealably disposed thereon. The vacuum pump 1930 can be operated by a controller 1999 mounted on its exterior surface 1997 or can be controllable (on / off) by a foot pedal 251. A vacuum tube 1932 connects the vacuum pump 1930 to the interior 1940 of the vacuum chamber 1934. A control valve 1948 is adjustable to control the aperture between the vacuum tube 1932 and the interior 1940 of the vacuum chamber 1934. The interior 1940 communicates with the lumen 244 of the dilation tube 238 via a proximal end 242 that is connected to a port 1942 of the vacuum chamber 1934. An adjustable valve 1946 controls the aperture between the interior 1940 of the vacuum chamber 1934 and the lumen 244 of the dilation tube 238. The vacuum pump 1930 is separately supported on a table, cart, or other support.The weight of the vacuum tube 1932 and extension tube 238 can be tared from the readout of the scale 1802 so that only the weight of fluid / clot etc. drawn into the interior 1940 of the vacuum chamber 1934 is measured over time.

[0258] Thrombosis (thrombus, blood clot) within the vascular system, including arteries, veins, and other blood vessels, is a significant risk factor for debilitating and even fatal outcomes. Aspiration systems, including aspiration catheters, include dedicated aspiration devices and forced aspiration devices configured to inject pressurized fluid, such as heparinized saline, into the distal portion of the aspiration lumen to create a greater aspiration pressure gradient, enabling maceration and removal of critical clots. While many of these aspiration systems are used in peripheral or coronary arteries, thromboembolic stroke involving the arteries of the neck and head is also a concern. Many of the arteries of the neck and head, including the cerebral arteries, basilar artery, and other nearby communicating arteries, are located significantly away from traditional insertion / puncture sites, such as the femoral and radial arteries. Because the pathways to these arteries can be highly tortuous and the vessels are often small in diameter, long, small-diameter catheters with significant distal flexibility are utilized. Many of these design criteria confound other physical requirements of aspiration catheters, such as a large diameter aspiration lumen to increase aspiration flow, or multiple lumens in forced aspiration catheters that must fit within a small diameter overall catheter shaft.

[0259]

[0259] Clogged aspiration catheters, for example by large clots, are a common concern for users. Techniques for avoiding clogging / occlusion of material within the catheter often involve quickly and aggressively advancing the aspiration catheter or gently picking at the edge of the clot to ensure that only a small piece or portion is introduced at a time, small enough to not clog or obstruct the aspiration lumen. If the device becomes clogged during use, the likelihood of accidental dislodgement of the clot downstream increases; this is called distal embolization. Because this type of aspiration procedure is often used in highly technical emergency settings, early detection of a clogged aspiration catheter for users during aspiration can contribute to the success of the procedure and clinical outcome. Some sources report that up to 50% of used aspiration catheters become clogged during use.

[0260]

[0260] A user may have difficulty determining whether there is a vacuum or negative pressure gradient in the system. For example, a user may have difficulty determining whether a vacuum or negative pressure is being applied (e.g., a vacuum source or negative pressure pump is turned on or off). Additionally, a user may have difficulty determining whether there has been a vacuum or negative pressure drop in the system, for example, because the syringe (or other vacuum source or negative pressure pump) is filling with fluid or because of a system leak. Blood is relatively opaque and can coat the walls of a syringe, making it difficult to determine when the syringe is filled. This makes it difficult to determine whether sufficient vacuum or negative pressure is being applied to the aspiration catheter. The vacuum or negative pressure level may change to an unacceptable level even before the syringe is filled. Extension or other tubing can also cause a drop in the vacuum or negative pressure gradient in the system. Kinks in certain tubing may be difficult for a user to see or identify. It is also difficult to determine whether there is an air leak in the system, which could be another cause of a drop in vacuum or negative pressure, even before the syringe is filled with aspiration fluid.

[0261] FIG. 48 shows an aspiration system 600 including an aspiration catheter 602 with an elongate shaft 601 including an aspiration lumen 604 having an open distal end 605 and a proximal end 606, configured to connect to a peristaltic pump 608. The peristaltic pump 608 may be a roller pump having a base 626, a pressure shoe 628 carried by the base 626, and a rotatable head 630 rotatably connected to the base 626 and carrying two or more rollers 632a-632d. The rollers 632a-632d are arranged around a periphery 634 of the rotatable head 630. The rotatable head 630 is configured to be rotatable in at least a first rotational direction 636 (e.g., by a motor, directly, or with a gear train, not shown). The peristaltic pump 608 may be battery-powered, and the battery may be rechargeable wired or wirelessly. The peristaltic pump 608 may alternatively or additionally be powered by a power cord (not shown) configured to connect to a power source. An extension tube 638 having a distal end 640 and a proximal end 642 and a lumen 644 extending therethrough is hydraulically connected to the proximal end 606 of the aspiration lumen 604 via a connector 624. A Touhy-Borst seal 646, as described herein, allows for the insertion of a guidewire 648 through the connector 624 and the aspiration lumen 604, which may be used to track the aspiration catheter 602 through the subject's vasculature. The Touhy-Borst seal 646 can be tightened to seal the guidewire 648 and maintain hemostasis. The extension tube 638 may include a male luer 650 at its distal end 640 for connecting to a female luer 652 on the connector 624. Male luer 650 may include a stopcock 654 configured to rotate between an open position (as shown) or a closed position. Alternatively, dilation tube 638 may be integral with suction lumen 604 or may be permanently attached to connector 624.In use, the compressible portion 637 of the dilation tube 638 is positioned within the pressure shoe 628 of the peristaltic pump 608 such that, when the rotatable head 630 is rotated in a rotational direction 636 (e.g., via user input to the interface 656), fluid is forced through the lumen 644 of the dilation tube 638 from the distal end 640 to the proximal end 642, one at a time, via compression of the compressible portion 637 by the rollers 632. In some embodiments, there are only two rollers 632. In other embodiments, there are three rollers 632. In yet other embodiments, there are four rollers 632, as shown. As described, the rollers 632 can be replaced by ridges or protrusions. The compressible portion 637, or any compressible portion described herein, can include silicone tubing, polyurethane tubing, polyvinyl chloride tubing, thermoplastic elastomer (TPE), such as Bioprene®, a registered trademark of Watson-Marlowe, Inc., Wilmington, Massachusetts, USA, or other compressible tubing. The compressible section 637 may be a relatively short section that is attachable and detachable to the peripheral end of the dilation tube 638, or in other embodiments, may include the entire dilation tube 638 between the distal end 640 and the proximal end 642. The proximal end 642 of the dilation tube 638 may be connected to a canister 658 having an interior 660 to allow fluid 659 passing through the dilation tube 638 to pass into the interior 660. The proximal end 642 of the dilation tube 638 is connected to the canister 658 by a tube clamp 657 that holds the dilation tube 638 longitudinally without compromising the patency of the lumen 644. To minimize fluid resistance at the proximal end 642 of the dilation tube, in addition to the end hole 621, there are also multiple side holes 623, similar to a sump tube. In other embodiments, the end hole 621 may be blocked, with outflow venting only through the multiple side holes 623. The side holes 623 ensure that the smallest area of ​​flow resistance within the extension tube 638 is not at the proximal end 642. The side holes 623 help prevent spurting into the canister 658.The ejection of blood is a negative factor, applying shear stress to the blood and causing hemolysis or platelet activation, thus damaging or altering the blood that may be desired for reinfusion into the patient. An additional hub 662 in canister 658 can be left open (as shown) to allow the uncharged interior 660 to equalize to atmospheric pressure.

