US20160081558A1 - Method of photoacoustic microscopy with lateral resolution of microvasculature - Google Patents
Method of photoacoustic microscopy with lateral resolution of microvasculature Download PDFInfo
- Publication number
- US20160081558A1 US20160081558A1 US14/950,189 US201514950189A US2016081558A1 US 20160081558 A1 US20160081558 A1 US 20160081558A1 US 201514950189 A US201514950189 A US 201514950189A US 2016081558 A1 US2016081558 A1 US 2016081558A1
- Authority
- US
- United States
- Prior art keywords
- optical
- signal
- light pulse
- photoacoustic
- focusing
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Abandoned
Links
Images
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/0093—Detecting, measuring or recording by applying one single type of energy and measuring its conversion into another type of energy
- A61B5/0095—Detecting, measuring or recording by applying one single type of energy and measuring its conversion into another type of energy by applying light and detecting acoustic waves, i.e. photoacoustic measurements
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/0059—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/0059—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence
- A61B5/0062—Arrangements for scanning
- A61B5/0068—Confocal scanning
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/0059—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence
- A61B5/0082—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence adapted for particular medical purposes
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/02—Detecting, measuring or recording pulse, heart rate, blood pressure or blood flow; Combined pulse/heart-rate/blood pressure determination; Evaluating a cardiovascular condition not otherwise provided for, e.g. using combinations of techniques provided for in this group with electrocardiography or electroauscultation; Heart catheters for measuring blood pressure
- A61B5/02007—Evaluating blood vessel condition, e.g. elasticity, compliance
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
- A61B5/14542—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue for measuring blood gases
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
- A61B5/14546—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue for measuring analytes not otherwise provided for, e.g. ions, cytochromes
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/44—Detecting, measuring or recording for evaluating the integumentary system, e.g. skin, hair or nails
- A61B5/441—Skin evaluation, e.g. for skin disorder diagnosis
- A61B5/444—Evaluating skin marks, e.g. mole, nevi, tumour, scar
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/48—Other medical applications
- A61B5/4848—Monitoring or testing the effects of treatment, e.g. of medication
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
- G01N21/17—Systems in which incident light is modified in accordance with the properties of the material investigated
- G01N21/1702—Systems in which incident light is modified in accordance with the properties of the material investigated with opto-acoustic detection, e.g. for gases or analysing solids
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N29/00—Investigating or analysing materials by the use of ultrasonic, sonic or infrasonic waves; Visualisation of the interior of objects by transmitting ultrasonic or sonic waves through the object
- G01N29/04—Analysing solids
- G01N29/06—Visualisation of the interior, e.g. acoustic microscopy
- G01N29/0654—Imaging
- G01N29/0681—Imaging by acoustic microscopy, e.g. scanning acoustic microscopy
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N29/00—Investigating or analysing materials by the use of ultrasonic, sonic or infrasonic waves; Visualisation of the interior of objects by transmitting ultrasonic or sonic waves through the object
- G01N29/22—Details, e.g. general constructional or apparatus details
- G01N29/24—Probes
- G01N29/2418—Probes using optoacoustic interaction with the material, e.g. laser radiation, photoacoustics
-
- G—PHYSICS
- G02—OPTICS
- G02B—OPTICAL ELEMENTS, SYSTEMS OR APPARATUS
- G02B21/00—Microscopes
- G02B21/0004—Microscopes specially adapted for specific applications
- G02B21/002—Scanning microscopes
- G02B21/0024—Confocal scanning microscopes (CSOMs) or confocal "macroscopes"; Accessories which are not restricted to use with CSOMs, e.g. sample holders
- G02B21/0028—Confocal scanning microscopes (CSOMs) or confocal "macroscopes"; Accessories which are not restricted to use with CSOMs, e.g. sample holders specially adapted for specific applications, e.g. for endoscopes, ophthalmoscopes, attachments to conventional microscopes
-
- G—PHYSICS
- G02—OPTICS
- G02B—OPTICAL ELEMENTS, SYSTEMS OR APPARATUS
- G02B21/00—Microscopes
- G02B21/0004—Microscopes specially adapted for specific applications
- G02B21/002—Scanning microscopes
- G02B21/0024—Confocal scanning microscopes (CSOMs) or confocal "macroscopes"; Accessories which are not restricted to use with CSOMs, e.g. sample holders
- G02B21/008—Details of detection or image processing, including general computer control
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B90/00—Instruments, implements or accessories specially adapted for surgery or diagnosis and not covered by any of the groups A61B1/00 - A61B50/00, e.g. for luxation treatment or for protecting wound edges
- A61B90/30—Devices for illuminating a surgical field, the devices having an interrelation with other surgical devices or with a surgical procedure
- A61B2090/306—Devices for illuminating a surgical field, the devices having an interrelation with other surgical devices or with a surgical procedure using optical fibres
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
- A61B8/48—Diagnostic techniques
- A61B8/485—Diagnostic techniques involving measuring strain or elastic properties
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N2291/00—Indexing codes associated with group G01N29/00
- G01N2291/02—Indexing codes associated with the analysed material
- G01N2291/028—Material parameters
- G01N2291/02836—Flow rate, liquid level
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N2291/00—Indexing codes associated with group G01N29/00
- G01N2291/02—Indexing codes associated with the analysed material
- G01N2291/028—Material parameters
- G01N2291/02872—Pressure
Landscapes
- Health & Medical Sciences (AREA)
- Life Sciences & Earth Sciences (AREA)
- Physics & Mathematics (AREA)
- General Health & Medical Sciences (AREA)
- Pathology (AREA)
- Engineering & Computer Science (AREA)
- Surgery (AREA)
- Biophysics (AREA)
- Animal Behavior & Ethology (AREA)
- Molecular Biology (AREA)
- Public Health (AREA)
- Veterinary Medicine (AREA)
- Biomedical Technology (AREA)
- Heart & Thoracic Surgery (AREA)
- Medical Informatics (AREA)
- General Physics & Mathematics (AREA)
- Analytical Chemistry (AREA)
- Chemical & Material Sciences (AREA)
- Optics & Photonics (AREA)
- Immunology (AREA)
- Biochemistry (AREA)
- Acoustics & Sound (AREA)
- Radiology & Medical Imaging (AREA)
- Ophthalmology & Optometry (AREA)
- General Engineering & Computer Science (AREA)
- Computer Vision & Pattern Recognition (AREA)
- Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
- Cardiology (AREA)
- Dermatology (AREA)
- Physiology (AREA)
- Vascular Medicine (AREA)
- Investigating Or Analyzing Materials By The Use Of Ultrasonic Waves (AREA)
- Ultra Sonic Daignosis Equipment (AREA)
- Investigating Or Analysing Materials By Optical Means (AREA)
- Microscoopes, Condenser (AREA)
- Measurement Of The Respiration, Hearing Ability, Form, And Blood Characteristics Of Living Organisms (AREA)
Abstract
Description
- This application is a divisional of U.S. patent application Ser. No. 13/874,653 filed Jun. 1, 2013, which is a divisional of U.S. patent application Ser. No. 12/739,589 filed Jun. 28, 2010, which is a U.S. National Phase Patent Application of International Application Serial No. PCT/US2008/081167 filed Oct. 24, 2008, which claims priority from U.S. Provisional Patent Application No. 60/982,624 filed Oct. 25, 2007, all of which are incorporated herein by reference in their entireties.
- This invention was made with government support under grants R01 EB000712 and R01 NS46214, both awarded by the U.S. National Institutes of Health. The government has certain rights in the invention.
- The field of the invention relates generally to noninvasive imaging and, more particularly, to imaging an area with an object using confocal photoacoustic imaging.
- The capability of noninvasively imaging capillaries, the smallest blood vessels, in vivo has long been desired by biologists at least because it provides a window to study fundamental physiological phenomena, such as neurovascular coupling, on a microscopic level. Existing imaging modalities, however, are unable to simultaneously provide sensitivity, contrast, and spatial resolution sufficient to noninvasively image capillaries.
- In one aspect, a method for obtaining a 3-D OR-PAM image of microvasculature within a region of interest of a subject is provided. The method includes: focusing a first light pulse at a first depth beneath a first surface position within the region of interest; receiving a first PA signal in response to the first light pulse; focusing a second light pulse at a second depth beneath the first surface position within the region of interest; receiving a second PA signal in response to the second light pulse; and forming the 3-D OR-PAM image by combining the first PA signal and the second PA signal.
- In another aspect, a method for monitoring a treatment of a port wine stain of a subject is provided. The methods includes: obtaining a baseline 3-D OR-PAM image of the port wine stain prior to the treatment; obtaining at least one additional 3-D OR-PAM image of the port wine stain after at least a portion of the treatment; and comparing the baseline and the at least one additional 3-D OR-PAM images to detect changes within the port wine stain after at least a portion of the treatment. Each of the baseline and at least one additional 3-D OR-PAM images are obtained by: focusing at least one first light pulse at a first depth beneath at least one surface position within the port wine stain; receiving at least one first PA signal in response to the at least one first light pulse; focusing at least one second light pulse at a second depth beneath the at least one surface position within the port wine stain; receiving at least one second PA signal in response to the at least one second light pulse; and forming the first 3-D OR-PAM image by combining the at least one first PA signal and the at least one second PA signal.
- Aspects of the invention may be better understood by referring to the following description in conjunction with the accompanying drawings.
-
FIG. 1 is a diagram of a photoacoustic sensor that may be used with an imaging system. -
FIG. 2 is a block diagram of a system that uses confocal photoacoustic microscopy. -
FIG. 3 is a diagram of a photoacoustic sensor that may be used with the imaging system shown inFIG. 2 . -
FIG. 4 is a diagram of an alternative photoacoustic sensor that may be used with the imaging system shown inFIG. 2 . -
FIG. 5 is a diagram of a second alternative photoacoustic sensor that may be used with the imaging system shown inFIG. 2 . -
FIG. 6 is a schematic diagram of a third alternative photoacoustic sensor that may be used with the imaging system shown inFIG. 2 . -
FIG. 7 is a schematic diagram of a fourth alternative photoacoustic sensor that may be used with the imaging system shown inFIG. 2 . -
FIG. 8 is a diagram of a fifth alternative photoacoustic sensor that may be used with the imaging system shown inFIG. 2 . -
FIG. 9 is a schematic diagram of a sixth alternative photoacoustic sensor that may be used with the imaging system shown inFIG. 2 . -
FIG. 10 is a schematic diagram of a seventh alternative photoacoustic sensor that may be used with the imaging system shown inFIG. 2 . -
FIG. 11 is a schematic diagram of an eighth photoacoustic sensor that may be used with the imaging system shown inFIG. 2 . -
FIGS. 12A-12C are images representing a lateral resolution measurement by the imaging system using a resolution test target immersed in clear liquid. -
FIGS. 13A and 13B are images representing a measurement of the imaging depth by the imaging system. -
FIGS. 14A and 14B are photoacoustic images of a microvasculature by the imaging system. -
FIG. 14C is a photograph of the microvasculature ofFIGS. 14A and 14B , taken from a transmission microscope. -
FIGS. 15A and 15B are maximum amplitude projection (MAP) images acquired before and after a high-intensity laser treatment. -
FIG. 16A is an in vivo image of a capillary bed captured using the imaging system. -
FIG. 16B is an in vivo image of multiple levels of blood vessel bifurcations captured using the imaging system. - While the making and using of various embodiments of the invention are discussed in detail below, it should be appreciated that the presently described embodiments provide many applicable inventive concepts that may be embodied in a wide variety of contexts. The embodiments discussed herein are merely illustrative of exemplary ways to make and use embodiments of the invention and do not delimit the scope of the invention.
- To facilitate the understanding of the presently described embodiments, a number of terms are defined below. Terms defined herein have meanings as commonly understood by a person of ordinary skill in the areas relevant to aspects of the invention. Terms such as “a,” “an,” “the,” and “said” are not intended to refer to only a singular entity, but include the general class of which a specific example may be used for illustration and are intended to mean that there are one or more of the elements. The terms “comprising,” “including,” and “having” are intended to be inclusive and mean that there may be additional elements other than the listed elements.
- The order of execution or performance of the operations in embodiments of the invention illustrated and described herein is not essential, unless otherwise specified. That is, the operations may be performed in any order, unless otherwise specified, and embodiments of the invention may include additional or fewer operations than those disclosed herein. For example, it is contemplated that executing or performing a particular operation before, contemporaneously with, or after another operation is within the scope of aspects of the invention.
- The terminology herein is used to describe embodiments of the invention, but their usage does not delimit the invention.
- In embodiments of the invention, the terms used herein follow the definitions recommended by the Optical Society of America (OCIS codes).
- In embodiments of the invention, the term “photoacoustic microscopy” includes, but is not limited to, a photoacoustic imaging technology that detects pressure waves generated by light absorption in the volume of a material, such as, but not limited to biological tissue, and propagated to the surface of the material. Photoacoustic microscopy includes, but is not limited to, a method for obtaining images of the optical contrast of a material by detecting acoustic and/or pressure waves traveling from an object under investigation. Moreover, the term “photoacoustic microscopy” includes, but is not limited to, detection of the pressure waves that are still within the object.
- In embodiments of the invention, the term “photoacoustic tomography” includes, but is not limited to, a photoacoustic imaging technology that detects acoustic and/or pressure waves generated by light absorption in the volume of a material, such as, but not limited to biological tissue, and propagated to the surface of the material.
- In embodiments of the invention, the term “piezoelectric detectors” includes, but is not limited to, detectors of acoustic waves utilizing the principle of electric charge generation upon a change of volume within crystals subjected to a pressure wave.
- In embodiments of the invention, the terms “reflection mode” and “transmission mode” includes, but is not limited to, a laser photoacoustic microscopy system that employs the detection of acoustic and/or pressure waves transmitted from a volume from which the waves are generated to an optically irradiated surface and a surface that is opposite to, or substantially different from, the irradiated surface, respectively.
- In embodiments of the invention, the term “time-resolved detection” includes, but is not limited to, the recording of the time history of a pressure wave with a temporal resolution sufficient to reconstruct the pressure wave profile.
- In embodiments of the invention, the term “transducer array” includes, but is not limited to, an array of ultrasonic transducers.
- In embodiments of the invention, the terms “focused ultrasonic detector,” “focused ultrasonic transducer,” and “focused piezoelectric transducer” include, but are not limited to, a curved ultrasonic transducer with a hemispherical surface or a planar ultrasonic transducer with an acoustic lens attached or an electronically focused ultrasonic array transducer.
- In embodiments of the invention, the term “diffraction-limited focus” includes, but is not limited to, a best possible focusing of light within limitations imposed by diffraction.
- In embodiments of the invention, the term “confocal” includes, but is not limited to, a situation when the focus of the illumination system coincides with the focus of the detection system.
- The embodiments described herein relate to noninvasively imaging capillaries. Some of the embodiments relate to microscopic photoacoustic imaging using focused optical illumination and focused ultrasonic detection. For example, an embodiment performs optical-resolution photoacoustic microscopy (OR-PAM), which facilitates providing a lateral resolution of 5 micrometers (μm) and a maximum imaging depth of greater than 0.7 millimeters (mm) based on endogenous optical absorption contrast. In vivo images of healthy capillary networks and laser coagulated microvessels in mouse ears, for example, are demonstrated as examples of applications of OR-PAM in biomedical research.
- In an embodiment, the lateral resolution is dominantly determined by the optical focus. A tightly focused optical illumination produces a local temperature rise due to light absorption. The temperature rise leads to thermal expansion, which results in photoacoustic emission. The photoacoustic emission may be detected by a high-frequency large numerical-aperture spherically focused ultrasonic transducer that is coaxial and confocal with the light focusing system. The photoacoustic emission may also be measured by an ultrasonic transducer array, a phase sensitive optical coherence tomography apparatus, a laser optical interferometer, and/or a capacitive surface displacement sensor. By focusing light to a focal spot of several micrometers in diameter, embodiments of the invention significantly improve the image resolution of photoacoustic microscopy of biological tissue or other optically scattering media. It combines the high spatial resolution of optical confocal microscopy and the high optical absorption contrast of photoacoustic tomography.
