The technology in this application enables 3D optical imaging of a diffuse medium (such as tissue). In a medical context, this could be used to identify tumors. Optical imaging is much less expensive than MRI imaging and is possible with off-the-shelf consumer electronics such as LCDs, CMOS image sensors, and lasers. In operation, a laser illuminates an LCD with infrared light. Driving different holographic 2D images onto the LCD allows for "steering" the laser light to different regions (voxels) in the tissue. A CMOS image sensor captures an interference image of an exit signal of the laser light exiting the tissue interfering with a reference wavefront (same wavelength as the laser light). Analysis of the interference image reveals the characteristics of the voxel.

The technology in this application enables 3D optical imaging of a diffuse medium (such as tissue). In a medical context, this could be used to identify tumors. Optical imaging is much less expensive than MRI imaging, for example, and is possible with off-the-shelf consumer electronics such as LCDs, CMOS image sensors, and lasers. In operation, a laser illuminates an LCD with infrared light. Driving different holographic 2D images onto the LCD allows for "steering" the laser light to different regions (voxels) in the tissue. A CMOS image sensor captures an interference image of an exit signal of the laser light exiting the tissue interfering with a reference wavefront (same wavelength as the laser light). Analysis of the interference image reveals the characteristics of the voxel.

The technology in this application enables 3D optical imaging of a diffuse medium (such as tissue). In a medical context, this could be used to identify tumors. Optical imaging is much less expensive than MRI imaging, for example, and is possible with off-the-shelf consumer electronics such as LCDs, CMOS image sensors, and lasers. In operation, a laser illuminates an LCD with infrared light. Driving different holographic 2D images onto the LCD allows for "steering" the laser light to different regions (voxels) in the tissue. A CMOS image sensor captures an interference image of an exit signal of the laser light exiting the tissue interfering with a reference wavefront (same wavelength as the laser light). Analysis of the interference image reveals the characteristics of the voxel.

The technology in this application enables 3D optical imaging of a diffuse medium (such as tissue). In a medical context, this could be used to identify tumors. Optical imaging is much less expensive than MRI imaging and is possible with off-the-shelf consumer electronics such as LCDs, CMOS image sensors, and lasers. In operation, a laser illuminates an LCD with infrared light. Driving different holographic 2D images onto the LCD allows for "steering" the laser light to different regions (voxels) in the tissue. A CMOS image sensor captures an interference image of an exit signal of the laser light exiting the tissue interfering with a reference wavefront (same wavelength as the laser light). Analysis of the interference image reveals the characteristics of the voxel.

The technology in this application enables 3D optical imaging of a diffuse medium (such as tissue). In a medical context, this could be used to identify tumors. Optical imaging is much less expensive than MRI imaging and is possible with off-the-shelf consumer electronics such as LCDs, CMOS image sensors, and lasers. In operation, a laser illuminates an LCD with infrared light. Driving different holographic 2D images onto the LCD allows for "steering" the laser light to different regions (voxels) in the tissue. A CMOS image sensor captures an interference image of an exit signal of the laser light exiting the tissue interfering with a reference wavefront (same wavelength as the laser light). Analysis of the interference image reveals the characteristics of the voxel.

The technology in this application enables 3D optical imaging of a diffuse medium (such as tissue). In a medical context, this could be used to identify tumors. Optical imaging is much less expensive than MRI imaging and is possible with off-the-shelf consumer electronics such as LCDs, CMOS image sensors, and lasers. In operation, a laser illuminates an LCD with infrared light. Driving different holographic 2D images onto the LCD allows for "steering" the laser light to different regions (voxels) in the tissue. A CMOS image sensor captures an interference image of an exit signal of the laser light exiting the tissue interfering with a reference wavefront (same wavelength as the laser light). Analysis of the interference image reveals the characteristics of the voxel.

The technology in this application enables 3D optical imaging of a diffuse medium (such as tissue). In a medical context, this could be used to identify tumors. Optical imaging is much less expensive than MRI imaging and is possible with off-the-shelf consumer electronics such as LCDs, CMOS image sensors, and lasers. In operation a laser illuminates an LCD with infrared light. Driving different holographic 2D images onto the LCD allows for "steering" the laser light to different regions (voxels) in the tissue. A CMOS image sensor captures an interference image of an exit signal of the laser light exiting the tissue interfering with a reference wavefront (same wavelength as the laser light). Analysis of the interference image reveals the characteristics of the voxel.

