CA2360241A1 - Optical apparatus - Google Patents
Optical apparatus Download PDFInfo
- Publication number
- CA2360241A1 CA2360241A1 CA002360241A CA2360241A CA2360241A1 CA 2360241 A1 CA2360241 A1 CA 2360241A1 CA 002360241 A CA002360241 A CA 002360241A CA 2360241 A CA2360241 A CA 2360241A CA 2360241 A1 CA2360241 A1 CA 2360241A1
- Authority
- CA
- Canada
- Prior art keywords
- optical element
- handpiece
- diffractive optical
- light
- tissues
- 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
- 230000003287 optical effect Effects 0.000 title claims abstract description 35
- 239000013307 optical fiber Substances 0.000 claims abstract description 17
- 239000003106 tissue adhesive Substances 0.000 claims abstract description 9
- 239000000853 adhesive Substances 0.000 claims description 12
- 230000001070 adhesive effect Effects 0.000 claims description 12
- 238000000034 method Methods 0.000 claims description 4
- 230000004913 activation Effects 0.000 abstract 1
- VYPSYNLAJGMNEJ-UHFFFAOYSA-N Silicium dioxide Chemical compound O=[Si]=O VYPSYNLAJGMNEJ-UHFFFAOYSA-N 0.000 description 4
- 239000000463 material Substances 0.000 description 4
- 239000011358 absorbing material Substances 0.000 description 2
- 239000004033 plastic Substances 0.000 description 2
- 229920003023 plastic Polymers 0.000 description 2
- 239000000377 silicon dioxide Substances 0.000 description 2
- 241001527902 Aratus Species 0.000 description 1
- 238000000862 absorption spectrum Methods 0.000 description 1
- 230000004075 alteration Effects 0.000 description 1
- 239000003086 colorant Substances 0.000 description 1
- 239000002537 cosmetic Substances 0.000 description 1
- 239000005548 dental material Substances 0.000 description 1
- 230000000694 effects Effects 0.000 description 1
- 238000001839 endoscopy Methods 0.000 description 1
- 239000000835 fiber Substances 0.000 description 1
- 238000001914 filtration Methods 0.000 description 1
- 239000003365 glass fiber Substances 0.000 description 1
- 238000010438 heat treatment Methods 0.000 description 1
- 238000005286 illumination Methods 0.000 description 1
- 238000001727 in vivo Methods 0.000 description 1
- 238000004519 manufacturing process Methods 0.000 description 1
- 238000000386 microscopy Methods 0.000 description 1
- 238000002324 minimally invasive surgery Methods 0.000 description 1
- 238000002428 photodynamic therapy Methods 0.000 description 1
- 229920002120 photoresistant polymer Polymers 0.000 description 1
- 238000006116 polymerization reaction Methods 0.000 description 1
- 230000001681 protective effect Effects 0.000 description 1
- 239000012460 protein solution Substances 0.000 description 1
- 102000004169 proteins and genes Human genes 0.000 description 1
- 108090000623 proteins and genes Proteins 0.000 description 1
- 230000005855 radiation Effects 0.000 description 1
- 239000000565 sealant Substances 0.000 description 1
- 239000004065 semiconductor Substances 0.000 description 1
- 238000004611 spectroscopical analysis Methods 0.000 description 1
- 239000000758 substrate Substances 0.000 description 1
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
-
- 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
- G02B6/241—Light guide terminations
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods
- A61B17/00491—Surgical glue applicators
- A61B2017/00513—Tissue soldering
- A61B2017/00517—Tissue soldering using laser
-
- 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
- A61B2018/1807—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 light other than laser radiation
-
- 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
- A61B2018/2266—Optical elements at the distal end of probe tips with a lens, e.g. ball tipped
-
- 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
Landscapes
- Physics & Mathematics (AREA)
- Health & Medical Sciences (AREA)
- Surgery (AREA)
- Life Sciences & Earth Sciences (AREA)
- Optics & Photonics (AREA)
- Biomedical Technology (AREA)
- Veterinary Medicine (AREA)
- Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
- Electromagnetism (AREA)
- Engineering & Computer Science (AREA)
- Otolaryngology (AREA)
- Heart & Thoracic Surgery (AREA)
- Medical Informatics (AREA)
- Molecular Biology (AREA)
- Animal Behavior & Ethology (AREA)
- General Health & Medical Sciences (AREA)
- Public Health (AREA)
- General Physics & Mathematics (AREA)
- Laser Surgery Devices (AREA)
- Radiation-Therapy Devices (AREA)
- Dental Tools And Instruments Or Auxiliary Dental Instruments (AREA)
- Lenses (AREA)
Abstract
Apparatus for the projection of a light beam onto a target comprises a light source (10) such as a laser or an arc lamp, a light guide such as an optical fibre (12) and focusing means (20). The focusing means (20) is at the output end of the light guide (12) and includes a diffractive optical element (24).