- The embodiments described herein provide for reflection-mode microscopic photoacoustic imaging using focused optical illumination. Embodiments of the invention use a nearly diffraction-limited focused optical illumination to achieve high spatial resolution. Embodiments of the invention use a confocal arrangement between the optical focus and the ultrasonic focus of a high-frequency large numerical-aperture (NA) spherically focused ultrasonic transducer to achieve high sensitivity. The ultrasonic transducer may be replaced with another detector capable of measuring local thermal expansion. By tightly focusing light, the lateral resolution limitations of existing photoacoustic microscopy based on the resolution of the ultrasonic focusing system may be overcome. In addition, because a photoacoustic signal is proportional to the optical fluence at the target, the currently described embodiments require only a low laser pulse energy and, hence, may be made relatively compact, fast, and inexpensive. In the exemplary embodiment, a laser pulse energy of approximately 100 nanojoules (nJ) may be used.
- Moreover, exemplary embodiments utilize optical focusing and time-resolved detection of laser-induced pressure waves to obtain three-dimensional images of the distribution of optical-absorption contrast within a sampling volume. The exemplary embodiments provide non-invasive imaging of scattering media, such as, but not limited to, biological tissue in vivo. The exemplary embodiments provide non-invasive imaging up to approximately one optical transport mean free path deep. For most biological tissue, an optical transport mean free path is approximately 1.0 millimeter (mm) In the exemplary embodiment, resolution on the order of 1.0 micrometer (μm) is attainable. Further, the exemplary embodiment images optical-absorption contrast in biological tissue up to approximately 0.7 mm deep with a lateral resolution of approximately 5.0 μm. In embodiments of the invention, a large numerical-aperture (NA) spherically focused ultrasonic transducer is used in a confocal coaxial arrangement with the light focusing optics to facilitate providing high axial resolution of between 10.0 and 15.0 μm.
- An imaging procedure, which uses a confocal photoacoustic imaging system, is one of the possible embodiments and is aimed at medical and biological applications. The presently described embodiments are complementary to the structural information that may be obtained from pure optical and ultrasonic imaging technologies and may be used for diagnostic, monitoring or research purposes. Applications of the technology include, but are not limited to, the imaging of arteries, veins, capillaries (the smallest blood vessels), pigmented tumors such as melanomas, and sebaceous glands in vivo in humans or animals. The presently described embodiments may use the spectral properties of intrinsic optical contrast to monitor blood oxygenation (oxygen saturation of hemoglobin), blood volume (total hemoglobin concentration), and even the metabolic rate of oxygen consumption; it may also use the spectral properties of a variety of dyes or other contrast agents to obtain additional functional or molecular-specific information. In other words, the presently described embodiments are capable of functional and molecular imaging. Further, the presently described embodiments may be used to monitor possible tissue changes during x-ray radiation therapy, chemotherapy, or other treatment. In addition, presently described embodiments may also be used to monitor topical application of cosmetics, skin creams, sun-blocks or other skin treatment products. The presently described embodiments, when miniaturized, may also be used endoscopically, e.g., for the imaging of atherosclerotic lesions in blood vessels.
- Further, the presently described embodiments provide a method of characterizing a target within a tissue by focusing one or more laser pulses on the region of interest in the tissue so as to penetrate the tissue and illuminate the region of interest, receiving the pressure waves induced in the object by optical absorption using one or more ultrasonic transducers that are focused on the same region of interest, and recording the received acoustic waves so that the structure or composition of the object may be imaged. The one or more laser pulses are focused by a microscope objective lens or a similar tightly focusing optical system, which typically includes an optical assembly of lenses and/or mirrors, which converges the one or more laser pulses towards the focal point of the ultrasonic transducer. The focusing device may also use one or more optical spatial filters, which may be a diaphragm or a single-mode fiber, to reduce the focal spot of the optical system to the smallest possible size so that the highest possible spatial resolution may be achieved. The focused one or more laser pulses selectively heat the region of interest, causing the object to expand and produce a pressure wave whose temporal profile reflects the optical absorption and thermo-mechanical properties of the target. Alternatively, an annular array of ultrasonic transducers may be used along the tissue to enhance a depth of field of an imaging system by using synthetic aperture image reconstruction. The signal recording includes digitizing the received acoustic waves and transferring the digitized acoustic waves to a computer for analysis. The image of the object is formed from the recorded acoustic waves.
- In addition, the presently described embodiments may also include an electronic system in communication with the focusing device, the one or more ultrasonic transducers, or a combination thereof. In one embodiment, the electronic system includes an XYZ or circular scanner or scanners, an amplifier, a digitizer, a laser wavelength tuning electronics, a computer, a processor, a display, a storage device, or combination thereof. One or more component of the electronic system may be in communication remotely with the other components of the electronic system, the apparatus, or both.
-
FIG. 1 shows a schematic of an exemplary focusingassembly 100 which uses the confocal photoacoustic microscopy method. The light out of the dye laser is focused by acondenser lens 1 on a diaphragm (pinhole) 2 for spatial filtering.Sampling beam splitter 10 is used to monitor the laser output power through photo-detector 11 and to optically image the object surface through eyepiece or aligningoptics 12 for alignment. The light coming out of the spatial filter is focused by microscopeobjective lens 3 ontoobject 13 throughbeam separating element acoustic lens 8.Correction lens 5 placed on top of the beam separation element compensates for the aberrations introduced by the prisms and the acoustic lens. The distance between the pinhole and the objective lens is approximately 400 millimeters (mm), which gives an optical focusing spot size of approximately 3.7 micrometers (μm) in diameter and a focal zone of approximately 200 μm in water. The laser pulse energy measured after the objective lens is approximately 100 nanojoules (nJ). The beam separation element consists of an isoscelestriangular prism 6 with an apex angle of approximately 52.5° and a rhomboidal 52.5°prism 7.Prisms Gap 9 is filled with an optical refractive-index-matching, low-acoustic-impedance, nonvolatile liquid such as 1000 cSt silicone oil, commercially available from Clearco Products. The silicone oil and the glass have a good optical refractive index match (glass: 1.5; silicone oil: 1.4) but a large acoustic impedance mismatch (glass: 12.1×106 N·s/m3; silicone oil: 0.95×106 N·s/m3). As a result, the silicone oil layer is optically transparent but acted as an acoustic reflector. The photoacoustic signal emitted by the target is transformed by the acoustic lens, having a radius of curvature of approximately 5.2 mm, a diameter of approximately 6.35 mm, a NA of approximately 0.46 in water, and an ultrasonic focal spot size of approximately 27 μm, into a plane elastic wave inrhomboidal prism 7 and is then detected by the high-frequency direct-contactultrasonic transducer 4 such as a model V2012-BC transducer, commercially available from Panametrics-NDT with a center frequency of approximately 75 MHz, a bandwidth of approximately 80%, and an active element diameter of approximately 6.35 mm. Within the bandwidth of theultrasonic transducer 4, ultrasonic absorption in silicone oil is high enough to dampen ultrasonic reverberations in the matching layer and thus minimize interferences to the image. -
FIG. 2 is a block diagram of asystem 200 based on confocal photoacoustic microscopy, which is capable of contour scanning and quantitative spectroscopic measurement. The system includes a pulsedtunable laser 1 including a tunable laser pumped by a Q-switched laser, a focusingassembly 2, one or moreultrasonic transducers 4, and an electronic system. The electronic system includes data acquisition personal computer (PC) 3,motion controller 9, first andsecond scanners amplifier 5, and data acquisition subsystem (DAQ) 6, which includes a signal conditioner and a digitizer. Focusingassembly 2 receives one or more laser pulses and focuses the one or more laser pulses into an area inside thesample object 10 so as to penetrate the tissue and illuminate the region of interest. The one or moreultrasonic transducers 4 are focused on the same the region of interest and receive the acoustic or pressure waves induced in the region of interest by the one or more laser pulses. The electronic system records and processes the received acoustic or pressure waves. The laser pulse generation, data acquisition, and object scanning are synchronized with the pulses produced by the motor controller at programmed locations of the laser focus with respect to object 10. As described above, the focusingassembly 2 includes an optical assembly of lenses and/or mirrors that focuses one or more laser beams on the object in such a way that the focal point of the optical focusing device coincides with that of the one or more ultrasonic transducers. - The focusing assembly is placed on an XYZ translation stage to perform raster scanning along the object surface with simultaneous adjustment of the sensor's axial position to compensate for the curvature of the object surface. Other embodiments may use different ways of image formation, which include, but are not limited to, circular scanning, sector scanning, optical scanning, electronic focusing using a transducer array, and array-based image reconstruction. The recorded pressure-wave time histories are displayed by the computer versus the focusing assembly position to construct a three dimensional image of the distribution of the optical contrast within the tissue, i.e., a three dimensional tomographic image of the object.
-
System 200 employs a tunable dye laser, such as a model CBR-D laser, commercially available from Sirah, pumped by a neodymium-doped yttrium lithium flouride (Nd:YLF) laser, such as the INNOSLAB laser, commercially available from Edgewave, as the irradiation source. The laser pulse duration is approximately 7 nanoseconds (ns) and the pulse repetition rate, which is controlled by the external triggering signal, is as high as approximately 2 kilohertz (kHz). In alternative embodiments, a plurality of sources of penetrating radiation, which may be confined to or concentrated in a small volume within the object, may be used. Such sources include, but are not limited to, pulsed lasers, flash lamps, other pulsed electromagnetic sources, particle beams, or their intensity-modulated continuous-wave counterparts. - The one or more focused short laser pulses are delivered to an object (e.g., human or animal body, tissue or organ) under investigation, where a small area of the object inside the focal area of the ultrasonic transducer is illuminated. The laser wavelength is selected as a compromise between the desired light penetration depth and the contrast between the structures of interest and the surrounding medium. Light absorption by the internal structures causes a transient temperature rise which, due to thermoelastic expansion of the medium, produces elastic waves that may travel through the medium.
- High-frequency ultrasonic waves generated in tissue by the laser pulse are recorded and analyzed by a PC to form a three-dimensional image. The shape and dimensions of the optical-contrast structures are generally determined from the temporal profile of the laser-induced ultrasonic waves and the position of the focusing assembly. Ordinarily, a raster scan by the focusing assembly is used to form a three-dimensional image. However, a transducer array may be used to reduce the time of scanning and the total light exposure. When the tissue under investigation is an internal organ, the optical fiber and ultrasonic transducer may be incorporated in an endoscope and positioned inside the body. The following examples will be provided for the purpose of illustrating various embodiments of the invention and are not meant to limit the present invention in any fashion.
- As illustrated in
FIGS. 3-6 , the presently described embodiments provide an optical resolution confocal microscopic photoacoustic imaging technology to image biological tissues in vivo. The exemplary embodiment has a lateral resolution as high as approximately 5 μm and a maximum imaging depth of approximately 0.7 mm. In alternative embodiments, the image resolution may be further improved by increasing the frequency of the ultrasonic transducer and the numerical aperture of the optical objective lens perhaps at the cost of imaging depth. The photoacoustic images shown inFIGS. 12-16 were obtained with minimal signal averaging and, therefore, could be further improved by averaging, at the expense of data acquisition time, in another embodiment of the invention. The current imaging speed is limited by the pulse repetition rate of the laser. Because lasers with pulse repetition rates of up to 100 KHz are now available, other embodiments involve faster photoacoustic imaging, which can reduce motion artifacts, and extensive signal averaging. - The presently described embodiments include any realization of light focusing using any kind of mirrors, lenses, fibers, and diaphragms that may produce well focused (preferably diffraction-limited) illumination confined to the focal area of the focused ultrasonic transducer. The presently described embodiments also cover any confocal photoacoustic techniques with any light delivery and detection arrangements in which the lateral resolution is defined by the focusing of the incident radiation rather than the acoustic detection unit.
