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WO1996018347A1 - Sonde en fibre optique vectrice d'un laser et son utilisation - Google Patents

Sonde en fibre optique vectrice d'un laser et son utilisation Download PDF

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Publication number
WO1996018347A1
WO1996018347A1 PCT/GB1995/002920 GB9502920W WO9618347A1 WO 1996018347 A1 WO1996018347 A1 WO 1996018347A1 GB 9502920 W GB9502920 W GB 9502920W WO 9618347 A1 WO9618347 A1 WO 9618347A1
Authority
WO
WIPO (PCT)
Prior art keywords
probe
fibre
optical fibre
sheath
laser
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.)
Ceased
Application number
PCT/GB1995/002920
Other languages
English (en)
Inventor
Lee Brine
David James Pointer
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Individual
Original Assignee
Individual
Priority date (The priority date 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 date listed.)
Filing date
Publication date
Priority claimed from GBGB9425216.0A external-priority patent/GB9425216D0/en
Application filed by Individual filed Critical Individual
Priority to AU41845/96A priority Critical patent/AU4184596A/en
Publication of WO1996018347A1 publication Critical patent/WO1996018347A1/fr
Anticipated expiration legal-status Critical
Ceased legal-status Critical Current

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Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B18/18—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves
    • A61B18/20—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using laser
    • A61B18/22—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using laser the beam being directed along or through a flexible conduit, e.g. an optical fibre; Couplings or hand-pieces therefor
    • A61B18/24—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using laser the beam being directed along or through a flexible conduit, e.g. an optical fibre; Couplings or hand-pieces therefor with a catheter
    • G—PHYSICS
    • G02—OPTICS
    • G02B—OPTICAL ELEMENTS, SYSTEMS OR APPARATUS
    • G02B6/00—Light guides; Structural details of arrangements comprising light guides and other optical elements, e.g. couplings
    • G02B6/24—Coupling light guides
    • G02B6/26—Optical coupling means
    • G02B6/262—Optical details of coupling light into, or out of, or between fibre ends, e.g. special fibre end shapes or associated optical elements
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00—Surgical instruments, devices or methods
    • A61B17/00234—Surgical instruments, devices or methods for minimally invasive surgery
    • A61B2017/00238—Type of minimally invasive operation
    • A61B2017/00274—Prostate operation, e.g. prostatectomy, turp, bhp treatment
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B2018/00315—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body for treatment of particular body parts
    • A61B2018/00547—Prostate
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B18/18—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves
    • A61B18/20—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using laser
    • A61B18/22—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using laser the beam being directed along or through a flexible conduit, e.g. an optical fibre; Couplings or hand-pieces therefor
    • A61B2018/2255—Optical elements at the distal end of probe tips
    • A61B2018/2272—Optical elements at the distal end of probe tips with reflective or refractive surfaces for deflecting the beam