The apparatus is particularly useful in the activation of tissue adhesive.
The apparatus is particularly useful in the activation of tissue adhesive.
Description
Title - O h~l Ap aratus This invention relates to an optical apparatus, in particular to apparatus for use in the projection of a light beam onto a target. An important application of such apparatus is for directing light from an intense light source onto a photo-activatable tissue adhesive with sufficient intensity to bring about polymerization of the adhesive.
Sealants and adhesives for the in vivo bonding of living tissues are known.
Typically such adhesives comprise protein solutions which are cross-linked by heating. Heat energy can be transferred to the proteins by incorporating into the adhesive a photon-absorbing material and exposing the adhesive to light of sufficiently high intensity. The amount of energy required to reach temperatures high enough for curing of the adhesive to occur necessitates the supply of a large number of photons of radiation within the absorption spectrum of the photon-absorbing material. It is also generally the case that the light beam which is used in such application be of very small dimensions.
In a typical set up for the curing of a tissue adhesive, an intense light source such as a laser is used to generate a beam of light which is carried along a flexible optical fibre. The end of the optical fibre is fitted with a handpiece which is used to focus the output light beam onto the target tissue. In use, the handpiece is held by the surgeon and manipulated such that the light beam is directed at the tissue to which adhesive has been applied, operation of the apparatus typically being controlled by means of a foot pedal or the like. The light beam is 2 0 typically focused by lenses in the handpiece at a point a few centimetres from the end of the handpiece.
A disadvantage of known arrangements of the type described above is that it may be difficult for the surgeon to maintain the handpiece in such a position that the target tissue is precisely at the focal point of the output beam. As a result the intensity of the irradiation at the target 2 5 may be less than desired. In addition, the light beam will normally be focused into a circular spot, which may not be the most appropriate form of illumination for the target.
There has now been devised apparatus for the projection of a light beam onto a target which overcomes or substantially mitigates the above-mentioned disadvantages.
According to the invention, apparatus for the projection of a light beam onto a target comprises a light source, light guide means adapted to conduct light from the light source to the vicinity of the target, and focusing means at an output end of said light guide means, said focusing means including a diffractive optical element.
The apparatus according to the invention is advantageous primarily in that the use of a diffractive optical element allows the output light beam to be focused into a spot (or, indeed, two or more spots) of any desired shape and size. In addition, by appropriate design of the diffractive optical element, it may be possible to focus the light beam over a range of distances, allowing greater tolerance in the positioning of the light beam with respect to a target.
For many applications, the focusing means is preferably housed within a hand-piece which is of such a size and shape that it can be readily manipulated by a user. Such a handpiece may typically be cylindrical, with a length of, say, 1 Scm and a diameter of the order of 2cm.
In some cases, however such a handpiece may not be necessary, the focusing means including the diffractive optical element being applied directly to the end of the light guide means.
Preferably, the diffractive optical element is used in conjunction with a refractive optical element, ie a lens. In such an arrangement the diffractive optical element is preferably 2 0 provided on one face of the lens. In a particularly preferred arrangement, the diffractive optical element is applied to the planar face of a piano-convex lens.
The diffractive optical element may be fabricated by methods known er se for the manufacture of such components. Most preferably, the diffractive optical element is made of silica, though other materials may be used, including plastics materials.
The diffractive 2 5 optical element most preferably comprises an array of discrete cells, eg a square array, the properties of the element being determined by the relative thicknesses of the cells. Where the light source is monochromatic the diffractive optical element may have a relatively simple structure comprising cells each with one of a small number of discrete thicknesses. Where the light beam is polychromatic the structure may be more complex, the thicknesses of the individual cells being quantised into a larger number of discrete values, eg sixteen discrete thicknesses, for instance in order to correct chromatic aberrations.