- One or more of the following embodiments may be used to implement laser focusing for the purpose described herein: (1) an optical microscope objective lens that focuses a well-collimated single-mode lased beam into a nearly diffraction-limited point, (2) an objective lens that forms an image of a small pinhole on the region of interest, (3) a focusing system in which a single-mode optical fiber is used instead of pinhole, (4) a focusing system in which an oscillating mirror scans the optical focus rapidly within the larger focal area of the ultrasonic transducer. The following embodiments, and further alternative embodiments, may also be used to implement laser focusing for further, undescribed purposes. Various examples of the focusing assembly will now be described in reference to
FIGS. 3-10 , wherein the focusing assembly includes, for example, an optical focusing device, and one or more ultrasonic transducers in the piezoelectric, optical, or another form. -
FIG. 3 is a diagram of a focusingassembly 300 of imaging system 200 (shown inFIG. 2 ). A custom-made cubic beam splitter or right-angle prism 4 with a sub-micron reflectivealuminum coating layer 6 sandwiched between the two prisms is used to couple the optical and ultrasonic radiations. A pair of opticalobjective lenses 1 focuses the laser light from the single-mode optical fiber onto the region of interest inside the object, wheremetal coating 6 is used to reflect the optical beam. Asampling beam splitter 8 is placed between theobjective lenses 1 to monitor the laser output power with a photo-detector 9 and to view the object surface for alignment with an eyepiece or aligningoptics 10. Ultrasonic radiation emitted by theobject 11 passes through anacoustic lens 5, the aluminum optical reflector, and reaches anultrasonic transducer 2. -
FIG. 4 is a diagram of a focusingassembly 400 of imaging system 200 (shown inFIG. 2 ). A laser pulse from a pulse laser is focused by acondenser lens 1 on adiaphragm 2 for spatial filtering. The light coming out of thespatial filter 2 is reflected by anoscillating mirror 10, which performs fast optical scanning within the wider focal area of anultrasonic transducer 4. The laser beam is focused into an object by a microscopeobjective lens 3 through abeam splitting element acoustic lens 8. A thin plano-convexoptical lens 5 is placed on top of thebeam splitting element prisms acoustic lens 8. Thebeam splitting element triangular prism 6 with an apex angle of 52.5° and a rhomboidal 52.5°prism 7.Prisms weight silicone oil 9. The photoacoustic signal emitted by the object is transformed by theacoustic lens 8 into a plane elastic wave inrhomboidal prism 7. Ultrasonic reflection from the boundary ofsilicone oil 9 converts at least 98% of the energy of the incident longitudinal wave into that of a shear wave, which is transformed back into a longitudinal wave on the free surface ofrhomboidal prism 7 and then detected by high-frequency direct-contactultrasonic transducer 4. Because the acoustic focus is generally several times wider than the optical focus, taking advantage of fast optical scanning in this embodiment may significantly decrease the image acquisition time. -
FIG. 5 is a diagram of a focusingassembly 500 of imaging system 200 (shown inFIG. 2 ). An opticalobjective lens 2 focuses the output aperture of a single-modeoptical fiber 1 into the object through the optically clear slit window in a one-dimensionalultrasonic array transducer 4 placed on an opticallytransparent substrate 5.Substrate 5 serves as a wave-guide for acoustic waves and may have a cylindrical focus acoustic lens on its outer surface. The light coming out of the spatial filter is reflected by anoscillating mirror 3, which performs fast optical scanning Ultrasonic radiation emitted by the object is collected byultrasonic transducer array 4. A multiple-element piezoelectric transducer array may accelerate the image acquisition time in one dimension owing to the electronic focusing of the transducer array. The acoustic focus provided byassembly 500 follows the focal position of the laser beam without mechanically scanning the ultrasonic transducer over the object. Three-dimensional images may be acquired by mechanically translating the focusing assembly perpendicularly to the slit. -
FIG. 6 is a diagram of a focusingassembly 600 of imaging system 200 (shown inFIG. 2 ). The light output from a single-modeoptical fiber 1 is reflected by amirror scanner 2, collimated by an optical objective orexcitation lens 3, passed through adichroic mirror 4, and then focused by anotherobjective lens 5 on a region of interest through a Fabry-Perot etalon 6, which is acoustically coupled to the object.Mirror scanner 2 performs rapid 2D raster scanning of the object by sweeping the excitation laser beam. The photoacoustic wave from the object causes a transient strain distribution in Fabry-Perot etalon 6, which shifts its resonance wavelengths. Another laser (probing laser) 9 working at a different optical wavelength scans over Fabry-Perot etalon 6 through asecond mirror scanner 8, a secondobjective lens 7, anddichroic mirror 4 to read the strain distribution in Fabry-Perot etalon 6. The strain is then converted into the photoacoustic pressure distribution. In the exemplary embodiment, no mechanical scanning is necessary to form a 3D image of the object. -
FIG. 7 is a diagram of a focusingassembly 700 of imaging system 200 (shown inFIG. 2 ). An opticalobjective lens 4 focuses the output aperture of a single-modeoptical fiber 1 into a region of interest in an object to excite photoacoustic waves. A2D mirror scanner 3 is introduced in the optical path to perform 2D scanning of the object. A phase-sensitive optical coherence tomography (OCT)system 5 working at a different optical wavelength is focused on the same region of interest by the opticalobjective lens 2D mirror scanner 3. The two light beams of different wavelengths are coupled by adichroic mirror 2. The phase-sensitive OCT system measures, within the optical focal spot inside the object, the photothermal effect due to absorption of the laser pulse. The photothermal effect in the object is measured before pressure waves propagate to the surface of the object. In the exemplary embodiment, focusingassembly 700 forms a 3D image without translating the objective lens and does not require direct contact with the object. Correspondingly, it may be potentially very fast and may be used where non-contact imaging is preferred. -
FIG. 8 is a diagram of an alternative embodiment of the focusingassembly 800 suitable for hand-held operation. An opticalobjective lens 4 images the aperture of a single-modeoptical fiber 1 onto the region of interest in the object through an optically clear window in a spherically focusedultrasonic transducer 5. Asampling beam splitter 2 reflects a small portion of the incident light to monitor the laser output power with a photo-detector 3. The ultrasonic radiation emitted by the object is received by theultrasonic transducer 5. The photoacoustic assembly is mounted on apendulum 6, which is attached to aframe 8 through a flexible mount, such as aflat spring 7. The frame is water-tight and contains optically transparent acoustic coupling fluid, such as water, for light delivery and acoustic coupling. Moved by anactuator 9,pendulum 6 may perform sector scanning of the object rapidly. Aposition sensor 10 monitors the position of the optical focus and is used to synchronize the pulse laser so that image distortion due to varying scanning velocity is minimized. -
FIG. 9 is a diagram of another alternative embodiment of a focusingassembly 900 suitable for applications inside body cavities such as inter-vascular imaging. A laser pulse delivered by a single-mode fiber 1 is focused on the region of interest in the object by anoptical lens assembly 4 through an optically clear window in a spherically focusedultrasonic transducer 6.Ultrasonic transducer 6 together with a right-angled prism 5 is connected to aflexible shaft 2 located inside acatheter 3. Optically and acoustically transparentcircular window 7 allows the optical beam and ultrasonic radiation to pass freely to and from the object. Photoacoustic images are formed by rotating theshaft 2 with respect to the axis of the catheter and axially translating the catheter. -
FIG. 10 is a block diagram of another alternative embodiment of a focusingassembly 1000 which uses the confocal photoacoustic microscopy method simultaneously with optical confocal microscopy. The light coming out of the pulsed laser is focused by acondenser lens 1 on a diaphragm (pinhole) 2 for spatial filtering. A dichroic beam splitter ormirror 10 is used to monitor the laser output power with a photo-detector 11 and to form an optical fluorescence confocal image of the object. The optical fluorescence confocal imaging portion consists of a pinhole, or diaphragm, 12, a focusing system orlens 13, a low passoptical filter 15, and a photo-detector (such as a photomultiplier) 14. The light coming out of the spatial filter is focused by a microscopeobjective lens 3 on the object through a beam splitting element. The beam splitting element consists of an isoscelestriangular prism 6 with an apex angle of 52.5° and a rhomboidal 52.5°prism 7.Prisms Gap 9 is filled with refractive-index-matching, low-acoustic-impedance, nonvolatile liquid. Acorrection lens 5 is placed on top of the beam splitting element to compensate for aberrations introduced by the prisms and the acoustic lens. The photoacoustic signal emitted by the object is transformed by anacoustic lens 8 into a plane elastic wave inrhomboidal prism 7. Ultrasonic reflection from the boundary of the prism converts the incident longitudinal elastic wave into a shear wave. The shear wave propagates toward the free surface of the rhomboidal prism, where it is transformed back into a longitudinal wave and detected by a high-frequency direct-contactultrasonic transducer 4 for image formation and spectral measurements of the target. - The fusion of the optical confocal microscopy and photoacoustic microscopy provides complementary information about the object. One feature is the quantitative measurement of the optical absorption spectrum of the object by simultaneously using the fluorescence signal from the optical confocal microscope and the photoacoustic signal from the photoacoustic microscope. The quantitative measurement of the optical absorption spectrum of the object requires knowledge of the spectral variation of the excitation optical fluence at the focus, which may be measured using the fluorescent signals as illustrated below.
- In the exemplary embodiment, two excitation optical wavelengths are used. If a fluorescence dye is present, the detected fluorescence signal Vf(λxi, λm) at the i-th excitation wavelength and the emission wavelength λm is a product of the unknown local excitation optical fluence F(λxi), the concentration of dye C, the known molar optical absorption coefficient of the dye εaf(λxi), the quantum yield of the dye Q, and the fluorescence detection sensitivity Sf(λm). For i=1 and 2, the following ratio in Equation (1) is present:
-
- Therefore, the local excitation optical fluence ratio may be recovered as in Equation (2):
-
- Similarly, the detected photoacoustic signal Vpa(λxi) is a product of the local excitation optical fluence F(λxi), the optical absorption coefficient of dominantly absorbing hemoglobin μah(λxi), and the acoustic detection sensitivity Sa. Assuming that the hemoglobin absorbs much more than the fluorescent dye, the following ratio in Equation (3) is developed:
-
- From the above two equations, the ratio of the hemoglobin absorption coefficient may be recovered as in Equation (4):
-
- This ratio may be used to quantify the oxygen saturation of hemoglobin and the relative total concentration of hemoglobin. Of course, this example merely illustrates the principle, which may be extended to the measurement of other optical absorbers using two or more excitation optical wavelengths.
- The presently described embodiments may be used to estimate oxygen metabolism in tissues and organs, by combining measurements of blood flow and oxygenation into and out of regions of interest. Oxygen metabolic rate (MRO2) is the amount of oxygen consumed in a given tissue region per unit time per 100 grams (g) of tissue or of the organ of interest. Since in typical physiological conditions, hemoglobin is the dominant carrier of oxygen, the key measure of blood oxygenation is oxygen saturation of hemoglobin (SO2), as follows in Equation (5):
-
MRO2∝(SO2,in−SO2,out)·CHb·Ain·ν in. (5) - Here, Ain is the area of the incoming vessel,
ν in is the mean flow velocity of blood in the incoming vessel, and CHb is the total concentration of hemoglobin. While Ain andν in may be estimated using ultrasound imaging, SO2 and relative CHb may be estimated from multi-wavelength photoacoustic methods. - Exemplary advantages of photoacoustic microscopy over traditional optical and ultrasonic imaging include the detection of endogenous optical absorption contrast at ultrasonic resolution. In photoacoustic microscopy, a pulsed laser beam is focused into the biological tissue to produce emission of ultrasonic waves due to the photoacoustic effect. The short-wavelength pulsed ultrasonic waves are then detected with a focused ultrasonic transducer to form high-resolution tomographic images. Among the existing photoacoustic imaging technologies, the spatial resolutions depend almost solely on the ultrasonic parameters including the center frequency, bandwidth, and numerical aperture (NA). For example, using dark-field confocal PAM, a lateral resolution of approximately 50 μm has been achieved with a center frequency of approximately 50 megahertz (MHz) and an NA of approximately 0.44. This resolution from prior systems is inadequate to resolve smaller structures such as capillaries between approximately 3 μm and approximately 7 μm in diameter with endogenous optical absorption contrast. Aspects of the invention provide improved spatial resolution.
- If such an improvement is achieved by increasing the ultrasonic focusing capability, an approximately 5-μm lateral resolution requires an ultrasonic center frequency greater than 300 MHz. At such a high frequency, unfortunately, the ultrasonic attenuation, which is approximately 400 μm−1 in water and 100 μm−1 in tissue, limits the penetration depth to approximately 100 μm. An alternative is to use fine optical focusing to provide the lateral resolution while ultrasonic temporal detection provides axial resolution. Such an alternative, called OR-PAM, is primarily sensitive to optical absorption contrast, whereas conventional reflection-mode optical confocal microscopy is dominantly sensitive to scattering or fluorescence.
-
FIG. 11 is a schematic of another exemplary embodiment of the OR-PAM imaging system. In this embodiment, the system employs nearly diffraction limited optical focusing with bright field optical illumination to achieve μm-level lateral resolution. A dye laser, such as a CBR-D laser commercially available from Sirah, pumped by a Nd:YLF laser is used as the irradiation source. The laser pulse duration is approximately 5 ns and the pulse repetition rate, controlled by an external trigger, is as high as 2 kHz. The light from the dye laser is attenuated by one thousand times, passed through a spatial filter, such as a 25 μm pinhole, commercially available as P250S from Thorlabs, and then focused by a microscope objective lens, such as a RMS4X lens available from Thorlabs and including a NA of approximately 0.1, a focal length of approximately 45 mm, and a working distance of approximately 22 mm. The distance between the pinhole and the objective lens is approximately 400 mm. The input aperture of the microscope objective is approximately 0.8 times the diameter of the Airy disk of the spatial filter. As a result, the diffraction-limited focus of the objective in water is approximately 3.7 μm in diameter and approximately 200 μm in focal zone. The laser pulse energy after the objective lens measures approximately 100 nJ. An optional beam splitter is located between the pinhole and the objective lens to facilitate focus adjustment and system alignment. Two right-angled prisms, the NT32-545 prism available from Edmund Optics, for example, form a cube with a gap of approximately 0 1 mm between the hypotenuses. The gap is filled with silicone oil. As described above, the silicone oil and the glass have a good optical refractive index match but a large acoustic impedance mismatch. As a result, this silicone oil layer is optically transparent but acoustically reflecting. An ultrasonic transducer, such as a V2012-BC transducer available from Panametrics-NDT, with a center frequency of 75 MHz, a bandwidth of 80%, and an active-element diameter of 6.35 mm, is attached to a cathetus of the bottom prism as shown inFIG. 11 . A plano-concave lens with an approximately 5.2 mm radius of curvature and an approximately 6.35 mm aperture is attached to the bottom of the cube to function as an acoustic lens, which has an NA of approximately 0.46 in water and a focal diameter of approximately 27 μm. Of course, this lens also functions as a negative optical lens, which is compensated for by a correcting positive optical lens placed on top of the cube. - The photoacoustic signal detected by the ultrasonic transducer is amplified by approximately 48 dB using, for example, two ZFL 500LN amplifiers commercially available from Mini-Circuits, then digitized by a 14-bit digital acquisition board using, for example, a CompuScope 12400 from Gage Applied Sciences. A raster scanning is controlled by a separate PC, which triggers both the data-acquisition PC and the pump laser. The trigger signal is synchronized with the clock-out signal from the digital acquisition board.
- An acoustic lens is immersed in water inside a heated container. A window is opened at the bottom of the container and sealed with an ultrasonically and optically transparent 25-μm thick polyethylene membrane. The animal is placed under the water tank with the region of interest (ROI) exposed below the window. Ultrasonic gel, such as Clear Image, available from SonoTech, is applied to the ROI for acoustic coupling. For simplicity, the raster scanning is implemented by translating the water tank and the animal together along the horizontal (x-y) plane. One-dimensional (1D) photoacoustic signal (A-line) at each horizontal location is recorded for 1 μs at a sampling rate of 200 MS/s. A volumetric photoacoustic image is formed by combining the time-resolved photoacoustic signals and may be viewed in direct volumetric rendering, cross-sectional (B-scan) images, or maximum amplitude projection (MAP) images.
- FIGS. 12A-12C are images representing a lateral resolution measurement by the imaging system.
FIG. 12A is a MAP image of an Air Force resolution test target,FIG. 12B is a magnified image of the region within the dashed box ofFIG. 12A , andFIG. 12C is a MAP image of a 6-μm-diameter carbon fiber. The lateral resolution of the OR-PAM system was experimentally measured by imaging an Air Force resolution test target immersed in clear liquid. Images were acquired at the optical wavelength of approximately 590 nm and no signal averaging was performed during data acquisition. InFIGS. 12A and 12B , the highlighted well-resolved bars, shown asgroup 6,element 5, have gaps of approximately 4.9 μm, a spatial frequency of approximately 102 mm−1, and a modulation transfer function value of 0.65. Other pairs of spatial frequency and modulation transfer function values include, for example, a 64 mm−1 spatial frequency with a 0.95 modulation transfer function value, and a 80 mm−1 spatial frequency with a 0.8 modulation transfer function value. Nonlinearly fitting of the modulation transfer function yields a lateral resolution of approximately 5 μm, which is 30% greater than the diffraction limit of 3.7 μm. As an illustration of the lateral resolution, an MAP image of a 6-μm-diameter carbon fiber immersed in water is shown inFIG. 12C . The mean full-width-at-half-maximum (FWHM) value of the imaged fiber is approximately 9.8 μm, which is 3.8 μm wider than the fiber diameter and hence in agreement with the ˜5 μm resolution. The axial resolution was estimated to be approximately 15 μm based on the measured transducer bandwidth, approximately 100 MHz in receiving-only mode, and the speed of sound in tissue, approximately 1.5 mm/μs. In tissue, both the lateral and the axial resolutions deteriorate with imaging depth because of optical scattering and frequency-dependent acoustic attenuation, respectively. -
FIGS. 13A and 13B are images representing a measurement of the imaging depth by the imaging system.FIG. 13A is a MAP image of two horse hairs placed above and below a piece of rat skin acquired with the OR-PAM system.FIG. 13B is a B-scan image at the location marked by the dashed line inFIG. 13A . The imaging depth of this system was measured by imaging two horse hairs with a diameter of approximately 200 μm placed above and below a piece of freshly harvested rat scalp. A photoacoustic image was acquired with 32 times signal averaging at the optical wavelength of 630 nm. Both hairs are clearly visible, where the bottom hair shows a weaker photoacoustic signal because of both optical and acoustic attenuation in the skin. The B-scan image shows that the bottom hair is 700 μm deep in the tissue. Therefore, the maximum imaging depth is at least 700 μm. - The microvessels in the ear of a nude mouse were imaged in vivo by this OR-PAM at the optical wavelength of 570 nm. Nude mouse ears having a thickness of approximately 300 μm have well-developed vasculature and have been widely used to study tumor angiogenesis and other microvascular diseases. During image acquisition, the animal was kept motionless using a breathing anesthesia system and was kept warm using an infrared lamp. Unlike studies published elsewhere, no optical clearing agent was applied to the skin surface. An area of 1 mm2 was scanned with a step size of approximately 1.25 μm. For each pixel, 16 (i.e., 4 by 4) neighboring A-lines were averaged to increase the signal-to-noise ratio (SNR). The scanning time for a complete volumetric dataset was approximately 18 minutes. After data acquisition, the animal recovered naturally without observable laser damage.
