WO1995015060A1 - Systeme d'eclairage a diodes electroluminescentes pour cameras d'endoscopes - Google Patents

Systeme d'eclairage a diodes electroluminescentes pour cameras d'endoscopes Download PDF

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Publication number
WO1995015060A1
WO1995015060A1 PCT/US1994/013476 US9413476W WO9515060A1 WO 1995015060 A1 WO1995015060 A1 WO 1995015060A1 US 9413476 W US9413476 W US 9413476W WO 9515060 A1 WO9515060 A1 WO 9515060A1
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WO
WIPO (PCT)
Prior art keywords
illumination
led
primary color
light
endoscope
Prior art date
Application number
PCT/US1994/013476
Other languages
English (en)
Inventor
John I. Shipp
Original Assignee
Apollo Camera, L.L.C.
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
Application filed by Apollo Camera, L.L.C. filed Critical Apollo Camera, L.L.C.
Priority to AU12927/95A priority Critical patent/AU694466B2/en
Priority to EP95904110A priority patent/EP0734629A1/fr
Publication of WO1995015060A1 publication Critical patent/WO1995015060A1/fr

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Classifications

    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04N—PICTORIAL COMMUNICATION, e.g. TELEVISION
    • H04N7/00—Television systems
    • H04N7/18—Closed-circuit television [CCTV] systems, i.e. systems in which the video signal is not broadcast
    • H04N7/183—Closed-circuit television [CCTV] systems, i.e. systems in which the video signal is not broadcast for receiving images from a single remote source
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B1/00—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor
    • A61B1/06—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor with illuminating arrangements
    • A61B1/0661—Endoscope light sources
    • A61B1/0684—Endoscope light sources using light emitting diodes [LED]