Any suitable light source may be used, provided that light of sufficient intensity is generated for the application for which the apparatus is to be used. The light source may be a laser light source, or may be a polychromatic light source, eg an arc lamp.
The light guide means most preferably comprises an optical fibre, which may in general be of conventional form. For many applications, the optical fibre will have a length of from about one to three metres. In order to maximise energy input into the optical fibre it preferably has a relatively high numerical aperture NA=sin0, where O is the semi-angle of the acceptance cone at the end plate of the optical fibre. Preferably, the numerical aperture is greater than 0.49. Such a numerical aperture can be attained with a glass fibre. A single fibre may be used, or a bundle of fibres. The optical fibre, or bundle of fibres, is most preferably contained within a protective sheath, which is most commonly of plastics material.
For many applications, it is desirable that the light guide means be flexible.
Although described herein principally in connection with the curing of tissue adhesive, the apparatus according to the invention may be used in a variety of other applications. Other 2 0 medical applications include endoscopy and other applications in which lasers or other intense light sources are conventionally used, such as biostimulation, photodynamic therapy, curing of dental materials, cosmetic methods of tattoo or hair removal, and minimally invasive surgery. Other applications include curing of materials such as semiconductor photoresists and industrial adhesives, and research applications in photochemistry, 2 5 spectroscopy and microscopy.
The invention will now be described in greater detail, by way of example only, with reference to the drawings, in which Figure 1 is a schematic view of apparatus in accordance with the invention, for the curing of photo-activatable tissue adhesive;
Figure 2 is a sectional view on a larger scale of a handpiece forming part of the apparatus of Figure 1;
Figure 3 is a schematic representation of the face of a diffractive optical element used in the handpiece of Figure 2;
Figure 4 is a schematic cross-sectional view (not to scale) of the diffractive optical element of Figure 3;
Figure 5 is a simulated view of the face of the diffractive optical element, the depths of the individual cells making up the element being represented on a grey scale, the darker colours representing greater thicknesses.
Refernng first to Figure 1, apparatus for delivering an intense light beam to a site at which two living tissues are to be bonded together comprises generally a light source unit 10, an optical fibre tube 12 and a hand-piece 14. The apparatus is used to direct light of sufficient intensity onto tissue adhesive applied to the junction of two living tissues.
The light source unit 10 includes an intense light source, which may be a laser light source or a polychromatic light source. In the latter case, appropriate filtering means will generally be provided to limit the light which is transmitted by the optical fibre tube 12 to a particular bandwidth. Appropriate optical components will also be provided to direct the light beam 2 0 onto the end plate of an optical fibre which is housed within the optical fibre tube 12. The light beam is transmitted along the optical fibre to the handpiece 14 by which it is focused in the manner described below. In use, a surgeon applies adhesive to tissues which are to be bonded, and brings those tissues into contact. Holding the handpiece 14, the surgeon then uses it to apply light to the adhesive. For ease of use, a foot pedal may be provided by which 2 5 the surgeon can increase the light output to full power. Application of high intensity light is continued for sufficient time to effect curing of the adhesive.
Figure 2 is a schematic sectional view of the handpiece 14. The optical fibre tube 12 terminates within the handpiece 14, l5mm from a hybrid optical element 20. The optical element 20 consists of a refractive plano-convex lens 22, the plane face of which is bonded to a diffractive optical element 24. The lens 22 has a focal length of l5mm, a thickness of 3.8mm, and an effective aperture of lOmm. The diffractive optical element 24 (shown schematically in more detail in Figures 3 and 4) has an effective aperture of approximately 7.Smm and comprises an array of square cells (see Figure 3) which are built up on a silica substrate approximately lmm in thickness. In reality, the array comprises 1024x1024 cells, for clarity a much smaller number being depicted in Figure 3. Each cell is 7.S~m square and has a thickness chosen such that the overall diffractive optical element 24 focuses the light beam in the desired manner. Figure 4 shows a typical cross-section (in arbitrary units and not to scale) of one vertical row of cells (the actual number of discrete thicknesses shown corresponding to the number of cells shown in Figure 3 and not to the actual number of 1024).
Figure 5 is a pictorial representation of the face of the diffractive optical element 24, in which each cell is shown with one of sixteen thickness levels, the greater thicknesses being represented by the darker tones on the grey scale shown at the right of the Figure.