The application is about co-located image pixels and display pixels to enable reconstruction of a received wavefront in order to retransmit the received wavefront along a reverse-optical path. In the context of medical imaging, this allows the device to "focus" infrared light back to a voxel of tissue in order to determine the absorption (and corresponding blood flow) through the voxel. A device may include an image pixel array with co-located display pixels. Each display pixel may receive infrared light through a corresponding co-located image pixel. An optical transformation engine modulates infrared display light emitted by the display pixels in response to the light received by the co-located image pixel. When the display pixels are liquid crystal, the phase of the received infrared light may be measured by modulating the orientation of the liquid crystals in the display nixel that is positioned in front of the on The application is about co-located image pixels and display pixels to enable reconstruction of a received wavefront in order to retransmit the received wavefront along a reverse-optical path. In the context of medical imaging, this allows the device to "focus" infrared light back to a voxel of tissue in order to determine the absorption (and corresponding blood flow) through the voxel. A device may include an image pixel array with co-located display pixels. Each display pixel may receive infrared light through a corresponding co-located image pixel. An optical transformation engine modulates infrared display light emitted by the display pixels in response to the light received by the co-located image pixel. When the display pixels are liquid crystal, the phase of the received infrared light may be measured by modulating the orientation of the liquid crystals in the display nixel that is positioned in front of the on

The technology in this application enables extracting phase data from an infrared imaging signal exiting tissue using optical transformation logic and then quickly generating a hologram from the phase data so that the hologram can be driven onto a display that reconstructs (and retransmits) the incoming infrared image signal back into the tissue in a reverse optical path.

The technology in this application enables 3D optical imaging of a diffuse medium (such as tissue). In a medical context, this could be used to identify tumors. Optical imaging is much less expensive than MRI imaging, for example, and is possible with off-the-shelf consumer electronics such as LCDs, CMOS image sensors, and lasers. In operation, a laser illuminates an LCD with infrared light. Driving different holographic 2D images onto the LCD allows for "steering" the laser light to different regions (voxels) in the tissue. A CMOS image sensor captures an interference image of an exit signal of the laser light exiting the tissue interfering with a reference wavefront (same wavelength as the laser light). Analysis of the interference image reveals the characteristics of the voxel.

This application is directed to a specific hardware implementation for implementing the methods of OPENWP103 that includes placing a beam splitter between an image sensor and a display placed 90 degrees offset from each other. See FIG. 1A-1C. The beam splitter functions to reflect an infrared reference wavefront to the image sensor so the image sensor can capture the interference pattern between the infrared reference wavefront and an incoming infrared image signal (received from tissue). The beam splitter also serves to reflect (and transmit) a reconstructed infrared wavefront back into the tissue.

This application is directed to a specific hardware implementation for implementing the methods of OPENWP 103 that includes placing an image sensor behind an LCD display. See FIG. 2A-2C.

This application is directed to a specific hardware implementation for implementing the methods of OPENWP103 that includes placing a beam splitter between an image sensor and a display placed 90 degrees offset from each other. See FIG. 1A-1C. The beam splitter functions to reflect an infrared reference wavefront to the image sensor so the image sensor can capture the interference pattem between the infrared reference wavefront and an incoming infrared image signal (received from tissue). The beam splitter also serves to reflect (and transmit) a reconstructed infrared wavefront back into the tissue.

This application is directed to a specific hardware implementation for implementing the methods of OPENWP103 that includes placing a beam splitter between an image sensor and a display placed 90 degrees offset from each other. See FIG. 1A-1C. The beam splitter functions to reflect an infrared reference wavefront to the image sensor so the image sensor can capture the interference pattem between the infrared reference wavefront and an incoming infrared image signal (received from tissue). The beam splitter also serves to reflect (and transmit) a reconstructed infrared wavefront back into the tissue.

This application is directed to a specific hardware implementation for implementing the methods of OPENWP103 that includes placing a beam splitter between an image sensor and a display placed 90 degrees offset from each other. See FIG. 1A-1C. The beam splitter functions to reflect an infrared reference wavefront to the image sensor so the image sensor can capture the interference pattem between the infrared reference wavefront and an incoming infrared image signal (received from tissue). The beam splitter also serves to reflect (and transmit) a reconstructed infrared wavefront back into the tissue.