[0262] Because the suction catheter 602 is configured to be inserted into arteries that may supply vital organs (e.g., the heart, brain), tight control of flow through the catheter allows for a higher level of safety. A recognition system is provided to ensure that the suction catheter 602 is used only with the peristaltic pump 608 and infusion pump 612 and not with alternative devices that do not have the same level of control over suction and infusion. An identification circuit 619 within the peristaltic pump 608 is connected to the controller 684 (e.g., via cable 686) and electrically connects to the first port 611 and the second port 613. The extension tube 638 may include a first tether 690 having a first identification module 607 configured to plug into or otherwise be secured in close proximity to the first port 611. Additionally or alternatively, the suction catheter 602 may include a second tether 688 having a second identification module 609 configured to plug into or otherwise be secured in close proximity to the second port 613. The controller 684 is configured to allow operation of the infusion pump 612 and / or the peristaltic pump 608 to occur only if one or both of the identification modules 607, 609 are identified as the correct components (e.g., correct model, correct size, correct clinical application) by the identification circuit 619. Thus, the pumps 612, 608 are enabled or disabled by the controller 684 depending on information provided by the identification modules 607, 609. In some embodiments, one or both of the identification modules 607, 609 include an RFID (radio frequency identification) chip and an identification circuit 619 configured to provide power to the RFID chip to receive and read data. In some embodiments, the identification circuit 619 may be further configured to write to the RFID chip. In other embodiments, one or both of the identification modules 607, 609 comprises a resistor and an identification circuit 619 configured to read the resistance of the resistor. For example, the resistor may complete a partial Wheatstone bridge mounted on the identification circuit 619.

[0263] The suction catheter 602 further has a high-pressure infusion lumen 610 for infusing saline from a fluid source 679, for example, via a high-pressure pump 612. The tubing set 664 may include a pump cartridge 666 having a piston or bellows or other moving element that the pump 612 can operate using an internal motor 691, thus pressurizing saline or other fluid from the fluid source 679 at a significantly high pressure so that the saline is forced through the infusion lumen 610 of the suction catheter 602. The tubing set 664 includes a proximal end 668 having a spike 689 or other element for hydraulically connecting it to the fluid source 679. The tubing set 1464 further has a distal end 670 (which may include a male luer) configured to hydraulically connect to the infusion lumen 610 via a female luer 672. Infused saline is forced by pump 612 through infusion lumen 610 and exits an orifice 674 in a hollow end portion 675 connected to the distal end 676 of infusion tubing 678, which contains infusion lumen 610. Tube 678 may be substantially or completely within shaft 601. In some embodiments, tube 678 is attached to the inner wall of shaft 601 only at distal end portion 603. Thus, the free-floating nature of the remainder of tube 678 within aspiration lumen 604 enhances the flexibility and trackability of shaft 601. High-pressure saline is forced through orifice 674, creating a jet, or jets, or multiple jets. The jets are directed into aspiration lumen 604 just proximal to open distal end 605, which can create a Venturi effect, pushing blood or clots externally adjacent open distal end 605 into aspiration lumen 640. The combination of the action of the peristaltic pump 608 and the jets generated by the high pressure saline causes maceration of the thrombus and movement / flow of material (saline / blood / macerated thrombus / thrombus fragments) through the suction lumen 604 from the open distal end 605 to the proximal end 606, through the connector 624, through the lumen 644 of the extension tube 638 from the distal end 640 to the proximal end 642, and finally into the interior 660 of the canister 658.Thus, thrombus in a subject's blood vessels can be macerated and removed using system 600. The blood vessels may include peripheral blood vessels, coronary blood vessels, or blood vessels in the subject's head or neck, including the carotid, cerebral, basilar, and communicating arteries. A suction monitoring system 614 including a pressure transducer 616 may be connected, for example, between the distal end 640 of the extension tube 638 and the connector 624 and / or proximal end 606 of the suction lumen 604 of the suction catheter 602. The suction monitoring system 614, or any of the others described herein, may include any of the features described in connection with the suction monitoring system described in U.S. Patent Application No. 2017 / 0056032 to Look et al., filed August 23, 2016, and published March 2, 2017. A signal from the pressure transducer 616 is carried over an electrical cable 680 to an input 682 of the pump 612. A controller 684 within pump 612 is configured to control the operation of pump 612, including motor 691, but controller 684 may also be configured to control the operation of peristaltic pump 608 via cable 686 or wirelessly. Controller 684 may include a microcontroller. Alternatively, controller 684 may be located within peristaltic pump 608 or elsewhere. Control using the measured pressure signal from pressure transducer 616 adds an additional element of safety to system 600. Furthermore, non-functioning devices (due to leaks, imperfect connections, imperfect priming, ruptures, or blockages) can be quickly identified. Unacceptably high pressures can also be quickly identified, protecting motor 691 of pump 612 from the risk of burning or overheating. The integrity of tubing 678 is also protected, avoiding unnaturally high pressures that could lead to, for example, rupture.

[0264] The female luer 652 of the aspiration catheter 602 is located distally on the connector 624 from the female luer 672. Thus, the aspirated blood / thrombus / saline enters the female luer 652 without having to contact any internal irregularities 625 (in geometry, shape) within the connector 624 that might otherwise cause flow resistance or trap thrombus (e.g., between the tubing 678 and the interior of the connector 624).