Definitions

  • the present invention relates to a probe for the delivery of laser radiation through an optical fibre to a desired target, and in particular to a probe for use in internal endoscopic treatment of the body with laser radiation. It is applicable to any treatment in which laser radiation is incident on body tissue to, for example, coagulate or vaporise the tissue.
  • One such form of treatment is photo-dynamic therapy.
  • Another is in urological applications, such as the treatment of benign Prostatic Hyperplasia (BPH) .
  • BPH is a long term condition where the outflow of urine from the bladder is restricted by an enlarged prostate gland. It is very common among elderly men. This condition was previously treated by surgical resection of the prostate to remove the obstruction.
  • this technique has disadvantages such as relatively high mortality rates, high incidence of morbidity, post-operative bleeding and long recovery times. There is therefore a desire to find an alternative form of treatment.
  • Endoscopic optical fibre laser probes are used as an alternative method of treating BPH.
  • the probes are inserted via an endoscope into the urethra and used to deliver laser radiation to the urethral wall and underlying prostatic tissue.
  • the laser energy coagulates, vaporises and in some cases chars the tissue, thereby effecting removal of the obstruction.
  • Laser treatment of BPH is preferred in many cases to resection, in view of its minimally invasive nature. This results in less post-operative trauma and risk to the patient.
  • the laser probes which are currently in use suffer from a number of disadvantages which limit their usefulness and practicability.
  • One problem encountered with prior art laser probes is the inability of the end of the probe and in particular the optical fibre, to withstand the high temperatures which can occur in use in the region of the operating tip of the probe.
  • the tissue temperature can exceed 1000°C, and the optical fibre probes frequently fail at these temperatures.
  • destruction of the probe in use is a relatively common occurrence. This is particularly the case if the probe touches the tissue being treated, as this creates intense local temperatures. This is, as might be expected, a relatively frequent event in the confined environment of endoscopic treatment.
  • probes have been designed with some form of protective, metal-coated cap surrounding the fibre tip, which is designed to hold the fibre tip away from the tissue.
  • the caps are covered with a metallic coating an opening in the cap must be left to allow the laser radiation to exit, thus exposing the optical fibre tip. It is still therefore possible to touch the optical fibre onto the tissue being treated.
  • probes with such protective caps have been found to fail at the temperatures encountered.
  • the problem of destruction of the probe by high temperatures is exacerbated by the preferred practice of irrigating the probe and treated tissue during treatment with, for example, water or saline solution.
  • the irrigant acts to cool the probe and the tissue surface, and to remove any debris.
  • the cool irrigant can lead to a high temperature gradient across the probe, and thus cause failure by thermal shock.
  • Tissue undergoes a number of processes on heating. At temperatures above 60°C coagulation of the tissue (i.e. denaturation of the protein) occurs. This leads to marked shrinkage of the collagen matrix, therefore decreasing the tissue size.
  • the heat generated by the laser is conducted to the underlying tissue and thus the effectively heated region of tissue is relatively deep and so accordingly is the necrotic zone.
  • the cell water boils and ruptures the cell walls (i.e. the tissue is vaporised) . Because of the high latent heat involved, boiling and vaporisation is more or less limited to the site of absorption of the heat radiation and thus the depth of heating (i.e. the necrotic zone) is severely restricted.
  • the preferred method of treatment is to coagulate the tissue whilst avoiding vaporisation (and particularly carbonisation) to achieve the greatest necrotic depth.
  • vaporisation and particularly carbonisation
  • the treatment is less effective than theoretically possible, and the limitations of the - A - probes themselves result in an increased chance of probe destruction in use.
  • an optical fibre laser delivery probe for the endoscopic delivery of laser radiation to a target comprising: an optical fibre for receiving laser radiation from a laser source and adapted to transmit the laser radiation from its distal end for delivery to the target,• wherein the distal end of the optical fibre is enclosed by a fused silica or synthetic fused silica sheath which is affixed over the distal end of the optical fibre.
  • the fused or synthetic fused silica sheath is able to withstand the high temperatures encountered during use of the probe without damage thereto, even in an irrigated environment. It will also shield and protect the optical fibre from the high temperatures. Thus the probe of the present invention is significantly less likely to destruct in use. Furthermore, as fused or synthetic fused silica is transparent to the laser radiation, the sheath does not have to have a gap for the laser radiation to pass through. Thus the fibre end can be completely enclosed to prevent all possibility of it coming into contact with the tissue being treated. The sheath of the present invention protects the fibre end and substantially prevents destruction of the probe in use.