The form of the diffractive optical element 24 may be such as simply to focus the light beam 2 0 to a spot at a fixed distance from the diffractive optical element 24.
Such a distance may be typically 100mm. Other forms of diffractive optical element may confer on the spot a particular shape, eg the spot may be rectangular. Still other forms of diffractive optical element may be used to provide a focal range, rather than a single focal length, thereby providing greater tolerance in the positioning of the handpiece 14 relative to the target 2 5 tissues.
Sealants and adhesives for the in vivo bonding of living tissues are known.
Typically such adhesives comprise protein solutions which are cross-linked by heating. Heat energy can be transferred to the proteins by incorporating into the adhesive a photon-absorbing material and exposing the adhesive to light of sufficiently high intensity. The amount of energy required to reach temperatures high enough for curing of the adhesive to occur necessitates the supply of a large number of photons of radiation within the absorption spectrum of the photon-absorbing material. It is also generally the case that the light beam which is used in such application be of very small dimensions.
In a typical set up for the curing of a tissue adhesive, an intense light source such as a laser is used to generate a beam of light which is carried along a flexible optical fibre. The end of the optical fibre is fitted with a handpiece which is used to focus the output light beam onto the target tissue. In use, the handpiece is held by the surgeon and manipulated such that the light beam is directed at the tissue to which adhesive has been applied, operation of the apparatus typically being controlled by means of a foot pedal or the like. The light beam is 2 0 typically focused by lenses in the handpiece at a point a few centimetres from the end of the handpiece.
A disadvantage of known arrangements of the type described above is that it may be difficult for the surgeon to maintain the handpiece in such a position that the target tissue is precisely at the focal point of the output beam. As a result the intensity of the irradiation at the target 2 5 may be less than desired. In addition, the light beam will normally be focused into a circular spot, which may not be the most appropriate form of illumination for the target.
There has now been devised apparatus for the projection of a light beam onto a target which overcomes or substantially mitigates the above-mentioned disadvantages.
According to the invention, apparatus for the projection of a light beam onto a target comprises a light source, light guide means adapted to conduct light from the light source to the vicinity of the target, and focusing means at an output end of said light guide means, said focusing means including a diffractive optical element.
The apparatus according to the invention is advantageous primarily in that the use of a diffractive optical element allows the output light beam to be focused into a spot (or, indeed, two or more spots) of any desired shape and size. In addition, by appropriate design of the diffractive optical element, it may be possible to focus the light beam over a range of distances, allowing greater tolerance in the positioning of the light beam with respect to a target.
For many applications, the focusing means is preferably housed within a hand-piece which is of such a size and shape that it can be readily manipulated by a user. Such a handpiece may typically be cylindrical, with a length of, say, 1 Scm and a diameter of the order of 2cm.
In some cases, however such a handpiece may not be necessary, the focusing means including the diffractive optical element being applied directly to the end of the light guide means.
Preferably, the diffractive optical element is used in conjunction with a refractive optical element, ie a lens. In such an arrangement the diffractive optical element is preferably 2 0 provided on one face of the lens. In a particularly preferred arrangement, the diffractive optical element is applied to the planar face of a piano-convex lens.
The diffractive optical element may be fabricated by methods known er se for the manufacture of such components. Most preferably, the diffractive optical element is made of silica, though other materials may be used, including plastics materials.
The diffractive 2 5 optical element most preferably comprises an array of discrete cells, eg a square array, the properties of the element being determined by the relative thicknesses of the cells. Where the light source is monochromatic the diffractive optical element may have a relatively simple structure comprising cells each with one of a small number of discrete thicknesses. Where the light beam is polychromatic the structure may be more complex, the thicknesses of the individual cells being quantised into a larger number of discrete values, eg sixteen discrete thicknesses, for instance in order to correct chromatic aberrations.
Any suitable light source may be used, provided that light of sufficient intensity is generated for the application for which the apparatus is to be used. The light source may be a laser light source, or may be a polychromatic light source, eg an arc lamp.
The light guide means most preferably comprises an optical fibre, which may in general be of conventional form. For many applications, the optical fibre will have a length of from about one to three metres. In order to maximise energy input into the optical fibre it preferably has a relatively high numerical aperture NA=sin0, where O is the semi-angle of the acceptance cone at the end plate of the optical fibre. Preferably, the numerical aperture is greater than 0.49. Such a numerical aperture can be attained with a glass fibre. A single fibre may be used, or a bundle of fibres. The optical fibre, or bundle of fibres, is most preferably contained within a protective sheath, which is most commonly of plastics material.