[0265] Foot pedal 651 has a base 653 and a pedal 655 connected to base 653 and movable or actuable by application of a user's foot. Pedal 655 may be spring-loaded, depressible by application of a moment or compressive force, or alternatively comprise a membrane switch. When activated, pedal 655 can switch on and off in some embodiments; in other embodiments, pedal 655 can be actuable when a force, pressure, or moment is applied and deactivated when no force, pressure, or moment is applied. A first cable 661 carries signals from foot pedal 651 to pump 612 via a plug 665 connected to input jack 667. A second cable 663 carries signals from foot pedal 651 to peristaltic pump 608 via a plug 669 connected to input jack 671. In some embodiments, activation of pedal 655 by the user's foot initiates operation of pump 612 and simultaneously initiates operation of peristaltic pump 608. In some embodiments, activation of pedal 655 by the user's foot initiates operation of peristaltic pump 608, which then initiates operation of pump 612 a short delay after peristaltic pump 608 has been initiated. The delay is useful to ensure that some suction or a significant amount of suction has been applied to aspiration lumen 604 before infusing pressurized fluid (e.g., saline) through infusion lumen 610. Thus, blood vessels or other vasculature near open distal end 605 are spared from infusion of fluid from the high-pressure jet, as they are instead aspirated through aspiration lumen 604.

[0266] Additionally, in some embodiments, activation of pedal 655 by the user's foot while pump 612 and peristaltic pump 608 are operating simultaneously stops operation of pump 612 and peristaltic pump 608. In other embodiments, a delay can be implemented, for example, such that pump 612 is stopped followed by a short delay in stopping peristaltic pump 608. The length of the described delay can be between about 0.01 seconds and about 1.00 seconds, or between about 0.10 seconds and about 0.25 seconds. Activating (on / off) pump 612 and / or peristaltic pump 608 via foot pedal 651 allows for hands-free activation, allowing a single user to operate suction catheter 602 and guidewire 648 with both hands. The location of foot pedal 651 can be tactilely located with the user's foot while maintaining visual contact with the patient and / or any monitors or other medical personnel.

[0267] In other embodiments, the foot pedal 651 may be replaced with another type of switch, including, but not limited to, a toggle on / off push button or hand switch, a voice-activated switch (voice-activated, clap-activated, click-activated), a light switch (beam / light sensor for hand or foot interruption), or any other type of switch that can be activated by medical personnel. The switch may be located in a remote location (e.g., a control room) or near the treatment area. The switch may also be a sterile switch or may be sterilizable for location on the sterile field.

[0268] In some cases, activating and deactivating (turning on and off) the suction flow applied to the suction lumen 604 by the peristaltic pump 608 can be done by leaving the peristaltic pump 608 running while a user opens and closes the stopcock 654. In other embodiments, the stopcock can be replaced with a pinch valve (not shown) to open or compress the extension tube 638. The pinch valve can be operated by a foot switch or push button (on / off).

[0269] The controller 684 also monitors and controls several device safety features, including overpressure detection, air bubble detection, and vacuum or negative pressure charging. An additional pressure transducer 615 mounted on the connector 624 monitors the pressure (i.e., the infusion pressure) and detects the presence of air bubbles. Alternatively, or in combination, an optical device 617 can be used to detect air bubbles. In one possible embodiment, the pump pressure is proportional to the current required by the pump 612 to generate that particular pressure. Thus, if the current required by the pump 612 exceeds a preset limit, the controller 684 disables the pump 612 by cutting power to the pump 612. Air bubble detection can also be monitored by monitoring the current required to drive the pump 612 at a particular moment. In order for the pump 612 to reach high fluid pressures, there should be little or no air (which is highly compressible) in the pump 612 or the connection system (including the aspiration lumen 604 of the aspiration catheter 604 and the tubing set 664). The fluid volume is small enough that air in the system does not create pressure at the pump head. A sufficient amount of liquid is required proximally to allow a finite amount of air to flow. The controller 684 monitors the pump 612 current for a sudden downward change that may indicate air has entered the system. If the rate of decline is faster than a preset limit, the controller 684 disables the pump 612 by cutting power to the pump until the problem is corrected.

[0270] 48 is shown as having pressurized fluid infusion via infusion lumen 610. However, in other embodiments of the aspiration system 600, the aspiration catheter 602 is replaced by a standard aspiration catheter that does not have an infusion lumen.

[0271] Instead of collecting the aspirated material in a blood bag, blood bottle, or canister 658, the aspirated components (blood, clot, saline, slurry, etc.) can be placed in a reinfusion device, such as the Stryker ConstaVac (CBCII) Blood Conservation System or the Haemonetics OrthoPAT Orthopedic Perioperative Autotransfusion System. In some embodiments, the canister 658 itself may comprise the reinfusion device. Returning at least a portion of the aspirated blood to the patient by reinfusion helps reduce blood loss, which is one of the drawbacks inherent to aspiration.

[0272] In some embodiments, the blood may be cooled before being infused. In some embodiments, the blood may be heated before being infused. In some embodiments, other drugs may be added to the blood before it is inserted. In some cases, the blood may be diluted with saline to reduce viscosity or lower the hematocrit. This may result in reduced hemolysis. In some cases, the blood collected in canister 658 or coming from extension tube 638 may even be used as donor blood for infusion into another patient.

[0273] In some embodiments, additional or alternative sensors may be used to monitor flow conditions for notification to the user, including, but not limited to, Doppler sensors, infrared sensors, or laser flow detection devices. In some embodiments, an externally mounted (non-contact) Doppler sensor may be used. In some embodiments, an infrared sensor or laser flow detection device may be used around the extension tube 638. Alternative sensors (e.g., flow sensors, etc.) may be placed at several different locations along the aspiration path, including on or within the extension tube 638, either proximal or distal to the rotatable head 630 of the peristaltic pump 608.

[0274] 49 illustrates an aspiration catheter 700 having an elongate shaft 702 with a radiopaque marker band 704 attached to a distal end 706 of the shaft 702. The shaft 702 defines an aspiration lumen 708 with an open distal end 710. An infusion tube 712 having a distal end 714 is capped off with a microfabricated cap 716. The microfabricated cap 716 has an inner cylindrical cavity 718 configured to be positioned over the distal end 714 of the infusion tube 712. An outer cylindrical surface 720 of the distal end 714 of the infusion tube 712 is sealingly connected to the microfabricated cap 716 at the inner cylindrical cavity 718, such that the infusion lumen 722 of the infusion tube 712 is closed, sealed, and resistant to high pressure at the distal end 714. The outer cylindrical surface 720 may be connected to the micromachined cap 716 at the inner cylindrical cavity 718 by at least one of adhesive, epoxy, welding (e.g., ultrasonic welding or fusing of other materials), or solvent. Alternatively, a circumferential seal (a thin elastomeric ring) may be inserted between the outer cylindrical surface 720 and the micromachined cap 716 at the inner cylindrical cavity 718 to create a seal and friction fit. The micromachined cap 716 may comprise several different materials, including polymers or metals. The micromachined cap 716 may be constructed by several different processes, including micromachining, micro-injection molding, three-dimensional printing, photolithography, shadow masking, etching, or microforming. These processes include additive and subtractive processes. The orifice 730 is formed in the wall 732 of the inlet tube 712 and has a similar function to the orifice 674 of FIG. 48 . Because the distal end 714 of the infusion tube 712 is sealed, high pressure fluid is forced out of the orifice 730 and into the aspiration lumen 708 (arrow).