  • the ability of the fused silica or synthetic fused silica sheath to withstand high temperatures also means that the probe of the present invention can be used in contact with the tissue being treated, without damage thereto.
  • the probe of the present invention can be used to vaporise tissue by deliberately contacting it therewith. The same probe can therefore be used to initially coagulate and then to vaporise tissue. This is a less complicated and expensive procedure than in the prior art where different probes for each different operation are required.
  • the optical fibre is preferably adapted to transmit the laser radiation from its distal end at an angle to the longitudinal axis of the fibre. This allows the probe to radiate a target to the side of the probe. This permits radiating the target by placing the probe adjacent the target tissue. The probe itself does not then obstruct the operator's view of the target through the endoscope.
  • the transmission of the laser radiation out of the fibre end can be achieved by any suitable means, such as by a mirrored surface or dielectric coating on the fibre end.
  • the optical fibre is adapted to be forward firing, i.e. it is adapted to transmit the laser radiation at an angle of 65°-85°, most preferably 70°-80°, to the optical fibre's longitudinal axis in a direction forward of the distal end of the probe.
  • the distance travelled by the laser radiation before it reaches the target is increased, therefore allowing greater beam divergence.
  • Greater beam divergence provides a larger spot size on the target and thus lowers the power density of the laser energy at the target.
  • a lower power density means that more energy can.be supplied to the target whilst maintaining the superficial tissue below the vaporisation threshold temperature.
  • the forward-firing transmission of the laser beam from the optical fibre end can again be achieved by an appropriately positioned mirrored or dielectric surface in the path of the laser beam.
  • this is preferably achieved by partial or total internal reflection at the suitably polished distal end of the optical fibre.
  • a polished fibre end is generally less expensive and complex to provide than a mirrored or dielectric surface.
  • the use of total internal reflection, for example, to deflect the laser beam is more efficient than using mirrored coatings, etc., alone and thus there is less energy loss at the fibre tip.
  • the forward firing transmission of the laser beam is achieved by means of partial internal reflection at the suitably polished distal end of the optical fibre.
  • the internal reflectivity of the distal end surface of the optical fibre is 80-90%, most preferably 82%.
  • the use of partial internal reflection allows some energy to be delivered into areas other than the main exit area of the beam. This diffusion of the energy reduces the amount of thermal shock across the outer cap, thus helping to alleviate cracking and failure at higher power settings and/or in contact mode.
  • the non-reflected radiation can, for example, gently heat the probe tip, which increases the durability of the probe tip in particular with respect to sudden contact with tissue and/or when the irrigant flow is stopped.
  • the sheath covering the fibre end is preferably arranged to maintain a sealed chamber enclosing the fibre end and containing air or any other suitable gas, such that partial or total internal reflection can occur at the glass-to-air or glass-to-gas interface at the distal end of the fibre.
  • a sealed chamber enclosing the fibre end and containing air or any other suitable gas, such that partial or total internal reflection can occur at the glass-to-air or glass-to-gas interface at the distal end of the fibre.
  • a mirror coating may also be provided on the polished end surface to increase the efficiency of the partial or total internal reflection.
  • the sealed glass-to-air or glass-to-gas interface provided by the sheath of the present invention also ensures that partial or total internal reflection will still occur even in a completely irrigated environment.
  • the optical fibre of the present invention is also preferably arranged to provide a widely divergent laser beam i.e. one having a cone angle of at least 20°.
  • the cone angle of the laser beam is defined as the cone angle of the cone which encompasses 86% of the total energy of the laser beam.
  • This widely divergent beam also helps to provide the largest possible spot size on the target being treated, thus again lowering the power density at the target.
  • a widely divergent beam can be achieved by the lensing effect of the curved surface of the optical fibre and/or sheath through which the beam exits the fibre and sheath (when the beam exits at an angle to the optical axis of the fibre) .
  • the curvature and shape of the end portion of the fibre, the curved fibre surface, the fibre end surface, and/or sheath can be varied appropriately to select the divergence of the beam.
  • the sheath covering the fibre is preferably spaced from the curved surface of the optical fibre at the point where the beam exits the fibre to create an glass-to-air or glass-to-gas interface, as this enhances the lensing effect of the optical fibre surface.