The technology in this application enables capturing 3D images of diffuse mediums (e.g. tissue) using extraction logic to isolate the intensity data from image pixels. A hologram generated by outputs of the extraction logic can be used to reconstruct (and retransmit) the incoming infrared image signal. An interference pattem between an infrared reference beam and an incoming infrared image signal (received from tissue) is captured by an image pixel array. The extraction logic (1) performs a Fast Fourier transform on the interference pattern; (2) isolates frequencies representing the interference pattern; (3) generates a spatial domain image on the isolated frequencies; and (4) extracts phase data from the spatial domain image. A hologram can be generated from the phase data and a display may be driven with the hologram to reconstruct the incoming infrared image signal.

The technology in this application enables capturing 3D images of diffuse mediums (e.g. tissue) using extraction logic to isolate the intensity data from image pixels. A hologram generated by outputs of the extraction logic can be used to reconstruct (and retransmit) the incoming infrared image signal. An interference pattem between an infrared reference beam and an incoming infrared image signal (received from tissue) is captured by an image pixel array. The extraction logic (1) performs a Fast Fourier transform on the interference pattern; (2) isolates frequencies representing the interference pattern; (3) generates a spatial domain image on the isolated frequencies; and (4) extracts phase data from the spatial domain image. A hologram can be generated from the phase data and a display may be driven with the hologram to reconstruct the incoming infrared image signal.

The technology in this application enables capturing 3D images of diffuse mediums (e.g. tissue) using extraction logic to isolate the intensity data from image pixels. A hologram generated by outputs of the extraction logic can be used to reconstruct (and retransmit) the incoming infrared image signal. An interference pattem between an infrared reference beam and an incoming infrared image signal (received from tissue) is captured by an image pixel array. The extraction logic (1) performs a Fast Fourier transform on the interference pattern; (2) isolates frequencies representing the interference pattern; (3) generates a spatial domain image on the isolated frequencies; and (4) extracts phase data from the spatial domain image. A hologram can be generated from the phase data and a display may be driven with the hologram to reconstruct the incomina infrared image sianal.

This application is for a compact optical element for generating a reference wavefront for optical imaging. For example, a fiber optic can carry a laser signal into the compact optical element and a diffractive optical element within the optical element can expand, collimate, and deliver a reference wavefront at a desired angle with respect to an image sensor.

This application is for a compact optical element for generating a reference wavefront for optical imaging. For example, a fiber optic can carry a laser signal into the compact optical element and a diffractive optical element within the optical element can expand, collimate, and deliver a reference wavefront at a desired angle with respect to an image sensor.

This application refers to a device or system illuminates a diffuse medium with an infrared light while an ultrasound emitter is focused on a particular voxel. The infrared light encountering the particular voxel may be wavelength-shifted by the ultrasonic signal. The wavelength-shifted infrared imaging signal can be measured by a light detector (e.g. image pixel array). Extraction logic may isolate the wavelength-shifted infrared imaging signal and extract intensity data and then populate a voxel value of a composite image with the intensity data. The composite image may include a three-dimensional image of the diffuse medium.

This application is directed to an optical element having a curved, partially reflective layer to combine an imaging signal with a reference wavefront. See element 483 in FIG. 4. The curved partially reflective layer redirects the reference wavefront to the image sensor at an engineered angle while also passing the infrared exit signal to interfere with the reference wavefront.

This application enables dual-wavelength optical imaging of tissue in a single image and the difference between the different wavelengths is representative of an absorption level of the voxel that was being imaged. The absorption of the voxel is tied to oxygenation and deoxygenation of blood and bloodflow. When multiple voxels are imaged, a 3D image showing absorption-level differences can be generated.

Pulsed lasers emit light pulses that have variations in intensity and duration. When pulsed lasers are used for optical imaging, the varying light pulses affect the intensity of the received signal voxel-to-voxel. In this invention, an energy meter (e.g. photodiode) measures the energy level of the light pulses emitted from a laser in an optical imaging system. Normalization logic receives the energy level from energy meter and normalizes the exit signal in response to the energy level.

