Various methods and systems are provided for a multi-frequency transducer array. In one example, the transducer array includes an element formed of one or more sub-elements, at least one sub-element having a different resonance frequency. A frequency range of the transducer array may thereby be broadened.

A multi-frequency ultrasound therapy apparatus is configured to operate at its center frequency and at the higher harmonic of its center frequency. The center frequency can be for the entire apparatus or for each ultrasound source element. At least one source element can generate ultrasound energy at its center frequency while, simultaneously, at least another source element can generate ultrasound energy at the higher harmonic of its center frequency. In addition, the same source element can generate ultrasound energy at its center frequency and the higher harmonic of its center frequency, respectively, but at different times. A data storage unit that stores encrypted and encoded data is disposed on the apparatus. The encoded data includes a unique identification code of the apparatus, the condition of use of the apparatus, the center frequency of each source element, the ultrasound efficiency of each source element, and/or other parameters relating to the apparatus.

A focused extracorporeal shock wave therapy (f-ESWT) device includes a handheld housing, a battery, and a transducer assembly. The battery is located in the handheld housing. The transducer assembly is located in the handheld housing and is operably connected to the battery. The transducer assembly is configured to generate a focused shock wave using electrical energy from the battery.

A focused extracorporeal shock wave therapy (f-ESWT) system includes an f-ESWT device and a plurality of interchangeable standoff structures. The f-ESWT device includes a housing. The f-ESWT device is configured to generate a focused shock wave as a combination of a plurality of individual shock waves. Each standoff structure is configured for removable connection to the housing to receive and to transmit the plurality of individual shock waves. Each standoff structure of the plurality of interchangeable standoff structures includes a rigid exterior shell defining a shell space, and an elastomeric interior at least partially located in the shell space. The plurality of individual shock waves is transmitted through the rigid exterior shell and the elastomeric interior of a selected standoff structure of the plurality of interchangeable standoff structures that is removably connected to the housing.

A method of generating a focused shock wave with a handheld focused extracorporeal shock wave therapy (f-ESWT) device includes driving a plurality of piezoelectric elements to generate a focused shock wave based on a first plurality of time delays when a first standoff structure is removably connected to a handheld housing of the f-ESWT device, and driving the plurality of piezoelectric elements to generate the focused shock wave based on a second plurality of time delays when a second standoff structure is removably connected to the handheld housing of the f-ESWT device, the second plurality of time delays different from the first plurality of time delays, and the second standoff structure different from the first standoff structure.

An ultrasonic transducer includes a piezoelectric material layer, a first electrode layer, and a second electrode layer. The piezoelectric material layer has an ultrasonic wave emitting side and a back side opposite to the ultrasonic wave emitting side. The piezoelectric material layer has a protrusion structure or a recess structure on the back side. The protrusion structure or the recess structure overlaps a central axis of the piezoelectric material layer. The first electrode layer is disposed on the back side of the piezoelectric material layer. The second electrode layer is disposed on the ultrasonic wave emitting side of the piezoelectric material layer.

Aspects of the technology described herein relate to ultrasound device circuitry as may form part of a single substrate ultrasound device having integrated ultrasonic transducers. The ultrasound device circuitry may facilitate the generation of ultrasound waveforms in a manner that is power- and data-efficient.

A method and system for controlling an array of piezoelectric transducers (11, 12, 13). Respective driving signals (Vn) are applied to the transducers. The driving signals (Vn) comprise an alternating component (A) oscillating at one or more driving frequencies to cause corresponding vibrations in the transducers for generating acoustic waves (Wn). One or more of the driving signals (Vn) are offset by a respective bias voltage (Bn). The bias voltage (Bn) is controlled to reduce a difference in resonance frequencies between the transducers. To eliminate any remaining difference, the alternating component (A) to at least a subset of the transducers (11,12) is periodically reset. In this way the phases of the resulting acoustic waves (W1,W2) can be synchronized.

An apparatus comprises a stressed glass member and an actuator mounted on the stressed glass member. A power source is coupled to the actuator. An abrasion structure is disposed between the actuator and the stressed glass member. The abrasion structure comprises abrading features in contact with the stressed glass member. The abrading features have a hardness higher than a hardness of the stressed glass member. When energized by the power source, the actuator is configured to induce movement of the abrasion structure that causes the abrading features to create scratches in the stressed glass member to a depth sufficient to initiate fracture of the stressed glass member.

The present invention relates to an ultrasound transducer assembly (10), in particular for intra vascular ultrasound systems. The assembly (10) comprises a transducer array (12) including a plurality of transducer elements (14) for transmitting and receiving ultrasound waves. Two support elements (16, 18) are provided for supporting the transducer array (12) in a curved or polygonal shape. The support elements (16, 18) are connected via a flexible connection layer (20) to the transducer array (12) for flexibly connecting the support elements (16, 18) to the transducer array (12).