  • the optical fibre used preferably has the largest diameter suitable for endoscopic use in the application concerned. Fibres having diameters of 500-1200 ⁇ m are suitable. For BPH treatment, for example, a fibre of 1000 ⁇ m diameter is preferably used. A large fibre provides a large initial spot and thus facilitates a larger spot size and lower power density on the target. A large fibre is also inherently more rigid, enabling more control and accurate positioning of the fibre whilst in the body lumen.
  • the sheath of the present invention is preferably of sufficient diameter to space the tissue being treated from the optical fibre as far as is practicable. It should preferably achieve a stand-off or spacing between the target and fibre, whilst still passing through the working endoscope.
  • a sheath outer diameter of at least 1.5 mm is preferred. In BPH applications an outer diameter of at least 2 mm, preferably 2-2.8 mm, is most suitable. This spacing of the tissue from the fibre by the sheath lengthens the distance the laser beam must travel from the fibre to its target and thus leads to an increased spot size and lower power density on the target.
  • the sheath of the present invention preferably has a relatively rounded, blunt end so as to prevent damage to any tissue it may contact.
  • the sheath is preferably arranged such that the laser beam exiting the fibre passes through a sheath wall of uniform thickness. This can be achieved by spacing the sheath a suitable distance e.g. 2-3 mm, from the fibre end, such that the curved end surface of the sheath has ended by the fibre exit point.
  • the sheath also acts as a heat sink in use, and thus is preferably sufficiently large to do this effectively. In the case of BPH, it is preferably at least 12 mm in length in order to act as a suitable heat sink.
  • an optical fibre laser delivery probe for the endoscopic delivery of laser radiation to a target, comprising: an optical fibre for receiving laser radiation from a laser source and adapted to transmit the laser radiation from its distal end for delivery to the target; wherein the optical fibre is adapted to transmit the laser radiation at an angle of 65°-85° to the longitudinal axis of the optical fibre in a direction forward of the fibre distal end and is adapted to provide a laser beam having a cone angle as defined herein of greater than 20°, the probe further comprising a sheath transparent to the laser radiation enclosing the distal end of the optical fibre and having an outer diameter of at least 1.5 mm.
  • the probe according to the second aspect of the present invention can include any or all of the preferred features of the invention.
  • the sheath for the second aspect does not have to be of fused silica or synthetic fused silica, although it is preferably made from either of those materials. It could comprise for example borosilicate glass (e.g. Pyrex (RT ) ) , or any other suitably transparent substance which can withstand temperatures up to 1000°C.
  • the probe of the present invention including a synthetic fused silica or a fused silica sheath is suitable for use in contact with the tissue being treated, i.e. it can cause high local temperatures in order to vaporise the tissue without damage to the probe itself.
  • the probe can be used in contact mode using high power settings to achieve charring and vaporisation, thus allowing debulking of obstructive tissue. It is therefore possible to use the probe of the present invention initially to coagulate tissue and then to place it in contact with the tissue to vaporise it.
  • a method of treating body tissue using the optical fibre delivery probe of the present invention comprising: delivering laser radiation to the tissue target using the probe without deliberately contacting the tissue to coagulate the tissue; and then moving said probe into contact with the tissue and increasing the laser power to the probe to vaporise the tissue.
  • Figure 1 is a schematic view of the laser delivery probe of the present invention
  • Figure 2 is a cross section of the laser delivery probe of the present invention
  • Figure 3 is a cross section along ZZ of the probe shown in Figure 2.
  • the laser treatment assembly 1 includes a length of flexible of optical fibre 2 which can be connected via a connector 3 at one end to a laser source 4.
  • the connector 3 can be any standard connector, such as an S A 905 connector.
  • the laser 4 used with the probe can suitably for BPH applications be one generating energy within the infrared wavelength range of 750 to 1500 nanometers which has a low absorption coefficient in water.
  • An Nd-Yag laser with an output of 1064 nanometers is preferred.
  • lasers having wavelengths within the transmission range of silica optical fibres, i.e. approximately 300-2400 nm, can be used.
  • a handle 5 is fitted on to the fibre 2 at an appropriate point thereon.
  • a suitable handle is a movable lockable standard commercially available Torey Borst handle.
  • the distal end of the fibre 2 comprises the probe 6 which is to be inserted into the body lumen during treatment.
  • Figure 2 shows a cross section of the probe 6.
  • the optical fibre 2 includes a round core 8 and a surrounding polymer cladding 9.
  • the fibre is preferably 1000 ⁇ m in diameter for BPH treatment.