For many applications, it is desirable that the light guide means be flexible.
Although described herein principally in connection with the curing of tissue adhesive, the apparatus according to the invention may be used in a variety of other applications. Other 2 0 medical applications include endoscopy and other applications in which lasers or other intense light sources are conventionally used, such as biostimulation, photodynamic therapy, curing of dental materials, cosmetic methods of tattoo or hair removal, and minimally invasive surgery. Other applications include curing of materials such as semiconductor photoresists and industrial adhesives, and research applications in photochemistry, 2 5 spectroscopy and microscopy.
The invention will now be described in greater detail, by way of example only, with reference to the drawings, in which Figure 1 is a schematic view of apparatus in accordance with the invention, for the curing of photo-activatable tissue adhesive;
Figure 2 is a sectional view on a larger scale of a handpiece forming part of the apparatus of Figure 1;
Figure 3 is a schematic representation of the face of a diffractive optical element used in the handpiece of Figure 2;
Figure 4 is a schematic cross-sectional view (not to scale) of the diffractive optical element of Figure 3;
Figure 5 is a simulated view of the face of the diffractive optical element, the depths of the individual cells making up the element being represented on a grey scale, the darker colours representing greater thicknesses.
Refernng first to Figure 1, apparatus for delivering an intense light beam to a site at which two living tissues are to be bonded together comprises generally a light source unit 10, an optical fibre tube 12 and a hand-piece 14. The apparatus is used to direct light of sufficient intensity onto tissue adhesive applied to the junction of two living tissues.
The light source unit 10 includes an intense light source, which may be a laser light source or a polychromatic light source. In the latter case, appropriate filtering means will generally be provided to limit the light which is transmitted by the optical fibre tube 12 to a particular bandwidth. Appropriate optical components will also be provided to direct the light beam 2 0 onto the end plate of an optical fibre which is housed within the optical fibre tube 12. The light beam is transmitted along the optical fibre to the handpiece 14 by which it is focused in the manner described below. In use, a surgeon applies adhesive to tissues which are to be bonded, and brings those tissues into contact. Holding the handpiece 14, the surgeon then uses it to apply light to the adhesive. For ease of use, a foot pedal may be provided by which 2 5 the surgeon can increase the light output to full power. Application of high intensity light is continued for sufficient time to effect curing of the adhesive.
Figure 2 is a schematic sectional view of the handpiece 14. The optical fibre tube 12 terminates within the handpiece 14, l5mm from a hybrid optical element 20. The optical element 20 consists of a refractive plano-convex lens 22, the plane face of which is bonded to a diffractive optical element 24. The lens 22 has a focal length of l5mm, a thickness of 3.8mm, and an effective aperture of lOmm. The diffractive optical element 24 (shown schematically in more detail in Figures 3 and 4) has an effective aperture of approximately 7.Smm and comprises an array of square cells (see Figure 3) which are built up on a silica substrate approximately lmm in thickness. In reality, the array comprises 1024x1024 cells, for clarity a much smaller number being depicted in Figure 3. Each cell is 7.S~m square and has a thickness chosen such that the overall diffractive optical element 24 focuses the light beam in the desired manner. Figure 4 shows a typical cross-section (in arbitrary units and not to scale) of one vertical row of cells (the actual number of discrete thicknesses shown corresponding to the number of cells shown in Figure 3 and not to the actual number of 1024).
Figure 5 is a pictorial representation of the face of the diffractive optical element 24, in which each cell is shown with one of sixteen thickness levels, the greater thicknesses being represented by the darker tones on the grey scale shown at the right of the Figure.
The form of the diffractive optical element 24 may be such as simply to focus the light beam 2 0 to a spot at a fixed distance from the diffractive optical element 24.
Such a distance may be typically 100mm. Other forms of diffractive optical element may confer on the spot a particular shape, eg the spot may be rectangular. Still other forms of diffractive optical element may be used to provide a focal range, rather than a single focal length, thereby providing greater tolerance in the positioning of the handpiece 14 relative to the target 2 5 tissues.