[0275] The outer surface 724 of the infusion tube 712 is connected to the inner surface 726 of the aspiration lumen 708 with adhesive 728 (or epoxy, or other bonding means). The infusion tube 712 is connected in a specific rotational orientation relative to the aspiration lumen 708 so that the orifice 730 faces the opposite surface 734 within the aspiration lumen 708. The unconnected section 736 extends proximally a significant portion of the length of the aspiration catheter 700, thus allowing for improved flexibility and trackability. The center of the orifice 730 may be located a distance d2, e.g., between about 0.05 mm and about 10.00 mm, from the proximal end of the micromachined cap 716 so that the jet emanating from the orifice 730 passes through the micromachined cap 716. The center of the orifice 730 is located a distance d1 from the open distal end 710 of the aspiration lumen 708 so that the distal end of the micromachined cap 716 does not extend from the aspiration lumen 708. However, in some embodiments, the micro-fabricated cap may be configured to extend from the suction lumen 708 as long as it does not have sharp leading features.

[0276] 50 illustrates an aspiration catheter 740 having an elongated shaft 742 with a radiopaque marker band 744 attached to a distal end 746 of the shaft 742. The shaft 742 defines an aspiration lumen 748 with an open distal end 750. An infusion tube 752 having a distal end 754 is capped off with a micro-machined cap 756. The micro-machined cap 756 has an inner cylindrical cavity 758 configured to be positioned over the distal end 754 of the infusion tube 752. An outer cylindrical surface 760 of the distal end 754 of the infusion tube 752 is sealingly connected to the micro-machined cap 756 at the inner cylindrical cavity 758 such that the infusion lumen 762 of the infusion tube 752 is closed, sealed, and resistant to high pressures at the distal end 754. A reinforcing ring 795 is attached to the infusion lumen 762 of the infusion tube 752 at its distal end 754 to reinforce the distal end 754 and enable a stronger seal. The reinforcing ring 795 may also be configured to enable a friction-fit seal. The reinforcing ring may comprise a high-strength metallic material, such as stainless steel, or a hard polymer. The outer cylindrical surface 760 may be connected and / or sealed to a micromachined cap 756 at the inner cylindrical cavity 758 by any of the methods or materials described in connection with the aspiration catheter 700 of FIG. 49 . The micromachined cap 756 may comprise any material and may be formed by any of the processes described in connection with the micromachined cap 716 of FIG. 49 . An orifice 770 is formed in the wall 772 of the infusion tube 752 and functions similarly to the orifice 674 of FIG. 48 . Because the distal end 754 of the infusion tube 752 is sealed, pressurized fluid is forced out of the orifice 770 and into the aspiration lumen 748.

[0277] An outer surface 764 of the infusion tube 752 is connected to an inner surface 766 of the aspiration lumen 748 with adhesive 768 (or epoxy, or other bonding means). The infusion tube 752 is connected in a specific rotational orientation relative to the aspiration lumen 748 so that the orifice 770 faces an opposing surface 774 within the aspiration lumen 748. The adhesive 768 connection extends proximally a significant portion of the length of the aspiration catheter 740.

[0278] 51 shows an aspiration catheter 701 having an elongated shaft 703 with a radiopaque marker band 705 attached to the distal end 707 of the shaft 703. The shaft 703 defines an aspiration lumen 709 with an open distal end 711. An infusion tube 713 having a distal end 715 is capped off with a micro-machined cap 717. The distal end 715 is necked down from the remainder of the infusion tube 713 by a heating and / or tension-drawing process to create a smaller outer diameter for the distal end 715. The micro-machined cap 717 has an inner cylindrical cavity 719 configured to be positioned over the reduced diameter distal end 715 of the infusion tube 713. The outer cylindrical surface 721 of the distal end 715 of the infusion tube 713 is sealingly connected to the micromachined cap 717 at the inner cylindrical cavity 719, such that the infusion lumen 723 of the infusion tube 713 is closed and sealed at the distal end 715, resisting high pressure. The smaller diameter of the distal end 715 and the inner cylindrical cavity 719 allows for a relatively high-strength connection, thereby increasing the hoop strength of the distal end 715. The outer cylindrical surface 721 may be connected and / or sealed to the micromachined cap 717 at the inner cylindrical cavity 719 by any of the methods or materials described in connection with the aspiration catheter 700 of FIG. 49. The micromachined cap 717 may comprise any material and may be formed by any of the processes described in connection with the micromachined cap 716 of FIG. 49. An orifice 731 is formed in the wall 733 of the infusion tube 713 and functions similarly to the orifice 674 of FIG. 48. Because the distal end 715 of the infusion tube 713 is sealed, the pressurized fluid is forced out of the orifice 731 and into the aspiration lumen 709 .

[0279] The outer surface 725 of the infusion tube 713 is not connected to the inner surface 727 of the aspiration lumen 709. Instead, the micromachined cap 717 is connected to the inner surface 727 with adhesive 729 (or epoxy, or other bonding means). The unconnected section 737 of the infusion tube 713 extends proximally a significant portion of the length of the aspiration catheter 701, thus allowing for increased flexibility and trackability. The micromachined cap 717 is connected in a manner that holds the infusion tube 713 in a specific rotational orientation relative to the aspiration lumen 709, so that the orifice 731 is oriented toward the opposing surface 735 within the aspiration lumen 709.

[0280] 52 shows an aspiration catheter 741 having an elongated shaft 743 with a radiopaque marker band 745 attached to a distal end 747 of the shaft 743. The shaft 743 defines an aspiration lumen 749 with an open distal end 751. An infusion tube 753 having a distal end 755 is capped off with a microfabricated cap 757. The microfabricated cap 757 has an inner cylindrical cavity 759 including a proximal portion 799 configured to be disposed over the distal end 755 of the infusion tube 753. An outer cylindrical surface 761 of the distal end 755 of the infusion tube 753 is sealingly connected to the microfabricated cap 757 at the inner proximal portion 799 of the cylindrical cavity 759, such that the infusion lumen 763 of the infusion tube 753 is sealed and resistant to high pressure. The outer cylindrical surface 761 may be connected and / or sealed to a microfabricated cap 757 at a proximal portion 799 of the inner cylindrical cavity 759 by any of the methods or materials described in connection with the suction catheter 700 of FIG. 49 . The microfabricated cap 757 may comprise any material and may be formed by any of the processes described in connection with the microfabricated cap 716 of FIG. 49 . An orifice 771 is an outlet for a distal portion 797 of the inner cylindrical cavity 759 that communicates with the proximal portion 799. While the inner cylindrical cavity 759 of FIG. 52 has a curved shape, it may instead form an L-shape or be angled at a 45° angle relative to the longitudinal axis of the suction catheter 741. The angle may vary between 45° and 135°. The orifice 771 is formed in a wall 773 of the microfabricated cap 757 and has a similar function to the orifice 674 of FIG. 48 . The high pressure fluid is forced through the inner cylindrical cavity 759 and out the orifice 771 into the aspiration lumen 749 because the distal end 755 of the infusion tube 753 is sealed.