  • the fibre core 8 and the cladding 9 have centres of curvature at the longitudinal axis,10 of the fibre.
  • the cladding 9 is stripped back from the distal end of the fibre for a distance not less than 4 mm.
  • a cylindrical protective sheath 11 of fused silica or synthetic fused silica is placed over the exposed end of the fibre and forms an airtight attachment to the cladding 9 (which also spaces the sheath from the curved walls of the fibre core 8) .
  • the sheath 11 encloses a trapped volume of air 12. This trapped volume of air ensures a glass to air interface at the end 13 of fibre core 8, and around the curved surface of the exposed core of the fibre 8 (due to the walls of the sheath 11 being spaced apart from the core 8 by the cladding 9) .
  • the sheath 11 is held in position by a high temperature heat shrink outer cover 16. The sheath 11 will often be in contact with the tissue during use, which creates very high local temperature.
  • the heat shrink outer cover 16 is approximately 50 mm in length and terminates at the same location as the cladding 9 at its distal end.
  • a coloured indicator line 17 may be positioned between the sheath 16 and the cladding 9 in line focus with the exiting laser beam 14 on the opposite side of the probe to the exit side of the laser beam. This line 17 acts as an alignment mark for the surgeon to show the direction of .the laser beam in use.
  • the sheath 11 is positioned at least 2 mm from the tip of the polished fibre core 8, such that the laser beam does not exit the sheath through any part of its curved end. This ensures that the laser beam exits via a uniform thickness wall of the sheath. This reduces thermal shock across the sheath wall, and the risk of distortion being introduced into the laser beam by any variations in the sheath wall.
  • the probe should be a relatively large diameter to achieve a relatively large stand-off (i.e. spacing) between the tissue and fibre, but small enough to pass through the working endoscope.
  • the end surface 13 of the fibre reflects the laser beam travelling along the optical fibre out of the end of the probe as a divergent beam 14 by internal reflection.
  • the internal reflection results from the refractive index difference between the glass core 8 and the air 12 trapped by the sheath 11.
  • the surface 13 is formed at an angle ⁇ : to the fibre axis 10 which exceeds the critical angle for total internal reflection for the majority, but not all, of the optical rays travelling down the fibre.
  • the surface 13 directs the laser beam 14 out of the fibre with an axis 15 that is not orthogonal to, but is directed beyond the distal end of the probe at an angle to the fibre axis 10, i.e. the probe is forward-firing.
  • the optimum angle ⁇ for a suitable forward firing angle which will also achieve sufficient radiation transmission from the optical fibre depends upon the refractive index of the core 8, the wavelength of the radiation, and the numerical aperture of the optical fibre.
  • the angle ⁇ 2 will be between 35°-45° and this will provide an exiting laser beam 14 with an axis 15 at an angle ⁇ 2 of 65-85° to the fibre axis.
  • a refractive index of 1.47 for a typical fibre core and a numerical aperture of 0.4 an angle Q 1 which reflects a substantial amount of the laser radiation in the fibre will be about 40°. This angle would result in the exiting beam 14 having a centre line 15 making an angle ⁇ 2 of about 75° with the optical fibre axis.
  • the preferred exit angles for the exiting laser beam 14 are for it to be forward-firing with the central beam axis 15 at an angle ⁇ 2 of 65° to 85°, preferably
  • the probe of the present invention is adapted to deliver a widely divergent beam 14, i.e. one in which 86% of the laser beam energy is encompassed by a cone having a cone angle of at least 20°.
  • the cone angle can suitably be from 30°-50°. This is illustrated in Figure 3.
  • the divergent beam profile is controlled primarily by the interface between the air 12 and the curved surface of the optical fibre core 8 through which the laser radiation exits after reflection from the surface 13.
  • the curved surface of the fibre core 8 acts as a cylindrical lens due to the glass-to-air interface and thus creates a widely divergent exit beam.
  • the probe 6 is inserted with an endoscope into the body lumen, such as the prostatic urethra, to position the end of the probe 6 suitably adjacent to the tissue to be treated.
  • Laser power can then be directed using the probe onto the tissue.
  • the probe of the present invention allows a relatively large amount of laser energy to be delivered with a large spot size, thus providing a lower power density. In this manner, the probe of the present invention can achieve coagulation of a large area of tissue, without vaporisation or carbonisation occurring.
  • Laser energy is typically delivered at power of 40W-60 for between 30-90 seconds.
  • Laser radiation application is repeated until the desired area of tissue has been fully coagulated.
  • the outer surface of the probe is typically irrigated by a cooling fluid such as water or saline solution.
  • the probe of the present invention can also be used to vaporise and carbonise tissue, by increasing the laser power and moving the probe into direct contact with the tissue, thus creating intense local heating. This can be performed after coagulation, to immediately remove some of the obstructing tissue.