This invention is an multi-tip apparatus to enable optical imaging of tissue. Image sensors and/or laser outputs (from fiber optics) are included in tips mounted to flexible members of the apparatus, which allows the tips to conform around the shape of the tissue being imaged. A body handle of the apparatus may include an ultrasonic emitter and the laser to illuminate the tissue by way of fiber optics that run through the flexible members to the tips.

This invention is a laser oscillator and amplifier that can be used for optical imaging. A seed laser is optically coupled to am optical amplifier configured to direct the amplified laser light into a diffuse medium.

This invention is a multi-channel laser that can be used for optical imaging. A seed laser is optically coupled to a plurality of optical amplifiers. An optical distribution assembly distributes the seed laser light to each optical amplifier and the optical amplifiers are configured to direct the amplified laser light into a diffuse medium (without the amplified laser light being optically combined back into the same laser beam).

This invention is a multi-channel laser that can be used for optical imaging. A seed laser is optically coupled to a plurality of optical amplifiers. An optical distribution assembly distributes the seed laser light to each optical amplifier and the optical amplifiers are configured to direct the amplified laser light into a diffuse medium (without the amplified laser light being optically combined back into the same laser beam).

This invention is a multi-channel laser that can be used for optical imaging. A seed laser is optically coupled to a plurality of optical amplifiers. An optical distribution assembly distributes the seed laser light to each optical amplifier and the optical amplifiers are configured to direct the amplified laser light into a diffuse medium (without the amplified laser light being optically combined back into the same laser beam).

This invention is a multi-channel laser that can be used for optical imaging. A seed laser is optically coupled to a plurality of optical amplifiers. An optical distribution assembly distributes the seed laser light to each optical amplifier and the optical amplifiers are configured to direct the amplified laser light into a diffuse medium (without the amplified laser light being optically combined back into the same laser beam).

This invention is a multi-channel laser that can be used for optical imaging. A seed laser is optically coupled to a plurality of optical amplifiers. An optical distribution assembly distributes the seed laser light to each optical amplifier and the optical amplifiers are configured to direct the amplified laser light into a diffuse medium (without the amplified laser light being optically combined back into the same laser beam).

This invention enables an ultrasound signal and optical signals to propagate along the same optical path for imaging purposes. When ultrasound and optical imaging are combined, this allows for imaging of the same voxel with dual modalities. A glass element is fixed in an index-matching liquid having the same refractive index as the glass element. The glass element is immersed in an enclosure and the glass element redirects the ultrasonic signal while the optical signal (e.g. infrared) propagates through the glass element (along the same optical path as the ultrasound signal). The optical signal is not refracted by the glass element because the index matching fluid surrounding the glass element is the same refractive index as the glass element.

This invention enables an ultrasound signal and optical signals to propagate along the same optical path for imaging purposes. When ultrasound and optical imaging are combined, this allows for imaging of the same voxel with dual modalities. A glass element is fixed in an index matching liquid having the same refractive index as the Sglass element. The glass element is immersed in a disclosure and the glass element redirects the ultrasonic signal while the optical signal (e.g. infrared) propagates through the glass element (along the same optical path as the ultrasound signal). The optical signal is not refracted by the glass element because the index matching fluid surrounding the glass element is the same refractive index as the glass element

This invention is directed to a laser amplifier that reduces or eliminates optical chirp in pulsed laser - especially for high powered pulsed lasers. The optical amplifier includes a waveguide and a diffraction grating positioned between two

semiconductor layers. The semiconductor optical amplifier emits output light through a 2D surface of one of the semiconductor layers. The diffraction grating is a 1D or 2D photonic crystalline structure that directs light to the waveguide to facilitate amplification through constructive interference and directs/deflects light into or out of the waveguide by constructive interference.

This invention is directed to a laser amplifier that reduces or eliminates optical chirp in pulsed laser - especially for high powered pulsed lasers. The optical amplifier includes a waveguide and a diffraction grating positioned between two semiconductor layers. The semiconductor optical amplifier emits output light through a 2D surface of one of the semiconductor layers. The diffraction grating is a 1D or 2D photonic crystalline structure that directs light to the waveguide to facilitate amplification through constructive interference and directs/deflects light into or out of the waveguide by constructive interference.

This invention allows for imaging measurements from an unshifted reference beam having the same wavelength as the laser source that illuminates the tissue. In prior optical imaging contexts, the reference beam that interfered with an infrared exit signal would be shifted to match the wavelength generated from an ultrasonic signal encountering the infrared illumination light. In this invention, the absence of the wavelength-shifted light is recorded by subtracting from a base infrared signal that is captured when no ultrasonic signal propagates through the tissue.