-
FIGS. 14A and 14B are photoacoustic images of a microvasculature by the imaging system.FIG. 14C is a photograph of the microvasculature ofFIGS. 14A and 14B , taken from a transmission microscope. More specifically,FIG. 14A is an in vivo photoacoustic image of microvasculature in a nude mouse ear,FIG. 14B is a 3D visualization of the volumetric photoacoustic data with pseudocolor, andFIG. 14C is a photograph taken with trans-illumination optical microscopy. InFIGS. 14A-14C , the area denoted as C is a capillary, the area denoted as CB is a capillary bed, and the area denoted as SG is a sebaceous gland. The photoacoustic image of the microvasculature (FIGS. 14A and 14B ) agrees with the photograph (FIG. 14C ) taken from a transmission microscope with a 4× magnification. However, capillaries are imaged by only the OR-PAM system described above. The mean ratio of the photoacoustic amplitudes between the blood vessels and the background is 20:1, which demonstrates a high endogenous optical-absorption-based imaging contrast. Some vessels, e.g. the vessel labeled with C inFIG. 14A , only occupy a single pixel, which presumably indicates a capillary with a diameter of approximately 5 μm. A volumetric rendering of the photoacoustic data (FIG. 14B ) shows the three-dimensional connectivity of the blood vessels. Parallel arteriole-venule pairs and their branching are clearly observed. The diameter and the morphological pattern of the vessel within the dashed-box in bothFIGS. 14A and 14B suggest that these microvessels belong to a capillary bed. Therefore, OR-PAM, as described above, is able to image capillaries in vivo with endogenous optical absorption contrast due to hemoglobin. In addition, sebaceous glands may also be imaged at the same time. -
FIGS. 15A and 15B are MAP images acquired before and after a high-intensity laser treatment.FIG. 15A is an in vivo photoacoustic image of laser-induced vessel destruction in a Swiss Webster mouse ear before a laser treatment.FIG. 15B is an in vivo photoacoustic image after the laser treatment. InFIGS. 15A and 15B , the area denoted as T is the laser treated area, the area denoted as W is widened blood vessels, and the area denoted as H is a possible hemorrhage. To further demonstrate the potential of OR-PAM, the high-intensity laser destruction of microvessels in the ear of a Swiss Webster mouse were imaged. This type of destruction is clinically used to remove port wine stains in humans.FIGS. 15A and 15B show the MAP images acquired before and after the high-intensity laser treatment. After the healthy vasculature was imaged by the OR-PAM system (shown inFIG. 15A ), the center region measuring approximately 0.25×0.25 mm2 was treated by high-intensity laser pulses having a peak optical fluence of approximately 10 J/cm2 scanned with the step size of approximately 1.25 μm. For the high-intensity illumination, the attenuator and the pin hole were removed from the light path. A second image (shown inFIG. 15B ) was acquired 15 minutes after the laser treatment. Disruption of the vessels within the treated region was clearly observed in the dashed box. Further, the destruction of the blood vessels dilated several neighboring vessels and produced possibly hemorrhage. -
FIG. 16A is an in vivo photoacoustic image of a capillary bed in a mouse ear, captured using the OR-PAM imaging system with a focusing depth of approximately 50 μm.FIG. 16B is an in vivo photoacoustic image of multiple levels of blood vessel bifurcations in a mouse ear, captured using the OR-PAM imaging systems with a focusing depths of approximately 150 μm. - The embodiments described herein use (1) optical focusing to achieve high lateral resolution, (2) time-resolved detection of laser-induced pressure waves to obtain high axial resolution, and/or (3) confocal arrangement between the optical excitation and ultrasonic receiving foci to achieve high sensitivity. In alternative embodiments, the focused ultrasonic receiving may be replaced with optical sensing of the photothermal effect directly inside the object. Three-dimensional images of the distribution of optical contrast within a sampling volume are acquired.
- In an existing system, an intensity-modulated continuous-wave beam of radiation is combined with the detection of the magnitude of the photoacoustic signal. In the embodiments described herein, short pulsed excitation is combined with time-resolved detection of the photoacoustic signal, which has the advantage of time-of-flight based axial resolution. Therefore, the presently described embodiments provide, for example, (a) enhanced axial resolution, (b) 3D imaging of optical contrast from a 2D raster scan, and (c) minimal image artifacts due to the interference of photoacoustic waves from various targets within the light illumination volume, in contrast to the existing system.
- Another existing system uses focused light to produce thermal expansion and uses optical detection, based on the thermal lens effect, or an ultrasonic detector to monitor the resulting pressure/density transients. Such a system lacks axial resolution. In addition, the lateral resolution of such a system is determined by the detector rather then the excitation optics. Utilization of the thermal lens effect in such a system requires transmission illumination in an optically clear medium, which limits the applications of the technology. Moreover, in using an unfocused ultrasonic transducer and an unfocused ultrasonic detector, the excitation beam has a large separation, which affects the detection sensitivity. The frequency mismatch between the central frequency of the photoacoustic waves (>100 MHz) and the central frequency of the ultrasonic transducer (<10 MHz) also limits the SNR of such a system.
- Another existing system uses laser excitation in a coaxial arrangement with a focused ultrasonic detection. However, the laser beam used in such a system is not focused. In fact, the laser beam is divergent because the positive acoustic lens functions as a negative optical lens. The negative optical lens actually broadens the optical beam. More importantly, such a system neither achieves nor claims optically defined lateral resolution, which is a key feature in the presently described embodiments.
- The ability to image microstructures such as the micro-vascular network in the skin or brain cortex and monitor physiological functions of tissue is invaluable. One of the promising technologies for accomplishing this objective is photoacoustic microscopy. Current high-resolution optical imaging techniques, such as optical coherence tomography, can image up to approximately one transport mean free path of between 1 to 2 mm into biological tissues. However, such techniques are sensitive to the backscattering that is related to tissue morphology, and are insensitive to the optical absorption that is related to important biochemical information. Other known techniques such as confocal microscopy and multi-photon microscopy have even more restrictive penetration depth limitation and often involve the introduction of exogenous dyes, which with a few notable exceptions have relatively high toxicity. Acoustic microscopic imaging and spectroscopy systems are sensitive to acoustic impedance variations, which have little functional information about biological tissue and have low contrast in soft tissue. Other imaging techniques such as diffuse optical tomography or thermal wave microscopy have low depth to resolution ratio. Photoacoustic imaging as in embodiments of the invention provides high optical-absorption contrast while maintaining high penetration depth and high ultrasonic resolution. Moreover, because photoacoustic wave magnitude is, within certain bounds, linearly proportional to the optical contrast, optical spectral measurement can be performed to gain functional, i.e., physiological, information such as the local blood oxygenation level. However, increasing the resolution power beyond several tens of micrometers meets serious challenges. At ultrasonic frequencies required to achieve such resolution, which is above approximately 100 MHz, ultrasonic absorption in tissue gradually becomes proportional to the square of the ultrasonic frequency. Consequently, a resolution of several micrometers will have penetration depth of a few tens of micrometers that is much less than the penetration depth of other optical imaging techniques such as confocal microscopy. Embodiments of the present invention overcome the resolution limitation by using optical focusing to achieve high lateral resolution and ultrasonic detection to achieve axial resolution.
- Although imaging of photothermal treatment of microvessels itself is biomedically significant, the capability of OR-PAM to image physiological and pathological changes in capillaries has broader applications. Other possible applications include imaging of vasodilation and vasoconstriction in stroke models, tumor angiogenesis, and tumor extravasations. Mouse ears were chosen as the initial organ to test OR-PAM because transmission optical microscopy could be used to validate the photoacoustic images. Since OR-PAM operates in reflection mode, it may be applied to many other anatomical sites.
- Several alternative embodiments are possible. First, photoacoustic images may be acquired by scanning the optical-acoustic dual foci instead of the sample and the transducer container. Second, it is possible to scan only the optical focus within the acoustic focusing area to reduce the image acquisition time significantly. Third, by varying the excitation optical wavelength, physiological parameters such as hemoglobin oxygen saturation and blood volume may be quantified for in vivo functional imaging using endogenous contrast. Similarly, targeted exogenous contrast agents such as indocyanine green (ICG) and nanoparticles may be quantified for in vivo molecular imaging. Fourth, the acoustic coupling cube may be made to transmit photoacoustic waves ten times more efficiently without transformation from p-waves into sv-waves so that the SNR may be improved. Acoustic antireflection coating on the lens should further increase the SNR by approximately 10 dB.
- When the optical focus is 100 μm below the tissue surface, the surface optical fluence is close to the ANSI safety limit of 20 mJ/cm2 in the visible spectral region. Although the ANSI standards regulate only the surface fluence, the spatial peak optical fluence is calculated at the focus in water, which is approximately 500 mJ/cm2. This focal fluence is still less than the experimentally observed damage threshold in live tissue. After the aforementioned improvements are implemented, the optical fluence may be reduced without affecting the SNR.
- It will be understood that particular embodiments described herein are shown by way of illustration and not as limitations of the invention. The principal features in embodiments of this invention may be employed in various embodiments without departing from the scope of the invention. Those skilled in the art will recognize, or be able to ascertain using no more than routine experimentation, numerous equivalents to the procedures described herein. Such equivalents are considered to be within the scope of this invention and are covered by the claims.
- All of the compositions and/or methods disclosed and claimed herein may be made and executed without undue experimentation in light of the present disclosure. While embodiments of this invention have been described in terms of preferred embodiments, it will be apparent to those of skill in the art that variations may be applied to the compositions and/or methods and in the steps or in the sequence of steps of the method described herein without departing from the concept, spirit, and scope of the invention. All such similar substitutes and modifications apparent to those skilled in the art are deemed to be within the spirit, scope and concept of the invention as defined by the appended claims.
- It will be understood by those of skill in the art that information and signals may be represented using any of a variety of different technologies and techniques (e.g., data, instructions, commands, information, signals, bits, symbols, and chips may be represented by voltages, currents, electromagnetic waves, magnetic fields or particles, optical fields or particles, or any combination thereof). Likewise, the various illustrative logical blocks, modules, circuits, and algorithm steps described herein may be implemented as electronic hardware, computer software, or combinations of both, depending on the application and functionality. Moreover, the various logical blocks, modules, and circuits described herein may be implemented or performed with a general purpose processor (e.g., microprocessor, conventional processor, controller, microcontroller, state machine, and/or combination of computing devices), a digital signal processor (“DSP”), an application specific integrated circuit (“ASIC”), a field programmable gate array (“FPGA”), or other programmable logic device, discrete gate or transistor logic, discrete hardware components, or any combination thereof designed to perform the functions described herein. Similarly, steps of a method or process described herein may be embodied directly in hardware, in a software module executed by a processor, or in a combination of the two. A software module may reside in RAM memory, flash memory, ROM memory, EPROM memory, EEPROM memory, registers, hard disk, a removable disk, a CD-ROM, or any other form of storage medium known in the art. Although embodiments of the present invention have been described in detail, it will be understood by those skilled in the art that various modifications may be made therein without departing from the spirit and scope of the invention as set forth in the appended claims.
- This written description uses examples to disclose the invention, including the best mode, and also to enable any person skilled in the art to practice the invention, including making and using any devices or systems and performing any incorporated methods. The patentable scope of the invention is defined by the claims, and may include other examples that occur to those skilled in the art. Such other examples are intended to be within the scope of the claims if they have structural elements that do not differ from the literal language of the claims, or if they include equivalent structural elements with insubstantial differences from the literal languages of the claims.
Claims (20)
Priority Applications (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US14/950,189 US20160081558A1 (en) | 2007-10-25 | 2015-11-24 | Method of photoacoustic microscopy with lateral resolution of microvasculature |
