Methods, systems, and apparatus, including computer programs encoded on computer storage media, for estimating wave properties of a body of water. A computer-implemented system obtains measurement data for a duration of time from an inertial measurement unit (IMU) onboard an underwater device, generates model input data based on at least the measurement data obtained at the plurality of time points, and processes the model input data to generate model output data indicating one or more wave properties using a machine-learning model. The system further determines, based on at least the one or more wave properties, whether the device is safe to be deployed.

Techniques, systems, and devices are disclosed for ultrasound diagnostics using spread spectrum, coherent, frequency- and/or phase-coded waveforms. In one aspect, a method includes synthesizing individual orthogonal coded waveforms to form a composite waveform for transmission toward a biological material of interest, in which the synthesized individual orthogonal coded waveforms correspond to distinct frequency bands and include one or both of frequency-coded or phase-coded waveforms; transmitting a composite acoustic waveform toward the biological material of interest, where the transmitting includes transducing the individual orthogonal coded waveforms into corresponding acoustic waveforms to form the composite acoustic waveform; receiving acoustic waveforms returned from at least part of the biological material of interest corresponding to at least some of the transmitted acoustic waveforms that form the composite acoustic waveform; and processing the received returned acoustic waveforms to produce an image of at least part of the biological material of interest.

A method for use in acoustic imaging, comprising: transmitting, from a transmitter, a first sound wave pulse at a first frequency determined by a maximum sampling rate of a receiver; transmitting at least one second sound wave pulse at a frequency substantially equal to the first frequency, the first and at least one second sound wave pulses being transmitted substantially within a fraction of a sample interval of the receiver; receiving and sampling, at the receiver, a reflection of at least two of the first and at least one second pulses to generate a set of receiver samples; and expanding the set of receiver samples, based on the first frequency and a total number of the first and at least one second pulses transmitted, to generate an expanded sample set with a larger number of samples than the set of receiver samples.

A system may include an ultrasound probe and a controller unit configured to communicate with the ultrasound probe. The controller unit may be further configured to transmit ultrasound signals using the ultrasound probe toward an area of interest in a patient's body, wherein the ultrasound signals include a fundamental frequency signal and at least one harmonic frequency signal; receive echo signals from the area of interest based on the transmitted ultrasound signals; obtain a fundamental frequency echo signal and at least one harmonic frequency echo signal from the received echo signals; and generate a visual representation of the area of interest based on the obtained fundamental frequency echo signal and the obtained at least one harmonic frequency echo signal.

Aspects of the technology described herein relate to ultrasound imaging of lungs. An ultrasound device may be configured with a set of parameter values associated with a shallow lung imaging mode. A selection of a change in imaging depth may be received. If the selected imaging depth is greater than or equal to a threshold imaging depth, the ultrasound device may be configured with a set of parameter values associated with a deep lung imaging mode. The set of parameter values associated with the shallow lung imaging mode may be optimized for imaging lung sliding and the set of parameter values associated with the deep lung imaging mode may be optimized for imaging A lines and B lines.

Some implementations of the disclosure are directed to an ultrasound measurement device including: multiple ultrasound sensors to capture tomographical information of a physiological structure, each ultrasound sensor comprising a transducer having a respective resonant frequency, where each transducer has a frequency response that partially overlaps with a frequency response of another transducer; and a processing device to control and process measurements made by the ultrasound sensors. The device may be incorporated in an adhesive substrate configured to be adhered to a patient's skin in alignment with an artery of the patient. The processing device may use the multiple ultrasound sensors to compute the mean arterial pressure through the artery by performing operations of: measuring a circumference of the artery using the multiple ultrasound sensors; measuring a blood flow velocity using the same ultrasound sensors; and computing the mean arterial pressure using the measured arterial circumference and blood flow velocity.

An acoustic imaging probe having an adjustable effective elevation length. The acoustic 5imaging probe has a transducer element, comprising a plurality of acoustic transducers, that is divided into a plurality of sets of adjacent transducers. A processing module controls how many sets contribute to an acoustic pulse emitted by the acoustic transducer element during an imaging process, to thereby adjust an effective elevation length of the acoustic imaging probe.

A transducer transmits into the bone a first plurality of excitation pulses at a plurality of frequencies and measures a plurality of echoes corresponding to the plurality of excitation pulses. An ultrasound machine calculates a plurality of energies each corresponding to a respective one of the plurality of echoes and identifies a lowest echo corresponding to a lowest of the plurality of energies. The ultrasound machine matches the lowest echo to a corresponding one of the first plurality of excitation pulses, the corresponding one of the first plurality of excitation pulses having a chosen frequency. The ultrasound machine generates an acoustic impulse response by deconvolving the corresponding one of the first plurality of excitation pulses with the lowest echo, and generates an updated sensing matrix by convolving the initial sensing matrix with the acoustic impulse response. Subsequent ultrasounds use the updated sensing matrix.

A dual frequency ultrasound transducer includes a high frequency ultrasound array and a low frequency transducer positioned behind or proximal to the high frequency ultrasound array. In one embodiment, a dampening material is positioned between a rear surface of the high frequency array and the a front surface of the low frequency array. The dampening preferably is high absorbing of signals at the frequency of the high frequency array but passes signals at the frequency of the low frequency transducer with little attenuation. In additional, or alternatively, the low frequency can angled with respect to the plane of the high frequency transducer to reduce inter-stack multipath reflections. Beamforming delays compensate for the differences in physical distances between the elements of the low frequency transducer and the plane of the high frequency transducer.

Estimation of vibration amplitude of intra-capillary micro-bubbles driven to vibrate with an incident ultrasound wave with amplitude and frequency to adjust the drive amplitude of the incident wave to obtain specified vibration amplitude of extra-capillary tissue. Estimation uses transmission of M groups of pulse complexes having low frequency pulse (LF) at bubble drive frequency, and high frequency (HF) pulse with angular frequency ω.sub.H> ~ 5 ω.sub.L, and pulse duration shorter than π/4ω.sub.L along HF beam. The phase between HF and LF pulses is ω.sub.Lt.sub.m for each group, where t.sub.m varies between the groups. Within each group, LF pulse varies between pulse complexes in amplitude and/or, where the LF pulse can be zero for a pulse complex, and LF pulse is different from zero for pulse complex within each group. HF receive signals are processed to obtain a parameter relating to bubble vibration amplitude when the HF pulse hits bubble.