[0281] The outer surface 765 of the infusion tube 753 is connected to the inner surface 767 of the aspiration lumen 708 with adhesive 769 (or epoxy, or other bonding means). The infusion tube 753 is connected in a specific rotational orientation relative to the aspiration lumen 749 so that the orifice 771 faces the opposing surface 775 of the aspiration lumen 749. The unconnected section 777 extends proximally a significant portion of the length of the aspiration catheter 741, thus allowing for improved flexibility and trackability. One or more of the individual features of the aspiration catheters 700, 740, 701, and 741 of FIGS. 49-52 can be rearranged to create other novel embodiments. Each of the individual features allows for the fabrication of a small-diameter aspiration catheter capable of tracking distal vasculature, such as that of the head and neck, while also providing aspiration, including high-pressure forced infusion.

[0282] 53-56 illustrate an insertable infusion tube 920 and a method for using it on a patient. For simplicity, the patient is not shown, and the device is shown in a straight configuration; however, during use, the device will typically be tracked through the bends in the patient's vasculature. In FIG. 53, a microcatheter 924 is configured to track the patient's neurovasculature, including the Circle of Willis and the cerebral arteries. The microcatheter 924 may be incorporated as a component of the aspiration system 922 (FIGS. 54-56) or may be a standard microcatheter purchased separately by the user. The microcatheter 924 comprises a shaft 926 having a proximal end 928 and a distal end 930, and a lumen 932 extending through the shaft 926. A luer hub 934 (e.g., a female luer connector) is sealingly attached to the proximal end 928 of the shaft 926. The microcatheter 924 may have a distal radiopaque marker (not shown) applied in a manner similar to the radiopaque marker bands 704, 744, 705, and 745 of the aspiration catheters 700, 740, 701, and 741 of FIGS. 49-52. The connector 936 includes a male luer 938 for connecting to the luer hub 934 and may include a valve 940, which may include a Touhy-Borst or equivalent. The side port 942 of the connector 936 may include a female luer for connecting to the male luer 650 of the dilation tube 638 of the system 600, which is described in detail in connection with FIG. 48. In FIG. 53, the user tracks the microcatheter 924 over the guidewire 944 to a blood vessel that is the region of interest. In some cases, the region of interest may be a cerebral artery or one of other nearby arteries where a thrombus 946 (FIG. 54) is causing a thromboembolic stroke in the patient.

[0283] In FIG. 54 , the user removes the guidewire 944 and inserts the insertable infusion tube 920 through the Touhy-Borst 940, into the connector 936, and into the lumen 932 of the microcatheter 924. The insertable infusion tube 920 may include a micromachined cap 948, as described in any of the embodiments of FIGS. 49-52 , or may include alternative configurations. However, the insertable infusion tube 920 at least comprises a high-strength hollow tube 952, which may include stainless steel, nickel-titanium alloy, polyimide, or other high-strength material having sufficient column strength to be inserted through the lumen 932 of the microcatheter 924. The micromachined cap 924 includes an orifice 950 configured to provide a jet of pressurized fluid, similar to the orifice 771 of the micromachined cap 757 of FIG. 52 . In FIG. 55 , the user further advances the insertable infusion tube 920 through the lumen 932 of the microcatheter 924 toward the distal end 930. The stop 954 is connected to the outside of the high-strength hollow tubing 952 and has a front surface 956 configured to abut a proximal surface 958 of the connector 936 when the center of the orifice 950 is located a preferred distance (e.g., d1, as in FIG. 49 ) from the distal end of the microcatheter 924. The insertable infusion tube 920 may be realized in different models, each having different lengths between the front surface 956 and the center of the orifice 950, each configured to be used with a particular length of microcatheter 924 or a particular model of microcatheter 924, or a particular microcatheter 924 model / connector 936 model combination. In some embodiments, the connector 936 may be a component of the insertable infusion tube 920 and may be permanently sealed and connected to the high-strength hollow tubing 952 at the proximal region, in place of the Touhy-Borst 940. Thus, the connection of the male luer 938 to the luer hub 934 realizes a longitudinal stop that controls the d1 distance.

[0284] Due to the small diameter and tortuosity of blood vessels, it may not always be possible to track the aspiration catheter 602 with high-pressure infusion forced aspiration capability (FIG. 48) into the neurovasculature. Therefore, the insertable infusion tube 920 allows the microcatheter 924 to be converted into a forced aspiration catheter. Forced aspiration can therefore occur at very distal locations, and in locations distal to significant bends where a microcatheter is usually the preferred means of access. The small-diameter insertable infusion tube 920 can be inserted through the lumen 932 of the microcatheter 924 after the microcatheter 924 has been inserted into the region of interest. In alternative procedures and embodiments of the system, the microcatheter 924 inserted over the guidewire 944 may be replaced by a flow-directing catheter having a lumen configured for placement of the insertable infusion tube 920 inserted into the region of interest without a guidewire.

[0285]

[0285] Figure 57 illustrates a particular distal configuration of the distal end 913 of the insertable infusion tube 920. This configuration allows the micromachined cap 948 and orifice 950 to be controllably and repeatedly inserted through the lumen 932 of the microcatheter 924, thereby automatically orienting the orifice so that one or more jets emanating from the orifice 950 (i.e., one or more orifices 950) are directed against the opposing wall 929 within the lumen 932 of the microcatheter 924. The micromachined cap 948 has a distal taper 960, which may include a fillet or bevel or other type of lead-in feature. The purpose of the distal taper 960 is to facilitate insertion into the connector 936, luer hub 934, or lumen 932 (Figure 54), and to facilitate advancement of the micromachined cap 948 through the lumen 932, especially when the shaft 926 is in a tortuous condition. The splined loop 962 is connected to the micromachined cap 948 and may be formed from a wire such as stainless steel or cobalt-chromium-nickel-molybdenum, or may comprise a superelastic material such as a nickel-titanium alloy. The splined loop 962 is configured to have a diameter slightly smaller than, equal to, or slightly larger than the diameter of the lumen 932 of the microcatheter 924. Referring to FIG. 58 , a first end 921 of the splined loop 962 is connected to a circumferential groove 923 in the micromachined cap 948. A gap 925 is present between the first end 921 and the second end 927 of the splined loop 962, allowing space for the two ends 921, 927 to approach each other, such that stress applied to the splined loop 962 from, for example, the wall around the lumen 932 of the microcatheter 924 will force the diameter of the splined loop 962 to decrease. The rotational orientation between the spline loop 962 and the micromachined cap 948 is fixed relative to each other (by connecting the first end 921 to the groove 923), so that the orifice 950 remains directed toward the opposite wall 929 within the lumen 932.Spline loop 962 is positioned at a different longitudinal position than orifice 950 on micro-machined cap 948, and therefore spline loop 962 does not block or deflect the jet emanating from orifice 950. In this embodiment, spline loop 962 is slightly distal to orifice 950, but in other embodiments, it may be positioned proximally instead. In other alternative embodiments, spline loop 962 (or any similar structure) may actually be used to at least somewhat deflect the jet emanating from orifice 950, for the purpose of changing the shape or direction of the jet, such as, for example, deflecting the jet at least partially proximally longitudinally. Thus, in these alternative embodiments, it may actually be desirable to position spline loop 962 at approximately the same longitudinal position as orifice 950.