US15/148,685 US10433733B2 (en) | 2007-10-25 | 2016-05-06 | Single-cell label-free photoacoustic flowoxigraphy in vivo |
Applications Claiming Priority (5)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US98262407P | 2007-10-25 | 2007-10-25 | |
PCT/US2008/081167 WO2009055705A2 (en) | 2007-10-25 | 2008-10-24 | Confocal photoacoustic microscopy with optical lateral resolution |
US73958910A | 2010-06-28 | 2010-06-28 | |
US13/874,653 US9226666B2 (en) | 2007-10-25 | 2013-05-01 | Confocal photoacoustic microscopy with optical lateral resolution |
US14/950,189 US20160081558A1 (en) | 2007-10-25 | 2015-11-24 | Method of photoacoustic microscopy with lateral resolution of microvasculature |
Related Parent Applications (2)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US13/874,653 Division US9226666B2 (en) | 2007-10-25 | 2013-05-01 | Confocal photoacoustic microscopy with optical lateral resolution |
US14/164,117 Continuation US20140142404A1 (en) | 2007-10-25 | 2014-01-24 | Single-cell label-free photoacoustic flowoxigraphy in vivo |
Related Child Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US15/148,685 Continuation US10433733B2 (en) | 2007-10-25 | 2016-05-06 | Single-cell label-free photoacoustic flowoxigraphy in vivo |
Publications (1)
Publication Number | Publication Date |
---|---|
US20160081558A1 true US20160081558A1 (en) | 2016-03-24 |
Family
ID=40580417
Family Applications (4)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US12/739,589 Active 2029-09-13 US8454512B2 (en) | 2007-10-25 | 2008-10-24 | Confocal photoacoustic microscopy with optical lateral resolution |
US13/874,653 Active US9226666B2 (en) | 2007-10-25 | 2013-05-01 | Confocal photoacoustic microscopy with optical lateral resolution |
US14/950,189 Abandoned US20160081558A1 (en) | 2007-10-25 | 2015-11-24 | Method of photoacoustic microscopy with lateral resolution of microvasculature |
US15/148,685 Active 2028-12-26 US10433733B2 (en) | 2007-10-25 | 2016-05-06 | Single-cell label-free photoacoustic flowoxigraphy in vivo |
Family Applications Before (2)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US12/739,589 Active 2029-09-13 US8454512B2 (en) | 2007-10-25 | 2008-10-24 | Confocal photoacoustic microscopy with optical lateral resolution |
US13/874,653 Active US9226666B2 (en) | 2007-10-25 | 2013-05-01 | Confocal photoacoustic microscopy with optical lateral resolution |
Family Applications After (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US15/148,685 Active 2028-12-26 US10433733B2 (en) | 2007-10-25 | 2016-05-06 | Single-cell label-free photoacoustic flowoxigraphy in vivo |
Country Status (5)
Country | Link |
---|---|
US (4) | US8454512B2 (en) |
EP (2) | EP2203733B1 (en) |
JP (2) | JP5643101B2 (en) |
CN (1) | CN101918811B (en) |
WO (1) | WO2009055705A2 (en) |
Cited By (12)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
ITUA20163677A1 (en) * | 2016-05-23 | 2017-11-23 | Scuola Superiore Di Studi Univ E Di Perfezionamento Santanna | ULTRASONIC STIMULATION SYSTEM OF A VITRO SAMPLE |
US10209226B2 (en) | 2014-02-26 | 2019-02-19 | Olympus Corporation | Photoacoustic microscope apparatus |
WO2020205809A1 (en) * | 2019-03-29 | 2020-10-08 | The Research Foundation For The State University Of New York | Photoacoustic breast imaging system and method |
US11020006B2 (en) | 2012-10-18 | 2021-06-01 | California Institute Of Technology | Transcranial photoacoustic/thermoacoustic tomography brain imaging informed by adjunct image data |
US11029287B2 (en) | 2011-02-11 | 2021-06-08 | California Institute Of Technology | Multi-focus optical-resolution photoacoustic microscopy with ultrasonic array detection |
US11137375B2 (en) | 2013-11-19 | 2021-10-05 | California Institute Of Technology | Systems and methods of grueneisen-relaxation photoacoustic microscopy and photoacoustic wavefront shaping |
US11209532B2 (en) | 2017-01-23 | 2021-12-28 | Olympus Corporation | Signal processing device, photoacoustic wave image-acquisition device, and signal processing method |
US11369280B2 (en) | 2019-03-01 | 2022-06-28 | California Institute Of Technology | Velocity-matched ultrasonic tagging in photoacoustic flowgraphy |
US11530979B2 (en) | 2018-08-14 | 2022-12-20 | California Institute Of Technology | Multifocal photoacoustic microscopy through an ergodic relay |
US11592652B2 (en) | 2018-09-04 | 2023-02-28 | California Institute Of Technology | Enhanced-resolution infrared photoacoustic microscopy and spectroscopy |
US11672426B2 (en) | 2017-05-10 | 2023-06-13 | California Institute Of Technology | Snapshot photoacoustic photography using an ergodic relay |
US11730375B2 (en) | 2016-12-14 | 2023-08-22 | Hyundai Motor Company | Photoacoustic, noninvasive, and continuous blood glucose measurement device |
Families Citing this family (186)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
WO2007070080A2 (en) * | 2005-05-04 | 2007-06-21 | Brandt Innovative Technologies, Inc. | Method and apparatus of detecting an object |
US7750536B2 (en) | 2006-03-02 | 2010-07-06 | Visualsonics Inc. | High frequency ultrasonic transducer and matching layer comprising cyanoacrylate |
US20090094287A1 (en) * | 2007-10-03 | 2009-04-09 | Johnson Robin M | Computerized Game and Associated Physical Game Piece for Trading and Tracking via an Online Community |
EP2203733B1 (en) | 2007-10-25 | 2017-05-03 | Washington University in St. Louis | Confocal photoacoustic microscopy with optical lateral resolution |
WO2010048258A1 (en) | 2008-10-23 | 2010-04-29 | Washington University In St. Louis | Reflection-mode photoacoustic tomography using a flexibly-supported cantilever beam |
US20140142404A1 (en) * | 2008-10-23 | 2014-05-22 | The Washington University | Single-cell label-free photoacoustic flowoxigraphy in vivo |
US9351705B2 (en) | 2009-01-09 | 2016-05-31 | Washington University | Miniaturized photoacoustic imaging apparatus including a rotatable reflector |
US8016419B2 (en) * | 2009-03-17 | 2011-09-13 | The Uwm Research Foundation, Inc. | Systems and methods for photoacoustic opthalmoscopy |
WO2011091423A2 (en) * | 2010-01-25 | 2011-07-28 | The Arizona Board Of Regents On Behalf Of The University Of Arizona | Ultrasonic/photoacoustic imaging devices and methods |
CN101782518A (en) * | 2010-02-11 | 2010-07-21 | 华南师范大学 | Cell opto-acoustic microscopic imaging method and device thereof |
CN101782506B (en) * | 2010-03-05 | 2012-05-30 | 华南师范大学 | Confocal-photoacoustic dual-mode microscopic imaging method and device thereof |
US9086365B2 (en) | 2010-04-09 | 2015-07-21 | Lihong Wang | Quantification of optical absorption coefficients using acoustic spectra in photoacoustic tomography |
CN103765289B (en) | 2010-08-27 | 2017-05-17 | 小利兰·斯坦福大学托管委员会 | Microscopy imaging device with advanced imaging properties |
US9289191B2 (en) | 2011-10-12 | 2016-03-22 | Seno Medical Instruments, Inc. | System and method for acquiring optoacoustic data and producing parametric maps thereof |
JP5725781B2 (en) | 2010-09-28 | 2015-05-27 | キヤノン株式会社 | Subject information acquisition device |
US8954130B2 (en) | 2010-12-17 | 2015-02-10 | Canon Kabushiki Kaisha | Apparatus and method for irradiating a medium |
JP6151882B2 (en) * | 2010-12-24 | 2017-06-21 | キヤノン株式会社 | Subject information acquisition apparatus and subject information acquisition method |
CN102175775B (en) * | 2011-01-14 | 2013-05-08 | 河南工业大学 | Food quality testing system and method based on laser ultrasound erosion mechanism |
US9743881B2 (en) * | 2011-03-29 | 2017-08-29 | Koninklijke Philips N.V. | Photoacoustic catheter for functional-imaging-based ablation monitoring |
JP5704998B2 (en) * | 2011-04-06 | 2015-04-22 | キヤノン株式会社 | Photoacoustic apparatus and control method thereof |
US20120275262A1 (en) * | 2011-04-29 | 2012-11-01 | Washington University | Section-illumination photoacoustic microscopy with ultrasonic array detection |
WO2012174413A1 (en) * | 2011-06-15 | 2012-12-20 | University Of Southern California | Optical coherence photoacoustic microscopy |
US8843190B2 (en) * | 2011-07-21 | 2014-09-23 | The Board Of Trustees Of The Leland Stanford Junior University | Medical screening and diagnostics based on air-coupled photoacoustics |
JP5626903B2 (en) * | 2011-07-27 | 2014-11-19 | 富士フイルム株式会社 | Catheter-type photoacoustic probe and photoacoustic imaging apparatus provided with the same |
WO2013023210A1 (en) * | 2011-08-11 | 2013-02-14 | University Of Washington Through Its Center For Commercialization | Methods and systems for integrated imaging using optical coherence tomography and photoacoustic imaging |
US9400376B2 (en) * | 2011-08-23 | 2016-07-26 | William L. Vogt | Z-axis optical focusing mechanism |
CN103076286B (en) * | 2011-10-26 | 2015-06-24 | 联发科技股份有限公司 | Photoacoustic microscopy (pam) systems and related methods for observing objects |
US20130107662A1 (en) * | 2011-10-26 | 2013-05-02 | Meng-Lin Li | Photoacoustic microscopy (pam) systems and related methods for observing objects |
US9055869B2 (en) * | 2011-10-28 | 2015-06-16 | Covidien Lp | Methods and systems for photoacoustic signal processing |
US11191435B2 (en) | 2013-01-22 | 2021-12-07 | Seno Medical Instruments, Inc. | Probe with optoacoustic isolator |
US9733119B2 (en) | 2011-11-02 | 2017-08-15 | Seno Medical Instruments, Inc. | Optoacoustic component utilization tracking |
US9730587B2 (en) | 2011-11-02 | 2017-08-15 | Seno Medical Instruments, Inc. | Diagnostic simulator |
US20140005544A1 (en) | 2011-11-02 | 2014-01-02 | Seno Medical Instruments, Inc. | System and method for providing selective channel sensitivity in an optoacoustic imaging system |
US9814394B2 (en) | 2011-11-02 | 2017-11-14 | Seno Medical Instruments, Inc. | Noise suppression in an optoacoustic system |
WO2013067419A1 (en) * | 2011-11-02 | 2013-05-10 | Seno Medical Instruments, Inc. | Dual modality imaging system for coregistered functional and anatomical mapping |
US9445786B2 (en) | 2011-11-02 | 2016-09-20 | Seno Medical Instruments, Inc. | Interframe energy normalization in an optoacoustic imaging system |
US20130338475A1 (en) | 2012-06-13 | 2013-12-19 | Seno Medical Instruments, Inc. | Optoacoustic imaging system with fiber optic cable |
US10433732B2 (en) | 2011-11-02 | 2019-10-08 | Seno Medical Instruments, Inc. | Optoacoustic imaging system having handheld probe utilizing optically reflective material |
US9743839B2 (en) | 2011-11-02 | 2017-08-29 | Seno Medical Instruments, Inc. | Playback mode in an optoacoustic imaging system |
US11287309B2 (en) | 2011-11-02 | 2022-03-29 | Seno Medical Instruments, Inc. | Optoacoustic component utilization tracking |
US9757092B2 (en) | 2011-11-02 | 2017-09-12 | Seno Medical Instruments, Inc. | Method for dual modality optoacoustic imaging |
US20130289381A1 (en) | 2011-11-02 | 2013-10-31 | Seno Medical Instruments, Inc. | Dual modality imaging system for coregistered functional and anatomical mapping |
CN102488494B (en) * | 2011-11-16 | 2013-09-25 | 华中科技大学 | Totally internal reflection type photo-acoustic microscopic imaging system and method |
CN102579073B (en) * | 2011-12-01 | 2013-09-11 | 华中科技大学 | Self-adaptive image reconstruction method for photo-acoustic microscopic imaging |
WO2013086293A1 (en) * | 2011-12-08 | 2013-06-13 | Washington University | In vivo label-free histology by photoacoustic microscopy of cell nuclei |
CA2866840C (en) | 2012-03-09 | 2022-03-29 | Seno Medical Instruments, Inc. | Statistical mapping in an optoacoustic imaging system |
WO2013185784A1 (en) * | 2012-06-11 | 2013-12-19 | Helmholtz Zentrum München Deutsches Forschungszentrum Für Gesundheit Und Umwelt (Gmbh) | Imaging system and method for imaging an object |
US9610043B2 (en) | 2012-06-13 | 2017-04-04 | Seno Medical Instruments, Inc. | System and method for producing parametric maps of optoacoustic data |
IN2014KN02685A (en) * | 2012-06-13 | 2015-05-08 | Seno Medical Instr Inc | |
JP5885600B2 (en) * | 2012-06-20 | 2016-03-15 | オリンパス株式会社 | Photoacoustic microscope |
US20130345541A1 (en) * | 2012-06-26 | 2013-12-26 | Covidien Lp | Electrosurgical device incorporating a photo-acoustic system for interrogating/imaging tissue |
US9636083B2 (en) * | 2012-07-17 | 2017-05-02 | The Johns Hopkins University | High quality closed-loop ultrasound imaging system |
CN102854142A (en) * | 2012-08-28 | 2013-01-02 | 曾吕明 | Optical resolution type photoacoustic microscope based on optical beam scanning |
US9891422B2 (en) * | 2012-09-12 | 2018-02-13 | Washington State University | Digital confocal optical profile microscopy |
CN102879335B (en) * | 2012-09-26 | 2015-07-08 | 华南师范大学 | Portable noninvasive real-time photoacoustic viscoelastic detector |
US9625423B2 (en) * | 2012-10-30 | 2017-04-18 | The Boeing Company | System and method for testing a composite structure using a laser ultrasound testing system |
CN103018171B (en) * | 2012-11-29 | 2014-12-31 | 华南师范大学 | Wide-frequency-band optical-acoustic and fluorescent double-imaging device without energy converter and detection method thereof |
JP6086719B2 (en) * | 2012-12-25 | 2017-03-01 | オリンパス株式会社 | Photoacoustic microscope |
JP6086718B2 (en) * | 2012-12-25 | 2017-03-01 | オリンパス株式会社 | Photoacoustic microscope |
WO2014103106A1 (en) * | 2012-12-25 | 2014-07-03 | オリンパス株式会社 | Photoacoustic microscope |
CN205067323U (en) | 2013-01-22 | 2016-03-02 | 贝克顿·迪金森公司 | Optical system , optical coupler and optical sensor |
DE102013203452B4 (en) * | 2013-02-28 | 2016-11-03 | Carl Zeiss Ag | Photoacoustic microscope |
DE102013203450B4 (en) * | 2013-02-28 | 2017-02-09 | Carl Zeiss Ag | microscope |
DE102013203454A1 (en) * | 2013-02-28 | 2014-09-11 | Carl Zeiss Ag | Recording device and recording method |
US9398893B2 (en) | 2013-03-15 | 2016-07-26 | Seno Medical Instruments, Inc. | System and method for diagnostic vector classification support |
US9380981B2 (en) * | 2013-03-15 | 2016-07-05 | Covidien Lp | Photoacoustic monitoring technique with noise reduction |
JP6238539B2 (en) * | 2013-03-21 | 2017-11-29 | キヤノン株式会社 | Processing apparatus, subject information acquisition apparatus, and processing method |
WO2014197899A2 (en) * | 2013-06-07 | 2014-12-11 | Northwestern University | Methods, systems and apparatus of an all-optics ultrasound sensor |
CN103393406B (en) * | 2013-07-29 | 2015-10-28 | 深圳先进技术研究院 | Simple and easy hand-held photoacoustic imaging probe |
CN103385697A (en) * | 2013-07-29 | 2013-11-13 | 深圳先进技术研究院 | High-performance handheld photoacoustic imaging probe |
WO2015016403A1 (en) * | 2013-08-01 | 2015-02-05 | 서강대학교 산학협력단 | Device and method for acquiring fusion image |
JP6200246B2 (en) * | 2013-09-08 | 2017-09-20 | キヤノン株式会社 | Probe |
EP3054853A4 (en) | 2013-10-11 | 2017-05-17 | Seno Medical Instruments, Inc. | Systems and methods for component separation in medical imaging |
JP2015112326A (en) * | 2013-12-12 | 2015-06-22 | キヤノン株式会社 | Probe and subject information acquisition device |
JP6210873B2 (en) * | 2013-12-25 | 2017-10-11 | オリンパス株式会社 | Photoacoustic microscope |