Claims (11)
1. Apparatus for use in the bonding together of living tissues by the curing of photo-activatable tissue adhesive applied to at least one of said tissues, said apparatus comprising a light source, light guide means adapted to conduct light from the light source to the vicinity of the tissues, and a handpiece at an output end of said light guide means, said handpiece being of such a size and shape as to be readily manipulated by a user, and said handpiece including focusing means including a diffracted optical element, the focusing means causing light output from the handpiece to be focused onto the tissue adhesive.
2. Apparatus as claimed in Claim 1, wherein the handpiece is cylindrical.
3. Apparatus as claimed in Claim 1 or Claim 2, wherein the focusing means including the diffractive optical element is applied directly to the end of the light guide means.
4. Apparatus as claimed in any preceding claim, wherein the diffractive optical element is used in conjunction with a lens.
5. Apparatus as claimed in Claim 4, wherein the diffractive optical element is provided on one face of the lens.
6. Apparatus as claimed in Claim 5, wherein the diffractive optical element is applied to the planar face of a piano-convex lens.
7. Apparatus as claimed in any preceding claim, wherein the diffractive optical element comprises an array of discrete cells, the properties of the element being determined by the relative thicknesses of the cells.
8. Apparatus as claimed in any preceding claim, wherein the light guide means comprises an optical fibre.
9. Apparatus as claimed in Claim 8, wherein the optical fibre has a length of from about one to three metres.
10. Apparatus as claimed in Claim 8 or Claim 9, wherein the optical fibre has a numerical aperture greater than 0.49.
11. A method for the bonding together of living tissues, which method comprises applying a photo-activatable tissue adhesive to at least one of the tissues to be bonded, bringing said tissues into contact, and projecting light onto the adhesive using apparatus according to any preceding claim.
Applications Claiming Priority (3)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| GB9903185.8 | 1999-02-13 | ||
| GBGB9903185.8A GB9903185D0 (en) | 1999-02-13 | 1999-02-13 | Optical apparatus |
| PCT/GB2000/000400 WO2000047125A1 (en) | 1999-02-13 | 2000-02-10 | Optical apparatus |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CA2360241A1 true CA2360241A1 (en) | 2000-08-17 |
Family
ID=10847627
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA002360241A Abandoned CA2360241A1 (en) | 1999-02-13 | 2000-02-10 | Optical apparatus |
Country Status (6)
| Country | Link |
|---|---|
| EP (1) | EP1161193A1 (en) |
| JP (1) | JP2002536108A (en) |
| AU (1) | AU2448400A (en) |
| CA (1) | CA2360241A1 (en) |
| GB (1) | GB9903185D0 (en) |
| WO (1) | WO2000047125A1 (en) |
Families Citing this family (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JP4660024B2 (en) | 2001-06-26 | 2011-03-30 | 帝人株式会社 | MMP activity lowering apparatus and method |
Family Cites Families (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| IT1220172B (en) * | 1987-07-17 | 1990-06-06 | Il Consiglio Nazionale Delle R | FIBER OPTIC DEVICE FOR THE TRANSMISSION AND LATERAL IRRADIATION OF LASER ENERGY, PARTICULARLY FOR ANGIOPLASTIC TREATMENTS |
| EP0441040A3 (en) * | 1990-01-30 | 1991-11-27 | C.R. Bard, Inc. | Laser catheter having diffraction grating for beam shaping |
| US5431647A (en) * | 1994-07-13 | 1995-07-11 | Pioneer Optics Company | Fiberoptic cylindrical diffuser |
-
1999
- 1999-02-13 GB GBGB9903185.8A patent/GB9903185D0/en not_active Ceased
-
2000
- 2000-02-10 AU AU24484/00A patent/AU2448400A/en not_active Abandoned
- 2000-02-10 JP JP2000598079A patent/JP2002536108A/en active Pending
- 2000-02-10 EP EP00902742A patent/EP1161193A1/en not_active Withdrawn
- 2000-02-10 WO PCT/GB2000/000400 patent/WO2000047125A1/en not_active Ceased
- 2000-02-10 CA CA002360241A patent/CA2360241A1/en not_active Abandoned
Also Published As
| Publication number | Publication date |
|---|---|
| EP1161193A1 (en) | 2001-12-12 |
| AU2448400A (en) | 2000-08-29 |
| JP2002536108A (en) | 2002-10-29 |
| GB9903185D0 (en) | 1999-04-07 |
| WO2000047125A1 (en) | 2000-08-17 |
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