Definitions

  • the present invention relates generally to light sources used to iUuminate body cavities during laparascopic surgery, and more particularly to a light assembly mounted in the distal end of an endoscope which emits white light, or red, blue, and green light within the body cavity during surgery.
  • An insufflated abdominal cavity for example, has a volume of several liters, with the distance from the peritoneum to the liver bed ranging from 5 to 12 centimeters, depending upon the size and obesity of the patient.
  • the geometry of the cavity is such that an angular field of view of between 50 to 80 degrees is desired for observation and illumination.
  • Typical laparascopic surgical procedures necessitate endoscope-to-object distances of 1.5 to 15 centimeters.
  • Several illumination techniques are employed in the prior art.
  • a Xenon light source is typically focused onto one end of a flexible fiber optics cable.
  • the other end of the cable is attached to a 90 degree coupling attached to an endoscope, the periphery of which comprises an annular fiber optics bundle terminating at the distal end of the endoscope.
  • Light is emitted from the annular (donut shaped) fiber bundle into the body cavity where a portion of it is reflected and captured by the objective lens of the endoscope and relayed through the center of the scope to the CCD detector array.
  • the white light thus must be separated, after the illumination step, into three primary components, usually red, green, and blue, before it can be processed into a color image by a non-sequential color CCD camera.
  • Field sequential cameras utilize light sources which usually are separated into three primary colors prior to illumination of the object.
  • Prior art sequential cameras such as that described in U.S. Patent 4,631,582 for example, utilize rotating segmented color filters in the path of white light sources, or color filters in the path of sequentially illuminated white strobe lights.
  • the fiber optics cable used in prior art illumination devices comes into contact with the sterile zone in the operating room and thus must be re-sterilized before each use.
  • the sterilization process often causes catastrophic damage to, or degrades, the cable.
  • the present invention solves these and other problems characteristic of prior art laparascopic illumination systems.
  • An object of the present invention is to provide a system for illuminating body cavities during laparascopic surgery which is optically and energy efficient and which provides the desired angular dispersion of illuminating light. Another object of the present invention is to eliminate the light-loss, size, and sterilization problems inherent in the use of fiber-optic cables and bundles. Yet another object of the present invention is to adapt an illumination system for use with a field sequential single sensor video camera or with a sequential chrominance- luminance YC camera system.
  • the present invention comprises an efficient, compact, light source mounted in the distal end of an endoscope, usable with a field sequential single sensor video imaging system such as that described in co-pending U.S. Patent application serial no. 905,278.
  • a series of four red, fourteen green, and ten blue light emitting diodes (LED's) are mounted and arranged on a ceramic substrate in a circular pattern concentrically around the optical path of the endoscope.
  • a reflector.cup surrounds each LED to help control the angular distribution of the emitted light.
  • the LED's are electrically wired to an illumination circuit which; causes them to emit red, blue, and green light in synchronization with the field period of a CCD endoscopic camera. Because the LED's are mounted in the distal end of the endoscope, the typical prior art light loss through fiber optics cables and connections is avoided and the need for cable sterilization is eliminated.
  • the LED arrangement uniformly illuminates objects within body cavities with the required angular dispersion. The efficiency of the light source allows for battery operation of the camera and lights making the system much more portable.
  • Fig. 1 is an oblique view of a first embodiment of the present invention in which the illumination means is a distally mounted LED assembly.
  • Fig. 2 is a schematic plan view of the LED assembly of Fig. 1, showing the approximate layout of the 28 LED's and power connection points on the substrate.
  • Fig. 3 is an enlarged view of a red LED chip as used in the present invention, showing its wired connections to the substrate of the illumination means.
  • Fig. 4 is an enlarged view of a green or blue LED chip as used in the present invention, showing its wired connections to the substrate of the illumination means.
  • Fig. 5 is an electrical schematic diagram of the LED assembly.
  • Fig. 6a is top view of the reflector cup used in conjunction with each of the LED's of the present invention.
  • Fig. 6b is a side view of the reflector cup of Fig. 6a.
  • Fig. 6c is a cutaway side view of the reflector cup of Fig.'s 6a and 6b.
  • Fig. 7 is a side view of a single LED chip or die mounted within a reflector cup, further showing the angles of light emitted from and reflected therein.
  • Fig. 8 is a cross-sectional side view of the distal end of the endoscope to which the present invention is mounted.
  • Fig. 9 is an electrical schematic of a circuit used for white balancing of the three colors emitted by the illumination system of the present invention.
  • Fig.'s 10a and b are plan and cutaway side views of a second embodiment of the LED assembly of the present invention in which the reflector cups are formed integral to the substrate.
  • Fig.'s 11a and b are plan and cutaway side views of the illumination means of Fig. 10a, after the LED wiring pads have been etched and gold flashed.
  • Fig.'s 12a and b are plan and cutaway side views of the illumination means of Fig. 11a, after mounting of the LED dies to the reflector cups.
  • Fig.'s 13a and b are plan and cutaway side views of the illumination means of Fig. 12, after wiring bonding of the anodes or cathodes of the LED's to the wiring pads.
  • Fig. 14 is a block diagram of a single sensor sequential video imaging system used in conjunction with the illumination system of the present invention.
  • Fig. 15 is a side view of second embodiment of the illumination system in which an LED assembly is mounted in the camera head, with light transmitted to the distal end of the endoscope via optical fibers or plexiglass.
  • Fig. 16 is a cutaway side view of a third embodiment of the illumination means in which an LED assembly is combined with a white light source at the distal end of the endoscope.
  • an illumination means 10 here an LED assembly
  • an illumination means 10 is adapted for mounting at the distal end of a 10 mm outside diameter endoscope 15, which is the typical size used in abdominal laparascopic procedures.
  • this first embodiment of illumination means 10 incorporates inner and outer rings of 28 individual LED chips or dies 22 mounted to separate reflector cups 21 which are then mechanically bonded to a base plate, which in this embodiment is an annular ceramic substrate 20.
  • a cylindrical aperture 24 passes through the center of substrate 20.