This invention allows for imaging measurements from an unshifted reference beam having the same wavelength as the laser source that illuminates the tissue. In prior optical imaging contexts, the reference beam that interfered with an infrared exit signal would be shifted to match the wavelength generated from an ultrasonic signal encountering the infrared illumination light. In this invention, the absence of the wavelength-shifted light is recorded by subtracting from a base infrared signal that is captured when no ultrasonic signal propagates through the tissue.

This invention increases the accuracy of optical imaging that is assisted by ultrasound by providing a "light scattering layer that can facilitate transmission of the ultrasound signal. A gel wax layer may be used as the light scattering layer. By measuring the wavelength-shift imparted by an ultrasound signal on a reference beam in a controlled/known medium (e.g. gel wax layer), the measurement of an infrared signal in an unknown medium (e.g. tissue) can be calibrated.

This invention increases the accuracy of optical imaging that is assisted by ultrasound by providing a "light scattering layer" that can facilitate transmission of the ultrasound signal. A gel wax layer may be used as the light scattering layer. By measuring the wavelength-shift imparted by an ultrasound signal on a reference beam in a controlled/known medium (e.g. gel wax layer), the measurement of an infrared signal in an unknown medium (e.g. tissue) can be calibrated.

This invention increases the accuracy of optical imaging that is assisted by ultrasound by using two optical wavelengths where one wavelength propagates within a light scattering layer. A first signal is measured of the ultrasound signal's impact on a first wavelength propagating within the light scattering layer (e.g. gel wax layer). This first signal represents a mechanical contrast of a voxel being imaged. A second signal is measured of the ultrasound signal's impact on a second wavelength propagating within tissue. The second signal represents both mechanical contrast and optical contrast. Thus, the optical contrast of a voxel can be determined by subtracting the first signal from the second signal.

This invention increases the accuracy of optical imaging that is assisted by ultrasound by using two optical wavelengths where one wavelength propagates within a light scattering layer. A first signal is measured of the ultrasound signal's impact on a first wavelength propagating within the light scattering layer (e.g. gel wax layer). This first signal represents a mechanical contrast of a voxel being imaged. A second signal is measured of the ultrasound signal's impact on a second wavelength propagating within tissue. The second signal represents both mechanical contrast and optical contrast. Thus, the optical contrast of a voxel can be determined by subtracting the first signal from the second signal.

This invention enables blood flow measurements in tissue based on coherent light values. A laser pulse is directed into the tissue. An image is captured of the diffuse laser light exiting the tissue. A coherence value of the diffuse laser light is determined. The blood flow rate is determined from the coherence value.

This invention enables blood flow measurements in tissue based on coherent light values. A laser pulse is directed into the tissue. An image is captured of the diffuse laser light exiting the tissue. A coherence value of the diffuse laser light is determined. The blood flow rate is determined from the coherence value.

This invention enables blood flow measurements in tissue based on coherent light values. A laser pulse is directed into the tissue. An image is captured of the diffuse laser light exiting the tissue. A coherence value of the diffuse laser light is determined. The blood flow rate is determined from the coherence value.

This invention enables blood flow measurements in tissue based on coherent light values. A laser pulse is directed into the tissue. An image is captured of the diffuse laser light exiting the tissue. A coherence value of the diffuse laser light is determined. The blood flow rate is determined from the coherence value.

This invention enables blood flow measurements in tissue based on coherent light values. A laser pulse is directed into the tissue. An image is captured of the diffuse laser light exiting the tissue. A coherence value of the diffuse laser light is determined. The blood flow rate is determined from the coherence value.

The presently disclosure methods and apparatus allow focusing and imaging of translucent materials with decreased size and complexity. The presently disclosed methods and apparatus provide improved focusing and imaging with decreased size and weight, so as to allow use in many fields. In some embodiments, the spatial light modulator comprises at least about a million independently controllable light modulating pixels, which can provide increased resolution and allow focusing, phase conjugation, and scanning over large volumes of the translucent material to be scanned,

This invention enables intracranial blood flow measurements based on waveforms generated from optical imaging. Coherent light is directed in the head. Sequential images of exit signals are captured at intervals. Coherence values of the sequential images are determined. The coherence values are combined into a waveform and intracranial blood flow is determined based on the waveform.