[0286] In FIG. 59, the splined loop 962 has been replaced by a splined ring 933 that is attached to a high-strength hollow tube 952 in place of the micro-machined cap 948. The splined ring 933 is formed from a flat wire (such as stainless steel or a nickel-titanium alloy) or a stiff polymer strip (such as polyimide or another stiff polymer) and is shaped like the number "6," extending between a first end 935 and a second end 937. The first loop portion 939 is configured to extend around the high-strength hollow tube 952 for connection thereon, and the second loop portion 941 serves the same purpose as the splined loop 962 in FIGS. 57-58 to guide the micro-machined cap 948 and rotate and direct the orifice 950 into the lumen 932. Alternatively, other spline shapes may be used that help maintain the micromachined cap 948 against one wall of the lumen 932 and / or help resist rotation between the shaft 926 of the microcatheter 924 and either the high-strength hollow tube 952 or the micromachined cap 948 (either of the two includes the orifice 950). The spline loop 962 or spline ring 933, respectively, may be made from a radiopaque material or may include a radiopaque material as a base or a plating or coating. Thus, it is easier to visualize the movement of the orifice 950 down the lumen 932 of the microcatheter 924 with x-ray or fluoroscopy during the procedure. The micromachined cap 948 may also, or instead, include a radiopaque material or a radiopaque coating or plating. The insertable infusion tube 920 in the presented embodiment is configured to be removable from the lumen 932 of the microcatheter 924 so that the microcatheter 924 can then be used for one of its other functions, such as delivering an embolic coil or embolic material, a drug, exchanging the guidewire 944, or aspirating through the empty lumen 932. In an alternative embodiment, the orifice 950 in the micromachined cap 948 can be used to infuse drugs or other materials into the vasculature, for example, by preventing or preventing vacuum or negative pressure on the proximal end of the lumen 932.

[0287] 60-63 illustrate a method for treating a patient using the aspiration system 600 of FIG. 48, using the aspiration catheter 602, or any of the alternative aspiration catheters 700, 740, 701, 741. Alternatively, this method may be accomplished using the aspiration system 922, or using an insertable infusion tube 920 with a standard single-lumen catheter, such as a microcatheter 924, guide catheter, or guide sheath (long sheath). All of these systems may utilize the pump 612 and peristaltic pump 608 described in FIG. 48. In FIG. 60, the aspiration catheter 602 is tracked (e.g., using a guidewire 648) within a blood vessel 943 and advanced so that the open distal end 605 is adjacent the proximal end 945 of a thrombus 947. In some cases, suction utilizing high-pressure infusion from pump 612 through tubing set 664 combined with a distal-to-proximal flow impulse imparted by peristaltic pump 608 to dilation tubing 638 is not sufficient to draw thrombus 947 sufficiently into open distal end 605 and aspiration lumen 604 so that it can be macerated and aspirated. Sometimes, this is due to the space 949 distal to thrombus 947 acting as a relative vacuum, pulling the thrombus with force (e.g., distally, away from aspiration catheter 602), making it difficult to aspirate. While blood vessel 943 is shown in a relatively normal state, it is possible that the vessel has collapsed due to a lack of blood pressure caused by occlusion by thrombus 947. In other cases, some of the thrombus 947 may have distinct solid or semi-solid portions that impede the ability to flow in a distal-to-proximal direction.

[0288] A user may encounter this condition while attempting to achieve aspiration via operation of pump 612 and peristaltic pump 608, and aspiration catheter 602 is inserted and advanced into blood vessel 943 as shown in FIG. 60. The user may then use techniques with aspiration system 600 to alleviate the substantially no flow condition. In FIG. 61, the user advances aspiration catheter 602 so that the open distal end 605 of aspiration lumen 604 is distal to thrombus 947. Advancement of open distal end 605 of aspiration catheter 602 through thrombus 947 can be accomplished without the use of a guidewire 648, although in certain instances, a guidewire 648 must be used to cannulate and then track aspiration catheter 602 through thrombus 947.

[0289] In FIG. 62 , while peristaltic pump 608 is not activated, a user activates pump 612 to inject fluid. Thus, pressurized fluid (e.g., heparinized saline or saline mixed with a thrombolytic agent) is infused through infusion lumen 610 of tube 678, through orifice 674, into suction lumen 604, and then out open distal end 605 (arrow) and into space 949 of blood vessel 943. This occurs because, without suction through suction lumen 604, stopped peristaltic pump 608 acts as a closed valve, causing one of rollers 632 to compress compressible portion 637 of dilation tube 638. Injection of fluid increases the fluid volume in space 949 and, by so doing, can also increase its internal pressure, thus neutralizing the previous relative vacuum effect caused in space 949. There is now flowable material in space 949, so suction using peristaltic pump 608 in conjunction with pump 612 can begin to macerate and aspirate thrombus 947 (by now turning on peristaltic pump 608). Aspiration catheter 602 can also be retracted as shown in FIG. 63 to make better contact with thrombus 947 and increase the percentage of thrombus 947 that is aspirated. This can continue until all, or at least a clinically significant portion, of thrombus 947 has been aspirated.