  • aperture 24 will have a diameter larger than the entrance pupil (not shown) of a conventional endoscope objective lens system 52 and slightly less than stepped down section 54 of lens system 52.
  • lens system 52 will have a 6 mm diameter and with an entrance pupil of approximately 3 mm diameter.
  • Aperture 24 allows light reflected from the object being viewed to pass through assembly 10 to lens system 52 unhindered.
  • the outside diameter of substrate 20, typically 9 mm, is sized and configured to mate with the inside diameter of a stainless steel sheath 53 of endoscope 15 that houses illumination means 10 and objective lens system 52.
  • An inner sleeve 51 preferably made of copper, lines the inner surface of sheath 53 and at its distal end, turns inward to form a base portion 56 to contact the proximal surface of substrate 20.
  • Sleeve 51 acts as a heat sink for illumination means 10.
  • a light coating of zinc oxide is applied to the proximal surface of substrate 20.
  • a translucent protective window 50 is mounted distally of illumination means 10.
  • the LED assembly illumination means 10 as described herein has an efficiency of approximately 1.2 per cent (light power output divided by electrical power input).
  • Inner sleeve 51 thermally contacts stainless steel sheath 53 so that a very small temperature drop occurs from the outside surface of sleeve 51 to the outer surface sheath 53, thus allowing maximum radiated and convective heat dissipation from the stainless steel.
  • the average temperature rise of endoscope 15 is held to 20 degrees centi ⁇ grade for a thermal load of 3.5 watts.
  • the average temperature rise for an all stainless steel construction exceeds 50 degrees centigrade and the distal tip temperature exceeds 90 degrees centigrade for an ambient temperature of 20 degrees centigrade.
  • LED illumination means 10 is fabricated by first depositing in a conventional manner the metal required for interconnecting land and lead bond pad patterns onto the 0.5 mm thick, high purity alumina substrate 20. Next, reflector cups 21 are soldered to substrate 20. The LED die 22 are bonded in place to reflector cups 21 with a conductive epoxy, cathode 42 down for blue die 32 and green die 31 as shown on Fig. 4, and with anode 41 down for red die 30, as shown in Fig. 3. For red die 30, cathodes 42 are then lead bonded to their respective pads 44, using wire bonds 43, as are anodes 41 in the case of blue and green die 32, 31. As seen on Fig. 2, six electrical connections must be made to illumination means
  • red LEDs 30 have a much smaller forward voltage drop than do blue or green LEDs 32, 31 at the same current.
  • This wiring arrangement more nearly matches the voltage required to drive the three LED strings shown in Fig. 5, thus minimizing voltage transients as the camera timing function switches sequentially among and between the three colors.
  • the supply voltage (VR) for red die 30 will be 3.9 V, with a total red LED current of 200mA.
  • the supply voltage for blue LED die 32 (VB) will be 5.5 V, at 1.2 A total blue LED current.
  • Green LED die 31 will have a supply voltage (VG) of 3.3 V, at 1.2 A total current.
  • the character of the object must be considered as well as the amplitude and spatial resolution of the three primary colors. It is known that the spatial resolution of the color components from a body cavity contain red data with high frequency variation, green data with little substantial variation , and blue data with intermediate frequency variation. Further, images from body cavities have very little blue amplitude component as compared with red and green.
  • the other factors that effect the number of die needed of each color are LED efficiency, CCD video detector quantum efficiency at each of the three wavelengths, and the needed signal-to-noise ratio.
  • the circuit shown in Fig. 9 can be used in the system of the present invention to provide proper color balance.
  • the video data input (as reflected from the object field into endoscope 15 is alternated between red, green, and blue positions.
  • the red primary color input is not adjusted.
  • Blue and green video amplifiers 60 and 62 are used to compensate and adjust the blue and green video levels, using amplifier gain control inputs 61 and 63.
  • the LED assemblies 10 of Fig. 1 or Fig.'s 13a and b can deliver 200 milliwatts per cubic centimeter of volume or 5 watts per pound of weight. Since the single sensor sequential camera described above requires approximately 5 to 10 milliwatts of light output, the illumination system of the present invention can be made small and light in weight as compared to the prior art, thus allowing it to be highly portable and installed in the distal end of an endoscope.
  • the power distribution of the light from endoscope 15 should be as homogenous as possible to insure adequate lighting in all zones of the image and, in the case of sequential cameras, the three colors should be coincident to avoid chromatic effects.
  • Fig. 7 shows a side view of a typical LED die 22 positioned within a reflector cup 21.
  • LED die 22 is almost cubic in shape, with each dimension being approximately 250 microns. Actually, most die are slightly trapezoidal in shape, being somewhat larger at the base than at the top.
  • the horizontal cross sections are usually square.
  • Light is emitted from the top edges 3 and 5 of die 22, primarily in a small horizontal angular cone and from the top surface 4 in, more or less, a cosine distribution. The fraction of the light emitted from the edges as compared to the top surface depends on the technology used in constructing die 22. Typically, for a blue LED 32 made of a silicon carbide die, the edge emission accounts for 80 per cent of the total light output.
  • Fig. 7 de ⁇ picts a die 22 mounted such that the edge emission is located in a 20 degree cone centered at the focus of a hemispherical reflecting cup 21. It can be seen that the rays are redirected into a 36 degree cone about the vertical axis. The reflected light adds to the light emitted from the top surface 4 of die 22. If LED die 22 were used without reflecting cup 21, none of the edge emitted light would reach the object field.
  • Fig.'s 6a, b, and c illustrate a preferred geometry of reflector cup 21 which is molded of very high purity alumina to have a flat, centrally disposed die mounting surface 26 with a 0.6 mm diameter, located approximately 0.4 mm below the top of cup 21.
  • a concave section 25 surrounds surface 26 and extends upwardly and outwardly a linear distance of approximately 0.68 mm, thereby defining an outer diameter of cup 21 of approximately 1.3 mm.
  • the radius of curvature of concave section 25 is approximately 0.56 mm.
  • An integrally formed post 27 facilitates mechanical attachment of 21 to substrate 20.
  • Fig.'s 10 - 13 illustrate an alternate embodiment of LED illumination means 10 in which reflector cups 21 are molded into ceramic substrate 20. Electrical interconnections are made by first metal depositing the entire top or distal surface of substrate 20 and etching away the areas that are not electrically connected, leaving the wire bond pattern shown on Fig. 11a. LED die.22 are then bonded to die mounting surface 26 of reflector cups 21, as seen in Fig.'s 12a and b. Lead bonding to the LED die is accomplished in the same manner as shown in Fig.'s 3 and 4, resulting in illumination means 10 shown in Fig.'s 13a and b.