This invention enables intracranial blood flow measurements based on waveforms generated from optical imaging. Coherent light is directed in the head. Sequential images of exit signals are captured at intervals. Coherence values of the sequential images are determined. The coherence values are combined into a waveform and intracranial blood flow is determined based on the waveform.

This invention provides a Large Vessel Occlusion (LVO) event notification to a medical center that is best positioned (in drive-time and in medical treatment capability) to provide stroke care to a patient. This reduces the time to medical care and allows the medical center to prepare for the patient's arrival. In stroke care. every second matters for patient outcomes.

This invention generates a Large Vessel Occlusion alert based on optical imaging. More specifically, a shallow optical measurement (e.g. 7 mm between light source and detector) and a deeper optical measurement (e.g. 30 mm between light source and detector) are made in the head. A ratio of the differences between shallow and deep measurements generated the LVO alert that may be provided to a screen to diagnose the patient. A head mounted medical device may perform the optical readings. In an implementation, the blood flow to the superficial temporal artery (STA) is temporary occluded to assist in the measurements.

This invention generates a Large Vessel Occlusion alert based on optical imaging. More specifically, a shallow optical measurement (e.g. 7 mm between light source and detector) and a deeper optical measurement (e.g. 30 mm between light source and detector) are made in the head. A ratio of the differences between shallow and deep measurements generated the LVO alert that may be provided to a screen to diagnose the patient. A head mounted medical device may perform the optical readings. In an implementation, the blood flow to the superficial temporal artery (STA) is temporary occluded to assist in the measurements.

This invention generates a Large Vessel Occlusion alert based on optical imaging. More specifically, a shallow optical measurement (e.g. 7 mm between light source and detector) and a deeper optical measurement (e.g. 30 mm between light source and detector) are made in the head. A ratio of the differences between shallow and deep measurements generated the LVO alert that may be provided to a screen to diagnose the patient. A head mounted medical device may perform the optical readings. In an implementation, the blood flow to the superficial temporal artery (STA) is temporary occluded to assist in the measurements.

This invention generates a Large Vessel Occlusion alert based on optical imaging More specifically, a shallow optical measurement (e.g. 7 mm between light source and detector) and a deeper optical measurement (e.g. 30 mm between light source and detector) are made in the head. A ratio of the differences between shallow and deep measurements generated the LVO alert that may be provided to a screen to diagnose the patient. A head mounted medical device may perform the optical readings. In an implementation, the blood flow to the superficial temporal artery (STA) is temporary occluded to assist in the measurements.

This invention provides transcranial therapy with ultrasound. This may be an alternative to Transcranial Magnetic Stimulation (TMS). Depending on an input, different ultrasound profiles (e.g. power, duration, duty cycle, frequency) are utilized and different regions of the brain are targeted. These different therapies may stimulate certain behaviors (e.g. executive function) or inhibit other behaviors (e.g. addiction).

This invention provides transcranial therapy with ultrasound. This may be an alternative to Transcranial Magnetic Stimulation (TMS). Depending on an input, different ultrasound profiles (e.g. power, duration, duty cycle, frequency) are utilized and different regions of the brain are targeted. These different therapies may stimulate certain behaviors (e.g. executive function) or inhibit other behaviors (e.g. addiction).

This invention uses ultrasonic signals to harmonically excite (shatter) abnormal tissue while propagating through healthy tissue without damaging the healthy tissue. In this way, the ultrasound signals can target the destruction of tumors (abnormal tissue). Selecting the correct resonant ultrasound frequency to destroy the tumor may include additional medical imaging (MRI) to assisting in identify the abnormal tissue and mapping the tumor position in the tissue. Once identified, the resonant ultrasound frequency can be selected that will shatter the tumor.

This invention uses ultrasonic signals to harmonically excite (shatter) abnormal tissue while propagating through healthy tissue without damaging the healthy tissue. In this way, the ultrasound signals can target the destruction of tumors (abnormal tissue). Selecting the correct resonant ultrasound frequency to destroy the tumor may include additional medical imaging (MRI) to assisting in identify the abnormal tissue and mapping the tumor position in the tissue. Once identified, the resonant ultrasound frequency can be selected that will shatter the tumor.

