The present disclosure provides a system for delivery of therapeutic energy. The system includes an energy unit configured to convert the acoustic energy signals transmitted to therapeutic ultrasound directed to fragment tumors and carcinogenic tissue in the body. The system also includes an energy unit configured to convert the acoustic energy signal transmitted from the energy unit to ultrasonic energy to image and monitor the treatment site with ultrasound. The system also includes a control unit including a computer for data storage and display.

A microcavitation system, device, and ultrasonic probe assembly for generating directional microcavitation includes a cannula and an ultrasonic transmission member. The ultrasonic transmission member has a first end portion and a second end spaced apart from the first end portion. The cannula has a tubular side wall, a cannula lumen, a fluid input port, a proximal end, a distal end, and a distal end portion. The ultrasonic transmission member is located in the cannula lumen. The fluid input port of the cannula is connected in fluid communication with the cannula lumen. The distal end portion of the cannula is configured to define a cavitation generation chamber. The cavitation generation chamber has a distal end wall at the distal end of the cannula that is configured as a sieve to define a plurality of apertures.

A handpiece-type high-frequency vibration cutting device includes a housing (10); a vibration device (21); a holding member (11); a tool (12); and a controller (20) to control the operations of the vibration device (21). The controller (20) controls the vibration of the tool (12) due to the vibration device (21) such that the vibration is burst oscillation in which vibration and stop of vibration are repeated. The controller (20) also controls the entire burst frequency f1 of the tool (12) to be included in the range of 1 to 8 [Hz], one cycle of the burst frequency f1 including a burst period with the holding member (11) vibrating and a stop period with the tool (12) not vibrating. The controller (20) also controls the vibration frequency f2 of the tool (12) during the burst period such that the vibration frequency f2 is in the range of 20 to 60 [kHz].

An ultrasonic probe assembly includes a handle configured to be handheld, and has a housing that defines a chamber. A carriage is slidably coupled to the housing. The carriage has an operator arm configured to be operable by a user to move the carriage between a first position and a second position. An ultrasonic catheter has a catheter sheath and an ultrasonic core wire. The ultrasonic catheter has a proximal end portion and a distal end portion. An ultrasonic transducer is positioned in the chamber of the housing. The ultrasonic transducer is connected to the proximal end portion of the ultrasonic catheter, and the ultrasonic transducer is connected to the carriage. The ultrasonic transducer is configured to longitudinally move in the chamber of the housing between a retracted position and an extended position coincident with a corresponding longitudinal movement of the carriage.

Described herein are shock wave devices and methods for the treatment of calcified heart valves. One variation of a shock wave device may comprise an elongated flexible tube carried by a sheath. The tube may have a fluid input end, which may be located near a proximal end of the sheath. The tube may include a loop portion. The loop portion may be configured to be at least partially accommodated within a cusp of the heart valve. The tube may be fillable with a conductive fluid. In some variations, the shock wave device may include an array of electrode pairs associated with a plurality of wires positioned within the loop portion of a tube. The electrode pairs may be electrically connectable to a voltage source and configured to generate shock waves in the conductive fluid in response to voltage pulses.

A method for making a vibrational catheter device includes providing a transition connector comprising a proximal portion, a distal portion, and a tapered portion that defines a tapered outer surface of the transition connector, the proximal portion being wider than the distal portion, and the transition connector having a bore disposed within the tapered portion; inserting a proximal end of an ultrasound transmission member into the bore; and deforming at least part of the transition connector at the tapered outer surface so as to apply greater force to the wider proximal portion than to the distal portion to secure the proximal end of the ultrasound transmission member within the bore.

A system for aspirating thrombus and delivering an agent includes an aspiration catheter having a supply lumen having a proximal end, a distal end, and a wall, and an aspiration lumen having a proximal end, an open distal end, and an interior wall surface adjacent the open distal end, and at least one orifice at or adjacent the distal end of the supply lumen, in fluid communication with the aspiration lumen and located proximally of the open distal end of the aspiration lumen, wherein the at least one orifice is configured to create a spray pattern that is caused to impinge on the interior wall surface of the aspiration lumen such that the spray pattern upon impinging on the interior wall surface is caused to transform into at least a substantially distally-oriented flow capable of exiting the open distal end of the aspiration lumen.

A clot removal device for removal of an occlusion from a lumen in a patient's body is provided. The clot removal device has a lumen, an elongated member positioned within the lumen and extending axially from a proximal end to a distal end of the lumen, a handle attached to the proximal end of the lumen, a first expandable member positioned along a length of the elongated member, a second expandable member positioned along the length of the elongated member, wherein the second expandable member is distal to the first expandable member relative to the handle. The handle has at least one actuation mechanism and at least one of the following applies: a) the first expandable member is coupled to the at least one actuation mechanism and is configured to be moveable relative to the second expandable member upon manipulation of the at least one actuation mechanism; b) the first expandable member is configured to mechanically expand or contract by manipulating the at least one actuation mechanism; c) the second expandable member is coupled to the at least one actuation mechanism and is configured to be moveable relative to the first expandable member upon manipulation of the at least one actuation mechanism; or d) the second expandable member is configured to mechanically expand or contract by manipulating the at least one actuation mechanism.

Described herein are shock wave devices and methods for the treatment of calcified heart valves. One variation of a shock wave device may comprise an elongated flexible tube carried by a sheath. The tube may have a fluid input end, which may be located near a proximal end of the sheath. The tube may include a loop portion. The loop portion may be configured to be at least partially accommodated within a cusp of the heart valve. The tube may be fillable with a conductive fluid. In some variations, the shock wave device may include an array of electrode pairs associated with a plurality of wires positioned within the loop portion of a tube. The electrode pairs may be electrically connectable to a voltage source and configured to generate shock waves in the conductive fluid in response to voltage pulses.

A method for attempting to fragment or comminute an object in a body using ultrasound includes producing a burst wave lithotripsy (BWL) waveform by a therapy transducer. The BWL waveform is configured to fragment or comminute the object. The BWL waveform includes a first burst of continuous ultrasound cycles and a second burst of continuous ultrasound cycles. A burst frequency corresponds to a frequency of repeating the bursts of the BWL waveform. The method also includes determining a cycle frequency f of the continuous ultrasound cycles within the first burst and the second burst based on a target fragment size D, where the cycle frequency is:
f(MHz)=0.47/D(mm).