JP6388360B2 (en) * | 2013-12-27 | 2018-09-12 | キヤノン株式会社 | SUBJECT INFORMATION ACQUISITION DEVICE AND METHOD FOR CONTROLLING SUBJECT INFORMATION ACQUISITION DEVICE |
JP6249783B2 (en) * | 2014-01-14 | 2017-12-20 | オリンパス株式会社 | microscope |
US10165955B2 (en) * | 2014-02-06 | 2019-01-01 | Reuven Gladshtein | Obtaining cardiovascular parameters using arterioles related transient time |
EP2913683A1 (en) * | 2014-02-26 | 2015-09-02 | Nuomedis AG | Method and apparatus for automated scanning probe microscopy |
WO2015131098A1 (en) | 2014-02-27 | 2015-09-03 | Seno Medical Instruments, Inc. | Probe adapted to control blood flow through vessels during imaging and method of use of same |
CN106456111B (en) | 2014-03-12 | 2020-02-11 | 富士胶片索诺声公司 | High frequency ultrasound transducer with ultrasound lens with integrated central matching layer |
JP6335612B2 (en) * | 2014-04-23 | 2018-05-30 | キヤノン株式会社 | Photoacoustic apparatus, processing apparatus, processing method, and program |
WO2016061679A1 (en) * | 2014-10-22 | 2016-04-28 | Parsin Haji Reza | Photoacoustic remote sensing (pars) |
JP6621819B2 (en) | 2014-10-30 | 2019-12-18 | セノ メディカル インストルメンツ,インク. | Photoacoustic imaging system with detection of relative orientation of light source and acoustic receiver using acoustic waves |
CN107106005B (en) * | 2014-11-07 | 2019-02-22 | 拜尔普泰戈恩公司 | Configurable light beam scan drive system |
JP6587385B2 (en) * | 2014-11-27 | 2019-10-09 | キヤノン株式会社 | Subject information acquisition apparatus and subject information acquisition method |
JP2016101393A (en) | 2014-11-28 | 2016-06-02 | キヤノン株式会社 | Subject information acquisition apparatus and control method therefor |
JP2016101369A (en) | 2014-11-28 | 2016-06-02 | キヤノン株式会社 | Photoacoustic device and control method of photoacoustic device |
JP6512801B2 (en) * | 2014-11-28 | 2019-05-15 | キヤノン株式会社 | Object information acquisition device |
WO2016094434A1 (en) * | 2014-12-08 | 2016-06-16 | University Of Virginia Patent Foundation | Systems and methods for multispectral photoacoustic microscopy |
CN104406944B (en) * | 2014-12-18 | 2017-09-29 | 重庆大学 | The method that optical microphotograph imaging resolution is improved using silicon nano |
CN104545814B (en) * | 2014-12-31 | 2017-07-14 | 中国科学院深圳先进技术研究院 | Animal wear-type opto-acoustic imaging devices |
WO2016110971A1 (en) * | 2015-01-07 | 2016-07-14 | オリンパス株式会社 | Objective lens unit for photoacoustic microscope and photoacoustic microscope having same |
CN104614846B (en) * | 2015-03-03 | 2017-01-11 | 北京理工大学 | Reflection type spectral pupil differential confocal-photoacoustic microimaging device and method |
CN104614349B (en) * | 2015-03-03 | 2017-05-31 | 北京理工大学 | Reflective light splitting pupil confocal photoacoustic microscopic imaging device and method |
CN104759753B (en) * | 2015-03-30 | 2016-08-31 | 江苏大学 | The co-ordination of multisystem automatization improves the method for induced with laser cavitation reinforcement |
US20180110417A1 (en) * | 2015-06-04 | 2018-04-26 | The University Of Massachusetts | Fiber optic temperature measurement system |
US11460711B2 (en) | 2015-06-09 | 2022-10-04 | Tintometer, Gmbh | Backscatter reductant anamorphic beam sampler |
EP3332239B1 (en) * | 2015-06-09 | 2022-10-05 | Tintometer GmbH | Fluidic module for turbidity measuring device |
CN107850580A (en) * | 2015-06-18 | 2018-03-27 | 索克普拉科学与工程公司 | Method and system for acoustically scanned samples |
JP6603403B2 (en) | 2015-08-31 | 2019-11-06 | ヒューレット−パッカード デベロップメント カンパニー エル.ピー. | Spectroscopic microscope and method thereof |
US10184835B2 (en) * | 2015-09-23 | 2019-01-22 | Agilent Technologies, Inc. | High dynamic range infrared imaging spectroscopy |
CN106551690A (en) * | 2015-09-30 | 2017-04-05 | 齐心 | A kind of vital sign measurement device and method |
US10448850B2 (en) | 2015-10-16 | 2019-10-22 | Washington University | Photoacoustic flowmetry systems and methods |
EP3362787A4 (en) * | 2015-10-16 | 2019-05-22 | Dalhousie University | Systems and methods for swept source optical coherence tomographic vibrography |
US20170112383A1 (en) * | 2015-10-23 | 2017-04-27 | Nec Laboratories America, Inc. | Three dimensional vein imaging using photo-acoustic tomography |
JP6045753B1 (en) * | 2015-11-05 | 2016-12-14 | オリンパス株式会社 | Photoacoustic wave detection device and endoscope system having the same |
WO2017096406A1 (en) | 2015-12-04 | 2017-06-08 | The Research Foundation For The State University Of New York | Devices and methods for photoacoustic tomography |
US9976989B2 (en) * | 2015-12-15 | 2018-05-22 | General Electric Company | Monitoring systems and methods for electrical machines |
KR101949404B1 (en) * | 2016-01-18 | 2019-02-19 | 포항공과대학교 산학협력단 | Photoacoustic/ultrasound handheld pen-type probe using mems scanner, and photoacoustic image acquisition system and method using the same |
CN105719325A (en) * | 2016-01-19 | 2016-06-29 | 哈尔滨工业大学(威海) | Optoacoustic microscopic imaging method and device based on low-rank matrix approximation |
CN105699295B (en) * | 2016-01-26 | 2018-08-24 | 华南师范大学 | Utilize the quantitative detecting method and device of optoacoustic fluorescence signal ratio measurement pH value |
US10327646B2 (en) | 2016-02-02 | 2019-06-25 | Illumisonics Inc. | Non-interferometric photoacoustic remote sensing (NI-PARS) |
WO2017138459A1 (en) * | 2016-02-08 | 2017-08-17 | 富士フイルム株式会社 | Acoustic wave image generation device and acoustic wave image generation method |
JP6750000B2 (en) * | 2016-03-25 | 2020-09-02 | テルモ株式会社 | Image diagnostic apparatus, control method of image diagnostic apparatus, computer program, computer-readable storage medium |
CN106618589B (en) * | 2016-11-16 | 2019-12-31 | 南昌洋深电子科技有限公司 | Photoacoustic imaging identity recognition method based on blood vessel network |
WO2018122266A1 (en) * | 2016-12-28 | 2018-07-05 | Koninklijke Philips N.V. | Light based skin treatment device |
KR101994937B1 (en) * | 2017-02-15 | 2019-07-01 | 울산과학기술원 | Array transducer-based side-scanning photoacoustic and ultrasonic endoscopy system |
US10856843B2 (en) | 2017-03-23 | 2020-12-08 | Vave Health, Inc. | Flag table based beamforming in a handheld ultrasound device |
US11446003B2 (en) * | 2017-03-27 | 2022-09-20 | Vave Health, Inc. | High performance handheld ultrasound |
US11531096B2 (en) | 2017-03-23 | 2022-12-20 | Vave Health, Inc. | High performance handheld ultrasound |
US10627338B2 (en) | 2017-03-23 | 2020-04-21 | Illumisonics Inc. | Camera-based photoacoustic remote sensing (C-PARS) |
CN106943120A (en) * | 2017-04-21 | 2017-07-14 | 厦门大学 | A kind of photoacoustic microscope and its method for monitoring microvesicle explosion in biological tissues |
CN106994006A (en) * | 2017-05-19 | 2017-08-01 | 厦门大学 | Bimodal imaging system |
JP6971646B2 (en) * | 2017-06-13 | 2021-11-24 | 株式会社キーエンス | Confocal displacement meter |
JP7408265B2 (en) * | 2017-06-13 | 2024-01-05 | 株式会社キーエンス | confocal displacement meter |
JP6971645B2 (en) * | 2017-06-13 | 2021-11-24 | 株式会社キーエンス | Confocal displacement meter |
WO2018235377A1 (en) | 2017-06-19 | 2018-12-27 | 横河電機株式会社 | Objective optical system and photoacoustic imaging device |
JP6780665B2 (en) | 2017-06-19 | 2020-11-04 | 横河電機株式会社 | Objective optical system and photoacoustic imaging equipment |
CN107228904B (en) * | 2017-07-21 | 2023-04-18 | 江西科技师范大学 | Photoinduced ultrasonic blood glucose noninvasive detection device and method |
CN107157491B (en) * | 2017-07-21 | 2023-04-14 | 江西科技师范大学 | Photoacoustic blood glucose detection device and method for automatically positioning blood vessel |
CN107677621A (en) * | 2017-10-11 | 2018-02-09 | 厦门大学 | The temperature measuring equipment of multispectral optical technology fusion |
US11596313B2 (en) * | 2017-10-13 | 2023-03-07 | Arizona Board Of Regents On Behalf Of Arizona State University | Photoacoustic targeting with micropipette electrodes |
US10585028B2 (en) | 2017-10-20 | 2020-03-10 | Charted Scientific, Inc. | Method and apparatus for optical analysis |
US11041756B2 (en) | 2017-10-20 | 2021-06-22 | Charted Scientific Inc. | Method and apparatus of filtering light using a spectrometer enhanced with additional spectral filters with optical analysis of fluorescence and scattered light from particles suspended in a liquid medium using confocal and non confocal illumination and imaging |
US10299682B1 (en) | 2017-11-22 | 2019-05-28 | Hi Llc | Pulsed ultrasound modulated optical tomography with increased optical/ultrasound pulse ratio |
US10016137B1 (en) | 2017-11-22 | 2018-07-10 | Hi Llc | System and method for simultaneously detecting phase modulated optical signals |
US20200359903A1 (en) * | 2018-01-26 | 2020-11-19 | Illumisonics Inc. | Coherence gated photoacoustic remote sensing (cg-pars) |
US10368752B1 (en) | 2018-03-08 | 2019-08-06 | Hi Llc | Devices and methods to convert conventional imagers into lock-in cameras |
US20190282069A1 (en) * | 2018-03-16 | 2019-09-19 | Barbara Smith | Deep brain stimulation electrode with photoacoustic and ultrasound imaging capabilities |
US10955335B2 (en) | 2018-03-28 | 2021-03-23 | University Of Washington | Non-contact photoacoustic spectrophotometry insensitive to light scattering |
US11206985B2 (en) | 2018-04-13 | 2021-12-28 | Hi Llc | Non-invasive optical detection systems and methods in highly scattering medium |
US11857316B2 (en) | 2018-05-07 | 2024-01-02 | Hi Llc | Non-invasive optical detection system and method |
CN108888238A (en) * | 2018-05-11 | 2018-11-27 | 南京大学深圳研究院 | A kind of photoacoustic microscope and imaging method based on ultrasonic reflection plate with holes |
CN108937853B (en) * | 2018-05-29 | 2022-06-24 | 华南师范大学 | Three-dimensional photoacoustic microscopic imaging method and imaging system with multi-port parallel processing |
US10966612B2 (en) * | 2018-06-14 | 2021-04-06 | Open Water Internet Inc. | Expanding beam optical element |
EP3627205A1 (en) * | 2018-09-20 | 2020-03-25 | Koninklijke Philips N.V. | Confocal laser scanning microscope configured for generating line foci |
WO2020065726A1 (en) * | 2018-09-25 | 2020-04-02 | オリンパス株式会社 | Photoacoustic imaging device |
CN109567758B (en) * | 2018-12-29 | 2021-09-28 | 中国科学院深圳先进技术研究院 | Cross-scale photoacoustic imaging system |
CN109620159B (en) * | 2018-12-29 | 2024-04-02 | 深圳先进技术研究院 | Photoacoustic microscopic imaging device |
CN109864707B (en) * | 2019-01-17 | 2021-09-07 | 南京科技职业学院 | Method for improving photoacoustic tomography resolution ratio under limited viewing angle condition |
US10724956B1 (en) * | 2019-02-01 | 2020-07-28 | Essen Instruments, Inc. | Spectral unmixing |
CA3132432A1 (en) | 2019-03-15 | 2020-09-24 | Parsin Haji Reza | Single source photoacoustic remote sensing (ss-pars) |
CN110037655B (en) * | 2019-04-12 | 2020-07-28 | 北京大学 | Photoacoustic mammary gland imaging device and imaging method thereof |
US11768182B2 (en) * | 2019-04-26 | 2023-09-26 | Arizona Board Of Regents On Behalf Of Arizona State University | Photoacoustic and optical microscopy combiner and method of generating a photoacoustic image of a sample |
TWI808435B (en) * | 2019-06-17 | 2023-07-11 | 邦睿生技股份有限公司 | Multi-view analysis in automated testing apparatus |
US11320370B2 (en) * | 2019-06-26 | 2022-05-03 | Open Water Internet Inc. | Apparatus for directing optical and acoustic signals |
CN110412123A (en) * | 2019-07-23 | 2019-11-05 | 南方科技大学 | A kind of micro-fluidic imaging system of optoacoustic and method |
RU2714515C1 (en) * | 2019-08-21 | 2020-02-18 | федеральное государственное бюджетное образовательное учреждение высшего образования "Донской государственный технический университет" (ДГТУ) | Device 3d visualization of deformation state of material surface in area of elastic deformations |
JP7293072B2 (en) * | 2019-09-27 | 2023-06-19 | 株式会社タムロン | Photoacoustic device, photoacoustic imaging device, and method for manufacturing photoacoustic device |
CN110824002B (en) * | 2019-10-11 | 2021-03-23 | 西安交通大学 | Coupling synchronous measurement system and method based on photoacoustic effect |
EP3822687A1 (en) * | 2019-11-15 | 2021-05-19 | Leica Microsystems CMS GmbH | Optical imaging device for a microscope |
WO2021123893A1 (en) | 2019-12-19 | 2021-06-24 | Illumisonics Inc. | Photoacoustic remote sensing (pars), and related methods of use |
US11925472B2 (en) * | 2019-12-23 | 2024-03-12 | Washington University | Transvaginal fast-scanning optical-resolution photoacoustic endoscopy |
US11122978B1 (en) | 2020-06-18 | 2021-09-21 | Illumisonics Inc. | PARS imaging methods |
US11786128B2 (en) | 2020-06-18 | 2023-10-17 | Illumisonics Inc. | PARS imaging methods |
CN111610148A (en) * | 2020-06-02 | 2020-09-01 | 天津大学 | Infrared multi-mode microscopic device based on liquid acousto-optic lens and microscopic method thereof |
CN111624257A (en) * | 2020-06-08 | 2020-09-04 | 上海工程技术大学 | Metal surface crack detection system based on SLS |
CA3177342A1 (en) * | 2020-06-18 | 2021-12-23 | Parsin Haji Reza | Pars imaging methods |
CN111693465B (en) * | 2020-07-15 | 2021-06-22 | 南京大学 | Microscopic imaging method for simultaneously obtaining light absorption and light scattering double contrasts |
CN112057046A (en) * | 2020-09-10 | 2020-12-11 | 南京诺源医疗器械有限公司 | Tumor fluorescence imaging spectrum diagnostic apparatus |
CN111948147B (en) * | 2020-09-25 | 2023-07-25 | 广东工业大学 | Non-blind area full-field ultrasonic microscope imaging system and method thereof |
CN112137589B (en) * | 2020-09-29 | 2021-11-05 | 北京理工大学 | Micro photoacoustic imaging probe and preparation method thereof |
KR20220069176A (en) | 2020-11-19 | 2022-05-27 | 삼성전자주식회사 | Photoacoustic apparatus, apparatus and method for obtaining photoacoustic image |
WO2022204525A1 (en) * | 2021-03-25 | 2022-09-29 | Trustees Of Boston University | Dark-field mid-infrared photothermal microscopy |
HUP2100200A1 (en) | 2021-05-20 | 2022-11-28 | Dermus Kft | Depth-surface imaging equipment for registrating ultrasound images by surface information |
US20230032932A1 (en) * | 2021-08-02 | 2023-02-02 | Leuko Labs, Inc. | Automated system for acquiring images of one or more capillaries in a capillary bed |
CN114010152B (en) * | 2021-09-16 | 2023-09-01 | 南方科技大学 | Blood brain barrier damage assessment device and method based on dual-wavelength photoacoustic microscopy imaging |
CN114098637B (en) * | 2021-11-10 | 2023-07-04 | 南方科技大学 | Large-view-field photoacoustic microscopic imaging device and method |
KR20230076286A (en) * | 2021-11-24 | 2023-05-31 | 삼성전자주식회사 | Apparatus and method for measuring bio-signal |
ES2916219B2 (en) * | 2022-04-01 | 2024-02-07 | Univ Valencia Politecnica | OPTICAL DEVICE, SYSTEM AND PROCEDURE FOR OBTAINING PHOTOACOUSTIC IMAGES THROUGH THE USE OF HOMOGENIZED BEAMS FROM PULSED LIGHT SOURCES |
US11497436B1 (en) * | 2022-05-17 | 2022-11-15 | Ix Innovation Llc | Systems, methods, and bone mapper devices for real-time mapping and analysis of bone tissue |
CN114984470B (en) * | 2022-08-04 | 2022-11-18 | 之江实验室 | Ultrasonic treatment system based on photoacoustic guidance |