[0290] Returning to FIG. 62, in certain cases, such as a thromboembolic stroke, downstream tissue may not receive sufficient flow due to an obstruction caused by a thrombus 947. A user can route fluid from a fluid source 679 through a cooling system, such as a heat exchanger or thermoelectric cooler 951 (FIG. 48), which tubing set 664 can operate, thereby cooling the fluid. Additionally, an extracorporeal circuit 953 (FIG. 62) can be attached to tubing set 664, such that blood removed from the patient (e.g., via a femoral artery, femoral vein, or jugular sheath 955) is added to the fluid from the fluid source 679, resulting in some oxygenated blood being infused into space 949, some of which may potentially provide oxygen or nutrients to downstream tissue. The cooled fluid (saline, blood, or saline and blood) can further reduce metabolic demand by actively cooling downstream tissue. The inventors have demonstrated that using a pump 612 utilizing a removable cartridge with a piston, hemolysis can be maintained at acceptably low levels during this type of injection and during mixing of the injected saline with the blood, from a mixture containing about 10% blood to a mixture containing about 80% blood.

[0291] 64-65 illustrate a method for treating a patient using the aspiration system 600 of FIG. 48, but incorporating an aspiration catheter 957 having a translatable infusion tube 959. The aspiration catheter 957 has an elongated shaft 963 having an aspiration lumen 965 with a proximal end 971 and an open distal end 961. The translatable infusion tube 959 has an infusion lumen 973 having a proximal end 975 and a distal end 977. The distal end 977 is connected to a micromachined cap 979 having an orifice 981 such that pressurized fluid infused through the infusion lumen 973 exits through the orifice 981, similar to the orifice 771 of FIG. 52. At a sufficiently high infusion pressure, the fluid can be expelled from the orifice 981 in a jet. Alternatively, the distal end 977 of the infusion lumen 973 may be blocked or capped, or there may be an orifice formed in the wall of the infusion tube 959, as in FIGS. 49-51. The pump 612 and peristaltic pump 608 described in FIG. 48 can be utilized. In FIG. 64, the aspiration catheter 957 is tracked (e.g., using a guidewire 648) into the blood vessel 943 and advanced so that the open distal end 961 is adjacent the proximal end 945 of the thrombus 947. A proximal female luer connector 983 is connected to the infusion lumen 973 and configured to connect to the male luer / distal end 670 of the tubing set 664. A filter 985 can be inserted between the female luer connector 983 and the male luer 670 to filter particles (FIG. 65). The filter has a proximal female luer 987 and a distal male luer 989. The filter 985 may be used with any of the embodiments described herein in which fluid may be injected (intentionally or unintentionally) into a patient's bloodstream.

[0292] As discussed, in some cases, suction utilizing high-pressure infusion from pump 612 through tubing set 664 combined with a distal-to-proximal flow impulse imparted by peristaltic pump 608 to dilation tube 638 is not sufficient to draw thrombus 947 sufficiently into open distal end 961 and suction lumen 965 for maceration and aspiration. Rigid tube 991 can be coaxially connected onto infusion tube 959 at its proximal length, or the infusion tube 959 itself can be made proximally rigid. The rigid tube 991 and / or female luer connector 983 and / or attached filter 985 can be grasped by the user to allow the user to sequentially advance the rigid tube 991 and infusion tube 959 distally, causing micromachined cap 979 and orifice 981 to be displaced distally through thrombus 947 and into space 949 distal to thrombus 947. In some cases, it may be sufficient to move distally to the distal portion of the thrombus 947. A dynamic seal 993 (O-ring, quad-ring, etc.) may be sealed onto the rigid tube 991 at all longitudinal positions of the rigid tube 991. Once the orifice 981 is positioned within the space 949, the pump 612 operates without operation of the peristaltic pump 608 (or with the peristaltic pump set significantly lower), causing fluid to be infused through the infusion lumen 973 and out of the orifice 981 into the space 949.

[0293] Injecting fluid increases the fluid volume of space 949, thereby increasing its pressure, thus neutralizing the previous relative vacuum effect from space 949. A flowable material is present in space 949 to allow suction using peristaltic pump 608 in conjunction with pump 612 to begin maceration and aspiration of thrombus 947 (by turning on peristaltic pump 608). The shaft 963 of catheter 957 can also be advanced and retracted during aspiration to increase the percentage of thrombus 947 being aspirated. Additionally, the injection tube 959 can be advanced or retracted relative to the catheter. The orifice 981 can be adjusted to an appropriate position inside or slightly outside the aspiration lumen 965. This can continue until all, or at least a clinically significant portion, of thrombus 947 has been aspirated. As discussed, in connection with certain ischemic conditions caused by thrombi 947, including stroke, a user can route fluid from a fluid source 679 through a cooling system, such as a heat exchanger or thermoelectric cooler 951 ( FIG. 48 ), which tubing set 664 can operate, thereby cooling the fluid. Additionally, an extracorporeal circuit 953 (as in FIG. 62 ) can be attached to tubing set 664, such that blood removed from the patient (e.g., via a femoral artery, femoral vein, or jugular sheath 955) is added to the fluid from the fluid source 679, resulting in some oxygenated blood being infused into space 949, some of which may potentially supply downstream tissues. The cooled fluid (saline, blood, or saline and blood) can further reduce the metabolic demands of downstream tissues.

[0294] 66-69 illustrate a method for treating a patient using the aspiration system 600 of FIG. 48, but incorporating a suction catheter 967 with a translatable infusion tube 969. The suction catheter 967 has an elongated shaft 995 with an aspiration lumen 997 with a proximal end 999 and an open distal end 2066. The translatable infusion tube 969 has an infusion lumen 2068 with a proximal end 2070 and a distal end 974. The distal end 974 has a distal orifice 2072 such that pressurized fluid infused through the infusion lumen 2068 exits through the orifice 2072, as in FIG. 69. At sufficiently high infusion pressures, the fluid can be expelled in a jet. The pump 612 and peristaltic pump 608 described in FIG. 48 can be utilized. 68 and 70 , an occluder 976 comprising an elongate shaft 978 and a handle 980 at its proximal end 984 has an elastomeric occlusion element 982 connected to its distal end 986 by a connecting member 988. The occlusion element 982 may comprise a circular ring or a spheroid or oval shape and may be formed of any elastomeric material, such as silicone, or a thermoplastic elastomer. The occlusion element 982 has a diameter slightly larger than the diameter of the infusion lumen 2068 and is configured to significantly occlude flow distal to that particular longitudinal position within the infusion lumen 2068. The position shown in FIG. 70 shows the occlusion element 982 occluding the infusion lumen 2068 at a longitudinal position distal to a side orifice 990 in a wall 992 of the infusion tube 969. Thus, when the occluder 976 is in the position shown in FIGS. 68 and 70 , the orifice 2072 is blocked by the occlusion element 982, and pressurized fluid flows through the side orifice 990 (curved arrow, FIG. 70 ). The connecting member 988 may comprise a radiopaque material. A radiopaque marker 994 attached to the infusion tube 969 may be viewed under x-ray or fluoroscopy along with the radiopaque connecting member 988 to assess the specific relative longitudinal position of the occlusion element 982 with respect to the side orifice 990. If desired, the radiopaque marker 994 can be positioned just proximal to the side orifice 990, although in FIG. 70 it is shown just distal to the side orifice 990.When the occlusion element 982 is retracted as shown in FIG. 71 and the occluder 976 is removed as shown in FIG. 69, fluid infusion through the infusion lumen 2068 can exit the orifice 2072. The size of the side orifice 990 can be small enough so that the majority of the infused fluid exits the orifice 2072 when the occluder 976 is removed due to the fact that there is more resistance through the side orifice 990 than through the orifice 2072. Thus, when the infusion tube 969 is in a particular longitudinal position relative to the shaft 995, the occluder 976 can be used to select whether to infuse into the space 949 through the orifice 2072 or into the aspiration lumen 997 of the aspiration catheter 967 through the side orifice 990.