  • the illumination system described above is ideally suited for use with applicant's
  • FIG. 14 there is shown by block diagram representation a field sequential video imaging system in combination with the illumination system of the present invention, as well as the basic method by which an object to be viewed is illuminated and color video image data is processed.
  • the method begins by illuminating an object (not shown) with light from a first primary color light source, red LED 30 for example, for a period of time typically equal to a standard television field period. Conventionally, this period is 1/60 second.
  • Red LED 30 is activated for this field period by one of three outputs from the divide by three ring counter 14, which has been selected by the vertical drive signal of the sensor 2 in endoscope 15, preferably a conventional charge coupled device (CCD) assembly, such as the model CCB/M27 from Sony Corporation of America. However, any appropriate photo sensor array can be used.
  • CCD charge coupled device
  • any appropriate photo sensor array can be used.
  • the light reflected from the object is focused onto sensor 2 by lens system 52, also of conventional design.
  • the vertical drive signal makes a transition and thereby selects the second output of the ring counter 14, resulting in the deactivation of red LED 30 and the activation of a second primary light source, green LED 31 for example, for one field period.
  • analog data measuring the response of sensor 2 to light reflected from red LED 30 is captured by analog- to-digital (A/D) converter 16 while integration of the second signal (from green LED 31) is occurring in sensor 2.
  • A/D 16 is provided both to a first digital delay unit 17 and a matrix switch 18.
  • First delay 17 delays the digitized signal for a time period equal to one field period.
  • the output signals of ring counter 14 are timed and synchronized such that matrix switch 18 connects the output of A/D 16 (reference DO) to first digital-to-analog converter (DAC) 19.
  • First DAC 19 converts the first captured and digitized primary color signal corresponding to the first primary color, from red LED 30, back to analog form, to be used as the odd field video data of the first primary color signal, red for example.
  • the object is illuminated by a third primary color light source, blue LED 32 for example, for a third period of time equal to a field period.
  • a third primary color light source blue LED 32 for example, for a third period of time equal to a field period. This is accomplished by the vertical drive signal from the sensor 2 making a transition, thereby deactivating green LED 31 and activating blue LED 32.
  • the third primary color light reflected from the object is focused onto sensor 2.
  • the analog video signal corresponding to the level of reflected second primary color light is captured and digitized by A/D 16.
  • the outputs of the ring counter 14 are in such a state as to connect the output from the A/D 16 (DO) to a second DAC 70, and the output from first delay 17 (Dl) to first DAC 19.
  • response of the sensor 15 to the first primary color signal, from red LED 30, is again presented at the output of first DAC 19 for the even field period of the first primary color.
  • the output of second DAC 70 is the analog video signal corresponding to the second primary color from green LED 31.
  • the object is again illuminated with red LED 30 for a fourth period of time equal to a standard field period. This is accomplished by the vertical drive signal of sensor 2 making a transition which causes green LED 32 to be deactivated and red LED 30 to again be activated.
  • the third color analog signal is captured from sensor 2 and digitized by the A/D 16 during this fourth field period, while the first color light signal is again being integrated.
  • the second color captured and digitized signal is delayed by first delay 17 and the first color digitized signal is further delayed by one field period by a second delay unit 72.
  • the outputs of ring counter 14 are such that A/D 16 output (DO) is connected to a third DAC 71, the output of the first delay 17 (Dl) is connected to second DAC 70, and the output of second delay 72 (D2) is connected to first DAC 19.
  • the second color digital signal is reconverted to analog format by second DAC 70 and becomes the odd field of the second color signal.
  • the captured digitized third primary signal (not delayed) is reconverted to analog format by third DAC 71 and becomes the odd field of the third color video signal.
  • the process continues, in the manner previously described, with repeated successive second, third, and fourth illumination periods.
  • the first field or illumination period is operationally identical to the seventh illumination period, except that the first illumination period begins with sensor 2 and related devices in a starting or "0-state" condition. It should be noted that if precise field period analog delay lines were available it would not be necessary to digitize the output of sensor 2 and then reconvert it to analog format. Rather, the sequential analog signals could be merely switched by matrix switch 18 to their respective color signal outputs.
  • the resulting video image will comprise conventional odd and even frames or fields of data comprising typically 262.5 horizontal lines each which are interlaced and displayed for one standard field period (1/60 second) each, producing a completed television video image of 525 horizontal lines.
  • the digitized primary color signals and sync signal can be sent to the inputs of a standard NTSC format modulator/encoder unit 28, for display on a standard NTSC format television receiver 29.
  • red LED's 30 can be activated simultaneously with green LED's 31 during periods which are sequentially interspersed between periods of separate illumination by red LED's 30 and blue LED's 32.
  • the reflected light from the object resulting therefrom is then used to obtain signal levels from which chrominance and luminance signals can be calculated and generated in manner well known to those skilled in the art.
  • Fig. 15 illustrates a second embodiment of the illumination system of the present invention in which illumination means 10 includes both an LED assembly or other light source mounted at the proximal or camera head end of endoscope 15 and a light transmission means, such as fiber optic cables 11 which extend along sheath 53 to the distal end of endoscope 15.
  • illumination means 10 includes both an LED assembly or other light source mounted at the proximal or camera head end of endoscope 15 and a light transmission means, such as fiber optic cables 11 which extend along sheath 53 to the distal end of endoscope 15.
  • Fig. 16 shows another embodiment of the illumination system in which illumination means 10 includes both an LED assembly 11 and a white light source 12 which extends through aperture 24 of assembly 11.
  • White light source 12 could be a Xenon tube, for example, which can be pulsed to conform with sequential color illumination requirements.
  • blue filter By placing a blue filter in front of white light source 12, blue light can be obtained and low efficiency blue LEDs could be eliminated from LED assembly 11.