WO2024050385A1 (en) * | 2022-09-01 | 2024-03-07 | The Regents Of The University Of California | Method and apparatus for photo acoustic-guided ultrasound treatment for port wine stains |
CN116223450B (en) * | 2023-03-23 | 2024-03-19 | 中南大学 | Instrument and method for measuring concentration of transparent liquid |
CN116879180B (en) * | 2023-09-08 | 2023-12-01 | 之江实验室 | Photoacoustic microimaging system and method based on radial polarization modulation beam focusing |
Citations (2)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20090054763A1 (en) * | 2006-01-19 | 2009-02-26 | The Regents Of The University Of Michigan | System and method for spectroscopic photoacoustic tomography |
US20090227997A1 (en) * | 2006-01-19 | 2009-09-10 | The Regents Of The University Of Michigan | System and method for photoacoustic imaging and monitoring of laser therapy |
Family Cites Families (161)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
DE2542075A1 (en) | 1975-09-20 | 1977-07-21 | Leitz Ernst Gmbh | LIGHTING DEVICE FOR LIGHT AND DARK FIELD ILLUMINATION |
US4029756A (en) | 1975-11-26 | 1977-06-14 | Research Corporation | Serological procedure for determining presence of neisseria gonorrhoeae antibodies |
US4255971A (en) * | 1978-11-01 | 1981-03-17 | Allan Rosencwaig | Thermoacoustic microscopy |
US4267732A (en) * | 1978-11-29 | 1981-05-19 | Stanford University Board Of Trustees | Acoustic microscope and method |
US4375818A (en) | 1979-03-12 | 1983-03-08 | Olympus Optical Company Ltd. | Ultrasonic diagnosis system assembled into endoscope |
US4489727A (en) | 1981-03-22 | 1984-12-25 | Olympus Optical Co., Ltd. | Device for diagnosing body cavity interior with supersonic waves |
US4385634A (en) | 1981-04-24 | 1983-05-31 | University Of Arizona Foundation | Radiation-induced thermoacoustic imaging |
US4430897A (en) * | 1981-05-14 | 1984-02-14 | The Board Of Trustees Of The Leland Stanford University | Acoustic microscope and method |
US4468136A (en) * | 1982-02-12 | 1984-08-28 | The Johns Hopkins University | Optical beam deflection thermal imaging |
US4546771A (en) | 1982-03-04 | 1985-10-15 | Indianapolis Center For Advanced Research, Inc. (Icfar) | Acoustic microscope |
US4462255A (en) | 1983-02-03 | 1984-07-31 | Technicare Corporation | Piezoelectric scanning systems for ultrasonic transducers |
US4596254A (en) | 1984-12-18 | 1986-06-24 | Tsi Research Associates Limited Partnership | Laser Doppler flow monitor |
DE3510704A1 (en) | 1985-03-23 | 1986-09-25 | Philips Patentverwaltung Gmbh, 2000 Hamburg | OPTICAL MEASURING DEVICE |
US5000185A (en) | 1986-02-28 | 1991-03-19 | Cardiovascular Imaging Systems, Inc. | Method for intravascular two-dimensional ultrasonography and recanalization |
DE3727213A1 (en) | 1986-08-14 | 1988-02-18 | Olympus Optical Co | ULTRASONIC DIAGNOSTIC DEVICE |
JPH07100064B2 (en) | 1986-09-29 | 1995-11-01 | 株式会社日立メデイコ | Ultrasonic Doppler velocity meter |
JPH074373B2 (en) | 1986-10-16 | 1995-01-25 | オリンパス光学工業株式会社 | Ultrasound endoscopy |
US4802487A (en) | 1987-03-26 | 1989-02-07 | Washington Research Foundation | Endoscopically deliverable ultrasound imaging system |
US4869256A (en) | 1987-04-22 | 1989-09-26 | Olympus Optical Co., Ltd. | Endoscope apparatus |
US4802461A (en) | 1987-08-26 | 1989-02-07 | Candela Laser Corporation | Rigid endoscope with flexible tip |
US4995396A (en) | 1988-12-08 | 1991-02-26 | Olympus Optical Co., Ltd. | Radioactive ray detecting endoscope |
US4921333A (en) | 1989-01-11 | 1990-05-01 | The United States Of America As Represented By The Secretary Of The Army | Phase contrast image microscopy using optical phase conjugation in a hybrid analog/digital design |
US5083549A (en) | 1989-02-06 | 1992-01-28 | Candela Laser Corporation | Endoscope with tapered shaft |
US5107844A (en) | 1989-04-06 | 1992-04-28 | Olympus Optical Co., Ltd. | Ultrasonic observing apparatus |
US5016173A (en) | 1989-04-13 | 1991-05-14 | Vanguard Imaging Ltd. | Apparatus and method for monitoring visually accessible surfaces of the body |
DE69027678T2 (en) | 1989-05-03 | 1997-02-20 | Medical Technologies Inc Enter | INSTRUMENT FOR INTRALUMINAL RELIEF OF STENOSES |
US5115814A (en) | 1989-08-18 | 1992-05-26 | Intertherapy, Inc. | Intravascular ultrasonic imaging probe and methods of using same |
US5125410A (en) | 1989-10-13 | 1992-06-30 | Olympus Optical Co., Ltd. | Integrated ultrasonic diagnosis device utilizing intra-blood-vessel probe |
US5070455A (en) | 1989-11-22 | 1991-12-03 | Singer Imaging, Inc. | Imaging system and method using scattered and diffused radiation |
JP2791165B2 (en) | 1990-02-07 | 1998-08-27 | 株式会社東芝 | Intravascular ultrasound probe |
US5140463A (en) | 1990-03-08 | 1992-08-18 | Yoo Kwong M | Method and apparatus for improving the signal to noise ratio of an image formed of an object hidden in or behind a semi-opaque random media |
US5305759A (en) | 1990-09-26 | 1994-04-26 | Olympus Optical Co., Ltd. | Examined body interior information observing apparatus by using photo-pulses controlling gains for depths |
US5445155A (en) | 1991-03-13 | 1995-08-29 | Scimed Life Systems Incorporated | Intravascular imaging apparatus and methods for use and manufacture |
US5331466A (en) | 1991-04-23 | 1994-07-19 | Lions Eye Institute Of Western Australia Inc. | Method and apparatus for homogenizing a collimated light beam |
US6111645A (en) | 1991-04-29 | 2000-08-29 | Massachusetts Institute Of Technology | Grating based phase control optical delay line |
US6564087B1 (en) | 1991-04-29 | 2003-05-13 | Massachusetts Institute Of Technology | Fiber optic needle probes for optical coherence tomography imaging |
US6134003A (en) | 1991-04-29 | 2000-10-17 | Massachusetts Institute Of Technology | Method and apparatus for performing optical measurements using a fiber optic imaging guidewire, catheter or endoscope |
US6485413B1 (en) | 1991-04-29 | 2002-11-26 | The General Hospital Corporation | Methods and apparatus for forward-directed optical scanning instruments |
WO1992019930A1 (en) | 1991-04-29 | 1992-11-12 | Massachusetts Institute Of Technology | Method and apparatus for optical imaging and measurement |
US6501551B1 (en) | 1991-04-29 | 2002-12-31 | Massachusetts Institute Of Technology | Fiber optic imaging endoscope interferometer with at least one faraday rotator |
JPH05126725A (en) * | 1991-09-25 | 1993-05-21 | Fuji Photo Film Co Ltd | Scanning type analysis microscope |
JP3144849B2 (en) | 1991-09-30 | 2001-03-12 | 株式会社東芝 | Cardiovascular diagnostic device |
US5227912A (en) | 1991-10-30 | 1993-07-13 | Ho Ping Pei | Multiple-stage optical kerr gate system |
US5269309A (en) | 1991-12-11 | 1993-12-14 | Fort J Robert | Synthetic aperture ultrasound imaging system |
EP0626823B1 (en) | 1992-02-21 | 2000-04-19 | Boston Scientific Limited | Ultrasound imaging guidewire |
US5414623A (en) | 1992-05-08 | 1995-05-09 | Iowa State University Research Foundation | Optoelectronic system for implementation of iterative computer tomography algorithms |
US5373845A (en) | 1992-05-22 | 1994-12-20 | Echo Cath, Ltd. | Apparatus and method for forward looking volume imaging |
US6005916A (en) | 1992-10-14 | 1999-12-21 | Techniscan, Inc. | Apparatus and method for imaging with wavefields using inverse scattering techniques |
US5860934A (en) | 1992-12-21 | 1999-01-19 | Artann Corporation | Method and device for mechanical imaging of breast |
US5394268A (en) | 1993-02-05 | 1995-02-28 | Carnegie Mellon University | Field synthesis and optical subsectioning for standing wave microscopy |
GB9312327D0 (en) * | 1993-06-15 | 1993-07-28 | British Tech Group | Laser ultrasound probe and ablator |
US5546947A (en) | 1993-09-30 | 1996-08-20 | Terumo Kabushiki Kaisha | Ultrasonic endoprobe |
US5606975A (en) | 1994-09-19 | 1997-03-04 | The Board Of Trustees Of The Leland Stanford Junior University | Forward viewing ultrasonic imaging catheter |
US5635784A (en) | 1995-02-13 | 1997-06-03 | Seale; Joseph B. | Bearingless ultrasound-sweep rotor |
US6309352B1 (en) | 1996-01-31 | 2001-10-30 | Board Of Regents, The University Of Texas System | Real time optoacoustic monitoring of changes in tissue properties |
US6405069B1 (en) | 1996-01-31 | 2002-06-11 | Board Of Regents, The University Of Texas System | Time-resolved optoacoustic method and system for noninvasive monitoring of glucose |
US5840023A (en) * | 1996-01-31 | 1998-11-24 | Oraevsky; Alexander A. | Optoacoustic imaging for medical diagnosis |
US6108576A (en) | 1996-03-18 | 2000-08-22 | The Research Foundation Of City College Of New York | Time-resolved diffusion tomographic 2D and 3D imaging in highly scattering turbid media |
US5615675A (en) | 1996-04-19 | 1997-04-01 | Regents Of The University Of Michigan | Method and system for 3-D acoustic microscopy using short pulse excitation and 3-D acoustic microscope for use therein |
US5944687A (en) | 1996-04-24 | 1999-08-31 | The Regents Of The University Of California | Opto-acoustic transducer for medical applications |
US5713356A (en) | 1996-10-04 | 1998-02-03 | Optosonics, Inc. | Photoacoustic breast scanner |
US6424852B1 (en) | 1996-10-18 | 2002-07-23 | Lucid, Inc. | System for confocal imaging within dermal tissue |
US5904651A (en) | 1996-10-28 | 1999-05-18 | Ep Technologies, Inc. | Systems and methods for visualizing tissue during diagnostic or therapeutic procedures |
EP0840105A1 (en) | 1996-11-05 | 1998-05-06 | Orbisphere Laboratories Neuchatel Sa | Spectroscopic method and apparatus |
US5991697A (en) | 1996-12-31 | 1999-11-23 | The Regents Of The University Of California | Method and apparatus for optical Doppler tomographic imaging of fluid flow velocity in highly scattering media |
GB9704737D0 (en) | 1997-03-07 | 1997-04-23 | Optel Instr Limited | Biological measurement system |
GB9710049D0 (en) * | 1997-05-19 | 1997-07-09 | Nycomed Imaging As | Method |
US6007499A (en) | 1997-10-31 | 1999-12-28 | University Of Washington | Method and apparatus for medical procedures using high-intensity focused ultrasound |
US6831781B2 (en) | 1998-02-26 | 2004-12-14 | The General Hospital Corporation | Confocal microscopy with multi-spectral encoding and system and apparatus for spectroscopically encoded confocal microscopy |
EP1057063A4 (en) | 1998-02-26 | 2004-10-06 | Gen Hospital Corp | Confocal microscopy with multi-spectral encoding |
US6201608B1 (en) | 1998-03-13 | 2001-03-13 | Optical Biopsy Technologies, Inc. | Method and apparatus for measuring optical reflectivity and imaging through a scattering medium |
US5971998A (en) | 1998-03-31 | 1999-10-26 | Donald G. Russell | Support device and method for controlling breast thickness during stereotactic guided needle biopsy |
CN1089443C (en) * | 1998-04-24 | 2002-08-21 | 中国科学院上海光学精密机械研究所 | Incoherent laser radar system atmospheric sounding |
US6104942A (en) | 1998-05-12 | 2000-08-15 | Optosonics, Inc. | Thermoacoustic tissue scanner |
US6545264B1 (en) * | 1998-10-30 | 2003-04-08 | Affymetrix, Inc. | Systems and methods for high performance scanning |
US6413228B1 (en) | 1998-12-28 | 2002-07-02 | Pro Duct Health, Inc. | Devices, methods and systems for collecting material from a breast duct |
US6216025B1 (en) | 1999-02-02 | 2001-04-10 | Optosonics, Inc. | Thermoacoustic computed tomography scanner |
JP3745157B2 (en) * | 1999-04-06 | 2006-02-15 | 独立行政法人科学技術振興機構 | Photoacoustic microscope apparatus and video method thereof |
GB9915082D0 (en) | 1999-06-28 | 1999-08-25 | Univ London | Optical fibre probe |
US6717668B2 (en) | 2000-03-07 | 2004-04-06 | Chemimage Corporation | Simultaneous imaging and spectroscopy apparatus |
AU6894500A (en) * | 1999-08-06 | 2001-03-05 | Board Of Regents, The University Of Texas System | Optoacoustic monitoring of blood oxygenation |
US6567688B1 (en) | 1999-08-19 | 2003-05-20 | The Texas A&M University System | Methods and apparatus for scanning electromagnetically-induced thermoacoustic tomography |
US6694173B1 (en) | 1999-11-12 | 2004-02-17 | Thomas Bende | Non-contact photoacoustic spectroscopy for photoablation control |
US7198778B2 (en) * | 2000-01-18 | 2007-04-03 | Mallinckrodt Inc. | Tumor-targeted optical contrast agents |
US6751490B2 (en) | 2000-03-01 | 2004-06-15 | The Board Of Regents Of The University Of Texas System | Continuous optoacoustic monitoring of hemoglobin concentration and hematocrit |
US6466806B1 (en) | 2000-05-17 | 2002-10-15 | Card Guard Scientific Survival Ltd. | Photoacoustic material analysis |
US20030160957A1 (en) | 2000-07-14 | 2003-08-28 | Applera Corporation | Scanning system and method for scanning a plurality of samples |
IL138073A0 (en) | 2000-08-24 | 2001-10-31 | Glucon Inc | Photoacoustic assay and imaging system |
WO2002036015A1 (en) | 2000-10-30 | 2002-05-10 | The General Hospital Corporation | Optical methods and systems for tissue analysis |
EP1349493A2 (en) | 2001-01-12 | 2003-10-08 | The General Hospital Corporation | System and method for enabling simultaneous calibration and imaging of a medium |
US6987558B2 (en) * | 2001-01-16 | 2006-01-17 | Nikon Corporation | Reaction mass for a stage device |
US6626834B2 (en) | 2001-01-25 | 2003-09-30 | Shane Dunne | Spiral scanner with electronic control |
US7202091B2 (en) | 2001-04-11 | 2007-04-10 | Inlight Solutions, Inc. | Optically similar reference samples |
US7616986B2 (en) | 2001-05-07 | 2009-11-10 | University Of Washington | Optical fiber scanner for performing multimodal optical imaging |
US6806965B2 (en) | 2001-05-22 | 2004-10-19 | Zygo Corporation | Wavefront and intensity analyzer for collimated beams |
US6654630B2 (en) | 2001-05-31 | 2003-11-25 | Infraredx, Inc. | Apparatus and method for the optical imaging of tissue samples |
US6701181B2 (en) | 2001-05-31 | 2004-03-02 | Infraredx, Inc. | Multi-path optical catheter |
US6490470B1 (en) | 2001-06-19 | 2002-12-03 | Optosonics, Inc. | Thermoacoustic tissue scanner |
US6860855B2 (en) | 2001-11-19 | 2005-03-01 | Advanced Imaging Technologies, Inc. | System and method for tissue biopsy using ultrasonic imaging |
US7072045B2 (en) | 2002-01-16 | 2006-07-04 | The Regents Of The University Of California | High resolution optical coherence tomography with an improved depth range using an axicon lens |
US6650420B2 (en) | 2002-02-27 | 2003-11-18 | The United States Of America As Represented By The Secretary Of The Navy | Nanoscale vibrometric measurement apparatus and method |
IL148795A0 (en) * | 2002-03-20 | 2002-09-12 | Vital Medical Ltd | Apparatus and method for monitoring tissue vitality parameters for the diagnosis of body metabolic emergency state |
US7322972B2 (en) | 2002-04-10 | 2008-01-29 | The Regents Of The University Of California | In vivo port wine stain, burn and melanin depth determination using a photoacoustic probe |
WO2003105709A1 (en) | 2002-06-13 | 2003-12-24 | Möller-Wedel GmbH | Method and instrument for surgical navigation |
US6877894B2 (en) | 2002-09-24 | 2005-04-12 | Siemens Westinghouse Power Corporation | Self-aligning apparatus for acoustic thermography |