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  • Physics & Mathematics (AREA)
  • Health & Medical Sciences (AREA)
  • Surgery (AREA)
  • Optics & Photonics (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Engineering & Computer Science (AREA)
  • Molecular Biology (AREA)
  • Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
  • Electromagnetism (AREA)
  • Biomedical Technology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Medical Informatics (AREA)
  • Otolaryngology (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • General Physics & Mathematics (AREA)
  • Laser Surgery Devices (AREA)

Abstract

Cette invention concerne une sonde en fibre optique vectrice d'un laser servant, en endoscopie, à acheminer le rayon émis par un laser vers une cible donnée. Cette sonde se compose d'un faisceau de fibre optique qui reçoit le rayon laser émis par une source, et qui permet de diriger par son extrémité distale ledit rayon (14) vers la cible. Le faisceau de fibre optique se compose d'un coeur (8) dont la surface à son extrémité (13) est polie de façon à ce que le rayon laser voyageant dans ledit faisceau puisse être réfléchi, par réflexion interne, par l'extrémité de la sonde et sous forme d'un rayon divergent dirigé vers l'avant (14). L'extrémité distale du faisceau de fibre optique est recouverte de verre de silice ou d'un fourreau en verre de silice synthétique (11), lequel laisse passer le rayon laser et peut résister aux hautes températures pendant l'utilisation. Ce fourreau permet d'éviter que la sonde soit détruite, lors de son utilisation, par les hautes températures que l'on observe souvent lors d'applications endoscopiques. Cette sonde pourra tout particulièrement être utilisée dans le traitement de l'hyperplasie bénigne de la prostate.
PCT/GB1995/002920 1994-12-14 1995-12-14 Sonde en fibre optique vectrice d'un laser et son utilisation Ceased WO1996018347A1 (fr)

Priority Applications (1)

Application Number Priority Date Filing Date Title
AU41845/96A AU4184596A (en) 1994-12-14 1995-12-14 Optical fibre laser delivery probe and use thereof

Applications Claiming Priority (4)

Application Number Priority Date Filing Date Title
GBGB9425216.0A GB9425216D0 (en) 1994-12-14 1994-12-14 Optical fibre laser delivery probe and use thereof
GB9425216.0 1994-12-14
GBGB9514872.2A GB9514872D0 (en) 1994-12-14 1995-07-20 Optical fibre laser delivery probe and use thereof
GB9514872.2 1995-07-20

Publications (1)

Publication Number Publication Date
WO1996018347A1 true WO1996018347A1 (fr) 1996-06-20

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PCT/GB1995/002920 Ceased WO1996018347A1 (fr) 1994-12-14 1995-12-14 Sonde en fibre optique vectrice d'un laser et son utilisation

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AU (1) AU4184596A (fr)
GB (1) GB9514872D0 (fr)
WO (1) WO1996018347A1 (fr)

Cited By (11)

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WO2008092823A1 (fr) * 2007-01-31 2008-08-07 Universita' Degli Studi Di Pavia Procédé et dispositif optique de manipulation de particule
FR2913192A1 (fr) * 2007-03-02 2008-09-05 Optical System Res For Industr Ensemble canule/fibre optique et instrument laser comportant ledit ensemble.
EP2254495A1 (fr) 2008-02-28 2010-12-01 CeramOptec GmbH Dispositif d'ablation laser endoluminal et procédé de traitement de veines
EP2263749A3 (fr) * 1998-03-27 2012-09-26 The General Hospital Corporation Procédé et appareil pour le ciblage sélectif des tissus riches en lipides
US8915948B2 (en) 2002-06-19 2014-12-23 Palomar Medical Technologies, Llc Method and apparatus for photothermal treatment of tissue at depth
US9028536B2 (en) 2006-08-02 2015-05-12 Cynosure, Inc. Picosecond laser apparatus and methods for its operation and use
US9780518B2 (en) 2012-04-18 2017-10-03 Cynosure, Inc. Picosecond laser apparatus and methods for treating target tissues with same
CN109513115A (zh) * 2018-12-06 2019-03-26 华南师范大学 一种基于带隙微结构光纤的柔性定点光疗系统
US10245107B2 (en) 2013-03-15 2019-04-02 Cynosure, Inc. Picosecond optical radiation systems and methods of use
US10434324B2 (en) 2005-04-22 2019-10-08 Cynosure, Llc Methods and systems for laser treatment using non-uniform output beam
US11418000B2 (en) 2018-02-26 2022-08-16 Cynosure, Llc Q-switched cavity dumped sub-nanosecond laser

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WO1990005562A1 (fr) * 1988-11-16 1990-05-31 Medilase, Incorporated Catheter d'angioplastie avec fibre a axes decales d'apport d'un rayon laser suivant un angle
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US5242438A (en) * 1991-04-22 1993-09-07 Trimedyne, Inc. Method and apparatus for treating a body site with laterally directed laser radiation
US5343543A (en) * 1993-05-27 1994-08-30 Heraeus Surgical, Inc. Side-firing laser fiber with directional indicator and methods of use in determining the orientation of radiation to be emitted from the side-firing laser fiber
DE9410452U1 (de) * 1993-08-03 1994-09-08 Göbel, Dieter, Dr., 80333 München Lasereinrichtung

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