[0295] FIG. 72 illustrates additional or alternative embodiments and steps that may be used in conjunction with the systems and steps of FIGS. 66-69. The blocking member 996 includes an elongated shaft 998 that may be of a larger diameter proximally and a smaller diameter distally. The blocking member 996 also includes a helical blocking element (or feature) 899 at its distal end and a handle 897 at its proximal end. The blocking member 996 may be configured with or include any of the embodiments or features described in connection with the blocking member described in International Publication No. WO 2018 / 029196, filed April 24, 2018, and published November 1, 2018 as WO 2018 / 200566, commonly owned with Incuvate, LLC. Blocking element 899 is configured to be positioned below infusion lumen 2068 and delivered through orifice 2072 into space 949, as shown in FIG. 72, to capture potential dis...

Claims

1. an aspiration catheter configured for placement within a blood vessel of a subject, the aspiration catheter comprising an elongate shaft, the shaft comprising an aspiration lumen having a proximal end and an open distal end; a dilation tube having distal and proximal ends and a lumen extending therebetween, the distal end of the lumen of the dilation tube being configured to be hydraulically connected to the aspiration lumen of the aspiration catheter at or adjacent to the proximal end of the aspiration lumen of the aspiration catheter; a peristaltic pump configured to drive fluid through the expansion tube, the peristaltic pump comprising a pump base having a pressure shoe and a rotatable head, the rotatable head including two or more compression elements arranged around its periphery; a compressible tubular portion disposed between the distal end and the proximal end of the dilation tube, the compressible tubular portion configured to be connected to the pressure shoe and the rotatable head of the peristaltic pump, such that operation of the peristaltic pump rotates the rotatable head and causes the two or more compression elements to drive fluid from the aspiration lumen of the aspiration catheter through the dilation tube from the distal end of the dilation tube to the proximal end of the dilation tube; a first sensor configured to measure pressure through at least one of the aspiration lumen or the lumen of the dilation tube; a controller configured to receive a first signal from the first sensor and configured to vary operation of the peristaltic pump based at least in part on the first signal received from the first sensor related to a change in the pressure; and It is equipped with A system for catheter-based aspiration, wherein the first sensor is configured to directly measure pressure in at least one of the aspiration lumen or the lumen of the dilation tube.

2. 2. The system for catheter-based aspiration of claim 1, wherein the controller is configured to vary the rotational speed of the rotatable head of the peristaltic pump based at least in part on the first signal received from the first sensor related to the change in pressure.

3. 2. The system for catheter-based aspiration of claim 1, wherein the controller is configured to stop rotation of the rotatable head of the peristaltic pump based at least in part on the first signal received from the first sensor related to the change in pressure.

4. 4. The system for catheter-based aspiration of claim 3, wherein the controller is configured to stop rotation of the rotatable head of the peristaltic pump so that a first compression element of the two or more compression elements occludes the dilation tube with the compressible tubular portion.

5. The system for catheter-based aspiration of claim 1 , wherein the two or more compression elements comprise two or more rollers.

6. The system for catheter-based aspiration of claim 1 , wherein the first sensor comprises a pressure transducer.

7. The system for catheter-based aspiration of claim 1 , further comprising a collection receptacle having an interior, the proximal end of the dilation tube configured to deliver the fluid to the interior of the collection receptacle.

8. 10. The system for catheter-based aspiration of claim 1, further comprising a return conduit hydraulically connected to the dilation tube and configured to return to the vascular system of a subject's fluid that has passed through the dilation tube from its distal end to its proximal end.

9. The system for catheter-based aspiration of claim 8 , further comprising a filter disposed between the extension tube and the return conduit.

10. 10. The system for catheter-based aspiration of claim 1, wherein the aspiration catheter further comprises: an infusion lumen extending within the aspiration lumen and having a distal end and a proximal end; and an orifice at or near the distal end of the infusion lumen, the orifice configured to generate one or more jets in the aspiration lumen when pressurized fluid is infused through the infusion lumen; the system further comprises an infusion pump configured to pressurize fluid through the infusion lumen; and the controller configured to vary operation of the infusion pump.

11. The system for catheter-based aspiration of claim 10 , wherein the controller is configured to cause the infusion pump to infuse in a pulsatile manner.

12. The system for catheter-based aspiration of claim 10 , wherein the controller is configured to control a time interval between initiation of operation of the peristaltic pump and initiation of operation of the infusion pump.

13. The system for catheter-based aspiration of claim 12 , wherein the controller is configured to initiate operation of the peristaltic pump and the infusion pump substantially simultaneously.

14. The system for catheter-based aspiration of claim 10 , wherein the controller is configured to control a time interval between cessation of operation of the peristaltic pump and cessation of operation of the infusion pump.

15. The system for catheter-based aspiration of claim 14 , wherein the controller is configured to stop operation of the peristaltic pump and the infusion pump substantially simultaneously.

16. 11. The system for catheter-based aspiration of claim 10, wherein the controller is further configured to vary the operation of the infusion pump based at least in part on the first signal received from the first sensor related to the change in pressure.

17. 10. The system for catheter-based aspiration of claim 1, wherein at least one of the dilation tube or the suction catheter comprises an identification module configured to be read by the peristaltic pump to authorize use of the peristaltic pump with the dilation tube and the suction catheter.

18. The system for catheter-based aspiration of claim 1 , further comprising a foot pedal configured to send a signal to the controller to vary the operation of the peristaltic pump.

19. The system for catheter-based aspiration of claim 1 , further comprising an on / off hand switch configured to send a signal to the controller to vary operation of the peristaltic pump.

20. The system for catheter-based aspiration of claim 1 , wherein the compressible tubular portion comprises a material selected from the list consisting of silicone, polyurethane, and polyvinyl chloride.

21. The system for catheter-based aspiration of claim 1 , wherein the outer surface of the compressible tubular portion includes a coating of lubricious material.

Images