US7245789B2 (en) | 2002-10-07 | 2007-07-17 | Vascular Imaging Corporation | Systems and methods for minimally-invasive optical-acoustic imaging |
US7610080B1 (en) * | 2002-11-08 | 2009-10-27 | Wintec, Llc | Method and device for determining tension in ligaments and tendons |
WO2004062491A1 (en) | 2003-01-13 | 2004-07-29 | Glucon Inc. | Photoacoustic assay method and apparatus |
US20080194929A1 (en) * | 2003-04-01 | 2008-08-14 | Glucon, Inc. | Photoacoustic Assay Method and Apparatus |
JP4406226B2 (en) * | 2003-07-02 | 2010-01-27 | 株式会社東芝 | Biological information video device |
US20050015002A1 (en) | 2003-07-18 | 2005-01-20 | Dixon Gary S. | Integrated protocol for diagnosis, treatment, and prevention of bone mass degradation |
US20060181791A1 (en) * | 2003-07-31 | 2006-08-17 | Van Beek Michael C | Method and apparatus for determining a property of a fluid which flows through a biological tubular structure with variable numerical aperture |
US20070213590A1 (en) | 2003-10-09 | 2007-09-13 | Gyntec Medical, Inc. | Apparatus and methods for examining, visualizing, diagnosing, manipulating, treating and recording of abnormalities within interior regions of body cavities |
US20050143664A1 (en) | 2003-10-09 | 2005-06-30 | Zhongping Chen | Scanning probe using MEMS micromotor for endosocopic imaging |
US7266407B2 (en) | 2003-11-17 | 2007-09-04 | University Of Florida Research Foundation, Inc. | Multi-frequency microwave-induced thermoacoustic imaging of biological tissue |
US20050154308A1 (en) | 2003-12-30 | 2005-07-14 | Liposonix, Inc. | Disposable transducer seal |
US7357029B2 (en) * | 2004-03-31 | 2008-04-15 | Optometrix, Inc. | Thermal-acoustic scanning systems and methods |
FR2871358B1 (en) * | 2004-06-14 | 2007-02-09 | Mauna Kea Technologies Soc Par | METHOD AND SYSTEM FOR MICROSCOPIC MULTI-MARKING FIBER FLUORESCENCE IMAGING |
JP4494127B2 (en) | 2004-08-18 | 2010-06-30 | 富士フイルム株式会社 | Tomographic image observation device, endoscope device, and probe used for them |
JP2008510529A (en) * | 2004-08-27 | 2008-04-10 | エレックス メディカル プロプライエタリー リミテッド | Selective ophthalmic laser treatment |
EP1787105A2 (en) | 2004-09-10 | 2007-05-23 | The General Hospital Corporation | System and method for optical coherence imaging |
EP1807722B1 (en) | 2004-11-02 | 2022-08-10 | The General Hospital Corporation | Fiber-optic rotational device, optical system for imaging a sample |
US20060184042A1 (en) * | 2005-01-22 | 2006-08-17 | The Texas A&M University System | Method, system and apparatus for dark-field reflection-mode photoacoustic tomography |
US20060235299A1 (en) | 2005-04-13 | 2006-10-19 | Martinelli Michael A | Apparatus and method for intravascular imaging |
EP1874175A1 (en) * | 2005-04-19 | 2008-01-09 | Koninklijke Philips Electronics N.V. | Spectroscopic determination of analyte concentration |
US20070088206A1 (en) | 2005-10-14 | 2007-04-19 | Peyman Gholam A | Photoacoustic measurement of analyte concentration in the eye |
US20070093702A1 (en) * | 2005-10-26 | 2007-04-26 | Skyline Biomedical, Inc. | Apparatus and method for non-invasive and minimally-invasive sensing of parameters relating to blood |
US20070213618A1 (en) | 2006-01-17 | 2007-09-13 | University Of Washington | Scanning fiber-optic nonlinear optical imaging and spectroscopy endoscope |
US9439571B2 (en) | 2006-01-20 | 2016-09-13 | Washington University | Photoacoustic and thermoacoustic tomography for breast imaging |
JPWO2007088709A1 (en) * | 2006-01-31 | 2009-06-25 | 関西ティー・エル・オー株式会社 | Photoacoustic tomography apparatus and photoacoustic tomography method |
EP2034878A2 (en) | 2006-06-23 | 2009-03-18 | Koninklijke Philips Electronics N.V. | Timing controller for combined photoacoustic and ultrasound imager |
US7973927B2 (en) | 2006-09-29 | 2011-07-05 | Uwm Research Foundation, Inc. | Two-photon microscope with spectral resolution |
US8450674B2 (en) | 2009-11-10 | 2013-05-28 | California Institute Of Technology | Acoustic assisted phase conjugate optical tomography |
US20100056916A1 (en) | 2006-11-21 | 2010-03-04 | Koninklijke Philips Electronics N.V. | System, device, method, computer-readable medium, and use for in vivo imaging of tissue in an anatomical structure |
US20080173093A1 (en) | 2007-01-18 | 2008-07-24 | The Regents Of The University Of Michigan | System and method for photoacoustic tomography of joints |
US20110021924A1 (en) | 2007-02-09 | 2011-01-27 | Shriram Sethuraman | Intravascular photoacoustic and utrasound echo imaging |
US7576334B2 (en) | 2007-03-19 | 2009-08-18 | The Regents Of The University Of Michigan | Photoacoustic indicators |
US7541602B2 (en) * | 2007-06-04 | 2009-06-02 | Or-Nim Medical Ltd. | System and method for noninvasively monitoring conditions of a subject |
US8285362B2 (en) | 2007-06-28 | 2012-10-09 | W. L. Gore & Associates, Inc. | Catheter with deflectable imaging device |
JP5317449B2 (en) | 2007-09-12 | 2013-10-16 | キヤノン株式会社 | measuring device |
US7917312B2 (en) | 2007-10-18 | 2011-03-29 | Washington University | Photoacoustic doppler flow sensing and imaging |
EP2203733B1 (en) | 2007-10-25 | 2017-05-03 | Washington University in St. Louis | Confocal photoacoustic microscopy with optical lateral resolution |
US20140142404A1 (en) | 2008-10-23 | 2014-05-22 | The Washington University | Single-cell label-free photoacoustic flowoxigraphy in vivo |
WO2010048258A1 (en) | 2008-10-23 | 2010-04-29 | Washington University In St. Louis | Reflection-mode photoacoustic tomography using a flexibly-supported cantilever beam |
US20090116518A1 (en) | 2007-11-02 | 2009-05-07 | Pranalytica, Inc. | Multiplexing of optical beams using reversed laser scanning |
JP4829934B2 (en) | 2008-07-11 | 2011-12-07 | キヤノン株式会社 | Inspection device |
JP5451014B2 (en) | 2008-09-10 | 2014-03-26 | キヤノン株式会社 | Photoacoustic device |
US8416421B2 (en) | 2008-10-01 | 2013-04-09 | Washington University | Optical coherence computed tomography |
US9351705B2 (en) | 2009-01-09 | 2016-05-31 | Washington University | Miniaturized photoacoustic imaging apparatus including a rotatable reflector |
US20110282192A1 (en) * | 2009-01-29 | 2011-11-17 | Noel Axelrod | Multimodal depth-resolving endoscope |
US8016419B2 (en) * | 2009-03-17 | 2011-09-13 | The Uwm Research Foundation, Inc. | Systems and methods for photoacoustic opthalmoscopy |
US20100285518A1 (en) | 2009-04-20 | 2010-11-11 | The Curators Of The University Of Missouri | Photoacoustic detection of analytes in solid tissue and detection system |
US9057695B2 (en) | 2009-09-24 | 2015-06-16 | Canon Kabushiki Kaisha | Apparatus and method for irradiating a scattering medium with a reconstructive wave |
US8862206B2 (en) * | 2009-11-12 | 2014-10-14 | Virginia Tech Intellectual Properties, Inc. | Extended interior methods and systems for spectral, optical, and photoacoustic imaging |
WO2011091360A2 (en) | 2010-01-25 | 2011-07-28 | Washington University | Optical time reversal by ultrasonic encoding in biological tissue |
US9335605B2 (en) | 2010-01-25 | 2016-05-10 | Washington University | Iteration of optical time reversal by ultrasonic encoding in biological tissue |
US9086365B2 (en) | 2010-04-09 | 2015-07-21 | Lihong Wang | Quantification of optical absorption coefficients using acoustic spectra in photoacoustic tomography |
US10292589B2 (en) | 2010-09-20 | 2019-05-21 | California Institute Of Technology | Acoustic-assisted iterative wave form optimization for deep tissue focusing |
US8997572B2 (en) | 2011-02-11 | 2015-04-07 | Washington University | Multi-focus optical-resolution photoacoustic microscopy with ultrasonic array detection |
US20120275262A1 (en) | 2011-04-29 | 2012-11-01 | Washington University | Section-illumination photoacoustic microscopy with ultrasonic array detection |
WO2013086293A1 (en) | 2011-12-08 | 2013-06-13 | Washington University | In vivo label-free histology by photoacoustic microscopy of cell nuclei |
-
2008
- 2008-10-24 EP EP08842292.8A patent/EP2203733B1/en active Active
- 2008-10-24 CN CN2008801235613A patent/CN101918811B/en active Active
- 2008-10-24 WO PCT/US2008/081167 patent/WO2009055705A2/en active Application Filing
- 2008-10-24 JP JP2010531281A patent/JP5643101B2/en active Active
- 2008-10-24 EP EP17159220.7A patent/EP3229010A3/en not_active Withdrawn
- 2008-10-24 US US12/739,589 patent/US8454512B2/en active Active
-
2013
- 2013-05-01 US US13/874,653 patent/US9226666B2/en active Active
-
2014
- 2014-10-30 JP JP2014221837A patent/JP6006773B2/en active Active
-
2015
- 2015-11-24 US US14/950,189 patent/US20160081558A1/en not_active Abandoned
-
2016
- 2016-05-06 US US15/148,685 patent/US10433733B2/en active Active
Patent Citations (2)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20090054763A1 (en) * | 2006-01-19 | 2009-02-26 | The Regents Of The University Of Michigan | System and method for spectroscopic photoacoustic tomography |
US20090227997A1 (en) * | 2006-01-19 | 2009-09-10 | The Regents Of The University Of Michigan | System and method for photoacoustic imaging and monitoring of laser therapy |
Cited By (12)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US11029287B2 (en) | 2011-02-11 | 2021-06-08 | California Institute Of Technology | Multi-focus optical-resolution photoacoustic microscopy with ultrasonic array detection |
US11020006B2 (en) | 2012-10-18 | 2021-06-01 | California Institute Of Technology | Transcranial photoacoustic/thermoacoustic tomography brain imaging informed by adjunct image data |
US11137375B2 (en) | 2013-11-19 | 2021-10-05 | California Institute Of Technology | Systems and methods of grueneisen-relaxation photoacoustic microscopy and photoacoustic wavefront shaping |
US10209226B2 (en) | 2014-02-26 | 2019-02-19 | Olympus Corporation | Photoacoustic microscope apparatus |
ITUA20163677A1 (en) * | 2016-05-23 | 2017-11-23 | Scuola Superiore Di Studi Univ E Di Perfezionamento Santanna | ULTRASONIC STIMULATION SYSTEM OF A VITRO SAMPLE |
US11730375B2 (en) | 2016-12-14 | 2023-08-22 | Hyundai Motor Company | Photoacoustic, noninvasive, and continuous blood glucose measurement device |
US11209532B2 (en) | 2017-01-23 | 2021-12-28 | Olympus Corporation | Signal processing device, photoacoustic wave image-acquisition device, and signal processing method |
US11672426B2 (en) | 2017-05-10 | 2023-06-13 | California Institute Of Technology | Snapshot photoacoustic photography using an ergodic relay |
US11530979B2 (en) | 2018-08-14 | 2022-12-20 | California Institute Of Technology | Multifocal photoacoustic microscopy through an ergodic relay |
US11592652B2 (en) | 2018-09-04 | 2023-02-28 | California Institute Of Technology | Enhanced-resolution infrared photoacoustic microscopy and spectroscopy |
US11369280B2 (en) | 2019-03-01 | 2022-06-28 | California Institute Of Technology | Velocity-matched ultrasonic tagging in photoacoustic flowgraphy |
WO2020205809A1 (en) * | 2019-03-29 | 2020-10-08 | The Research Foundation For The State University Of New York | Photoacoustic breast imaging system and method |
Also Published As
Publication number | Publication date |
---|---|
EP2203733A2 (en) | 2010-07-07 |
JP2011519281A (en) | 2011-07-07 |
US20100268042A1 (en) | 2010-10-21 |
CN101918811B (en) | 2013-07-31 |
CN101918811A (en) | 2010-12-15 |
JP2015062678A (en) | 2015-04-09 |
JP6006773B2 (en) | 2016-10-12 |
US20130245406A1 (en) | 2013-09-19 |
US9226666B2 (en) | 2016-01-05 |
EP3229010A2 (en) | 2017-10-11 |
WO2009055705A2 (en) | 2009-04-30 |
US20160249812A1 (en) | 2016-09-01 |
US8454512B2 (en) | 2013-06-04 |
EP2203733A4 (en) | 2014-01-01 |
WO2009055705A3 (en) | 2009-06-11 |
EP3229010A3 (en) | 2018-01-10 |
JP5643101B2 (en) | 2014-12-17 |
EP2203733B1 (en) | 2017-05-03 |
US10433733B2 (en) | 2019-10-08 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
US9226666B2 (en) | Confocal photoacoustic microscopy with optical lateral resolution | |
US20210333241A1 (en) | Multi-focus optical-resolution photoacoustic microscopy with ultrasonic array detection | |
Upputuri et al. | Fast photoacoustic imaging systems using pulsed laser diodes: a review | |
US20060184042A1 (en) | Method, system and apparatus for dark-field reflection-mode photoacoustic tomography | |
US9528966B2 (en) | Reflection-mode photoacoustic tomography using a flexibly-supported cantilever beam | |
JP5349839B2 (en) | Biological information imaging device | |
US20120275262A1 (en) | Section-illumination photoacoustic microscopy with ultrasonic array detection | |
JP2011217767A (en) | Photoacoustic imaging apparatus and photoacoustic imaging method | |
US20130190594A1 (en) | Scanning Optoacoustic Imaging System with High Resolution and Improved Signal Collection Efficiency | |
CN104323762A (en) | Photoacoustic microscopy imaging-based quantitative detection device for nevus flammeus blood vessel | |
Zhang et al. | Three-dimensional photoacoustic imaging of vascular anatomy in small animals using an optical detection system | |
Maslov et al. | Photoacoustic microscopy with submicron resolution | |
Dahal et al. | Characterization of multiphoton photoacoustic spectroscopy for subsurface brain tissue diagnosis and imaging | |
Maslov et al. | Second generation optical-resolution photoacoustic microscopy | |
Hu et al. | Optical-resolution photoacoustic microscopy for in vivo volumetric microvascular imaging in intact tissues | |
RU169745U1 (en) | Optoacoustic Bioimaging Microscope | |
Thakur et al. | Photoacoustic imaging instrumentation for life sciences | |
Li | Label-Free Photoacoustic Microscopy for Biomedical and Point-of-Care Applications | |
Steenbergen | -Photoacoustic Tomography | |
Haji Reza | All-Optical and Endoscopic Photoacoustic Microscopy | |
Abraham et al. | Single-shot cross-correlation system for longitudinal imaging in biological tissues | |
Jian et al. | Multispectral adaptive optics photoacoustic imaging | |
Aguirre et al. | Broadband mesoscopic optoacoustic tomography |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
AS | Assignment |
Owner name: WASHINGTON UNIVERSITY, MISSOURI Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNORS:WANG, LIHONG;MASLOV, KONSTANTIN;SIGNING DATES FROM 20120111 TO 20120118;REEL/FRAME:038047/0193 |
|
AS | Assignment |
Owner name: NATIONAL INSTITUTES OF HEALTH (NIH), U.S. DEPT. OF Free format text: CONFIRMATORY LICENSE;ASSIGNOR:WASHINGTON UNIVERSITY;REEL/FRAME:039266/0193 Effective date: 20160601 |
|
STCB | Information on status: application discontinuation |
Free format text: ABANDONED -- FAILURE TO RESPOND TO AN OFFICE ACTION |
|
AS | Assignment |
Owner name: NATIONAL INSTITUTES OF HEALTH - DIRECTOR DEITR, MA Free format text: CONFIRMATORY LICENSE;ASSIGNOR:WASHINGTON UNIVERSITY IN ST. LOUIS;REEL/FRAME:047949/0077 Effective date: 20181024 |
|
AS | Assignment |
Owner name: NATIONAL INSTITUTES OF HEALTH - DIRECTOR DEITR, MA Free format text: CONFIRMATORY LICENSE;ASSIGNOR:WASHINGTON UNIVERSITY IN ST. LOUIS;REEL/FRAME:047812/0492 Effective date: 20181024 |