This invention uses ultrasonic signals to harmonically excite (shatter) abnormal tissue in conjunction with an anti-tumor agent to increase the susceptibility of a tumor. The anti-tumor agent is an immunotherapy or a large molecule anti-tumor biological agent (e.g. T cell therapy). Pairing the anti-tumor agent with the ultrasonic signals may increase neoantigen release from the tumor that primes an immune response from the patient. In this way, this therapy functions as an in situ vaccination against the tumor cells.

This invention uses ultrasonic signals to harmonically excite (shatter) abnormal tissue in conjunction with an anti-tumor agent to increase the susceptibility of a tumor. The anti-tumor agent is an immunotherapy or a large molecule anti-tumor biological agent (e.g. T cell therapy). Pairing the anti-tumor agent with the ultrasonic signals may increase neoantigen release from the tumor that primes an immune response from the patient. In this way, this therapy functions as an in situ vaccination against the tumor cells.

This invention uses ultrasonic signals to harmonically excite (shatter) abnormal tissue in conjunction with an anti-tumor agent to increase the susceptibility of a tumor. The anti-tumor agent is an immunotherapy or a large molecule anti-tumor biological agent (e.g. T cell therapy). Pairing the anti-tumor agent with the ultrasonic signals may increase neoantigen release from the tumor that primes an immune response from the patient. In this way, this therapy functions as an in situ vaccination against the tumor cells.

This invention is a therapy system that can be worn on the head to liquify blood clots that may cause (or be causing) a Large Vessel Occlusion. Ultrasound in a head wearable device directs a resonant ultrasound frequency to the blood clot to harmonically excite the blood clot and liquify the blood clot to become soluble to blood flowing through the head. A laser and a light sensor may be included in the wearable device to monitor the blood flow of the head and the ultrasound signal may be modulated in response to the optical imaging.

This invention is a therapy system that can be worn on the head to liquify blood clots that may cause (or be causing) a Large Vessel Occlusion. Ultrasound in a head wearable device directs a resonant ultrasound frequency to the blood clot to harmonically excite the blood clot and liquify the blood clot to become soluble to blood flowing through the head. A laser and a light sensor may be included in the wearable device to monitor the blood flow of the head and the ultrasound signal may be modulated in response to the optical imaging.

This invention is a therapy system that can be worn on the head to liquify blood clots that may cause (or be causing) a Large Vessel Occlusion. Ultrasound in a head wearable device directs a resonant ultrasound frequency to the blood clot to harmonically excite the blood clot and liquify the blood clot to become soluble to blood flowing through the head. A laser and a light sensor may be included in the wearable device to monitor the blood flow of the head and the ultrasound signal may be modulated in response to the optical imaging.

This invention stabilizes the wavelength of pulsed lasers which is particularly important in speckle contrast measurements. A major cause of instability is temperature rise in the laser. In this invention, laser oscillator pre-pulses and laser amplifier pre-pulses are interleaved to stabilize the temperature of the laser. Specifically, the temperatures of the laser amplifier and laser oscillator rise in the pre- lasing stage to approximate the temperature of the lasing stage. In the pre-lasing stage, the laser oscillator and the laser amplifier are not driven at the same time so that no pulses are emitted during the pre-lasing stage. A further enhancement to this invention includes reducing the laser oscillator current and delaying the reduction of the laser oscillator current into the lasing stage. See FIG. 10.

This invention stabilizes the wavelength of pulsed lasers which is particularly important in speckle contrast measurements. A major cause of instability is temperature rise in the laser. In this invention, laser oscillator pre-pulses and laser amplifier pre-pulses are interleaved to stabilize the temperature of the laser. Specifically, the temperatures of the laser amplifier and laser oscillator rise in the pre- lasing stage to approximate the temperature of the lasing stage. In the pre-lasing stage, the laser oscillator and the laser amplifier are not driven at the same time so that no pulses are emitted during the pre-lasing stage. A further enhancement to this invention includes reducing the laser oscillator current and delaying the reduction of the laser oscillator current into the lasing stage. See FIG. 10.

This invention discloses methods and apparature to allow focusing and imaging of translucent materials with decreased size and complexity with improved focusing and imaging, so as to allow use in many fields. Many embodiments are discussed for use of this technology in a wide range of fields