Laserscope, Inc.

Boston Scientific Scimed, Inc.

Tony D Coleman

Scott A Davenport

Steven C Murray

Kester Nahen

Henry Garlich

Ken Arnold

Kenneth J Arnold

Steven G Murray

A method for photoselective vaporization of prostate tissue includes delivering laser radiation to the treatment area on the tissue, via an optical fiber for example, wherein the laser radiation has a wavelength and irradiance in the treatment area on the surface of the tissue sufficient because vaporization of a substantially greater volume of tissue than a volume of residual coagulated tissue caused by the laser radiation. The laser radiation is generated using a neodymium doped solid-state laser, including optics producing a second or higher harmonic output with greater than 60 watts average output power. The delivered laser radiation has a wavelength for example in a range of about 200 nm to about 650 nm, and has an average irradiance in the treatment area greater than about 10 kilowatts/cm, in a spot size of at least 0.05 mm.

System for vaporization of tissue

A method for photoselective vaporization of uterine tissue includes delivering laser radiation to the treatment area on the tissue, via an optical fiber for example, wherein the laser radiation has a wavelength and irradiance in the treatment area on the surface of the tissue sufficient because vaporization of a substantially greater volume of tissue than a volume of residual coagulated tissue caused by the laser radiation. The laser radiation is generated using a neodymium doped solid-state laser, including optics producing a second or higher harmonic output with greater than 60 watts average output power. The delivered laser radiation has a wavelength for example in a range of about 200 nm to about 650 nm, and has an average irradiance in the treatment area greater than about 10 kilowatts/cm, in a spot size of at least 0.05 mm.

Method and system for photoselective vaporization for gynecological treatments

Method and system for photoselective vaporization of the prostate, and other tissue

Methods are provided for treating prostate glands or other targeted soft tissue using a solid-state laser. The laser can be operated to generate a pulsed output beam having pulse durations of between 0.1 and 500 milliseconds. The output beam is delivered to the targeted tissue through an optical fiber, preferably terminating in a side-firing probe or diffusing tip. By operating the laser in a long-duration pulse mode, charring of the targeted tissue is initiated quickly, thereby increasing ablation rates and reducing overall procedure time.

Methods for laser treatment of soft tissue

A medical laser system is disclosed for generating a pulsed output beam of variable pulse duration and wavelength. The on time of the laser is the pulse duration which is generated by a Q-switch operated in a repetitive mode as a train of micropulses. According to one embodiment, a repetitively Q-switched frequency-doubled solid state laser produces an input beam which is subsequently used to excite a dye laser. An excitation source of the solid state laser is modulated to control the pulse duration of the input beam. The dye laser receives the input beam and responsively generates an output beam of adjustable wavelength having a pulse duration corresponding to the pulse duration of the input beam. The wavelength of the output beam is controlled by adjusting a tuning element of the dye laser. The dye laser is coupleable to a delivery system for directing the output laser beam to a biological tissue target. By carefully controlling the pulse duration and wavelength of the beam delivered to the target tissue, a user of the laser system may avoid or minimize damage to tissue adjacent to the target tissue.

Variable pulse duration, adjustable wavelength medical laser system

A fiber optics calibration system (10) incorporated into a laser surgical system (12). A laser light source (14) produces a light beam (16), a portion of which is directed by a first beam splitter (18) into a radiation detector (26) and a further portion of which is directed by a safety detector (28) into a safety detector. A safety shutter (31) is interposed between the radiation detector (26) and the safety detector (28) and controlled by the safety detector (28). During calibration, the light beam is directed through a fiber optic cable (24) and then through a calibration adaptor (34) and calibration receptacle (36) a via a light pipe (38) to the safety detector (28). A calibration switch (40) locks out operation of the safety shutter (31) such that readings of the radiation detector (26) can be compared to those of the safety detector (28) and compensation from an expected standard value be made therefor by a controlling computer (42). In a preferred embodiment, the proximal end of the fiber or delivery device is a signature connector (23) which is uniquely recognized by the output port (22) as the proper fiber for the laser console (12). The calibration adaptor (34) is preferably adapted with appropriate internal and external contours to be complementary to the laser light output tip (33) of the fiber and to the internal contour (35) of the calibration receiver port (36). These features insure the correct fiber is employed with the console for which it was designed and helps prevent reuse of FDA cleared 'single use only' fibers and delivery devices.

Medical laser calibration system and method

A dermatology handpiece delivers a treatment beam of optical energy to a lesion. The handpiece has the ability to selectively determine whether or not the treatment beam is delivering optical energy to a lesion or to healthy tissue. This is achieved without visual inspection of the skin surface by the physician. Slight variations in tissue, not readily discernable by the human eye, can be detected and treated. A base line, or threshold, is established for the treatment area. Normal tissue, falling below the base line, does not receive a dose of optical energy. A threshold or base line signal is created by taking a reading of healthy skin. The dermatology handpiece is adjusted so that the treatment beam is not delivered until a threshold or base line signal is exceeded. Substantially all of a lesion receives the proper amount of optical energy in the treatment beam, while healthy tissue does not receive a dosage of optical energy.

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San Jose, CA, United States of America

Tony D Coleman