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  • Optics & Photonics (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Animal Behavior & Ethology (AREA)
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  • Instruments For Viewing The Inside Of Hollow Bodies (AREA)
  • Color Television Image Signal Generators (AREA)

Abstract

Un système d'éclairage (10) pour une caméra d'endoscope comporte une pluralité de diodes électroluminescentes fixées à un substrat (20). Le substrat est adapté pour être fixé à l'extrémité distale de l'endoscope. Chaque diode électroluminescente (22) est placée dans une coupelle de réflecteur (21) qui dirige la dispersion angulaire de la lumière émise vers l'objet à visionner.
PCT/US1994/013476 1993-11-22 1994-11-21 Systeme d'eclairage a diodes electroluminescentes pour cameras d'endoscopes WO1995015060A1 (fr)

Priority Applications (2)

Application Number Priority Date Filing Date Title
AU12927/95A AU694466B2 (en) 1993-11-22 1994-11-21 Single sensor video imaging system and method using sequential color object illumination
EP95904110A EP0734629A1 (fr) 1993-11-22 1994-11-21 Systeme d'eclairage a diodes electroluminescentes pour cameras d'endoscopes

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US15637693A 1993-11-22 1993-11-22
US08/156,376 1993-11-22

Publications (1)

Publication Number Publication Date
WO1995015060A1 true WO1995015060A1 (fr) 1995-06-01

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PCT/US1994/013476 WO1995015060A1 (fr) 1993-11-22 1994-11-21 Systeme d'eclairage a diodes electroluminescentes pour cameras d'endoscopes

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EP (1) EP0734629A1 (fr)
AU (1) AU694466B2 (fr)
CA (1) CA2177178A1 (fr)
WO (1) WO1995015060A1 (fr)

Cited By (13)

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GB2339926A (en) * 1998-07-07 2000-02-09 Winter & Ibe Olympus Endoscope with array of light sources
WO2001049164A1 (fr) * 1999-12-29 2001-07-12 Keymed (Medical & Industrial Equipment) Ltd Source lumineuse pour endoscopes
US6303916B1 (en) 1998-12-24 2001-10-16 Mitutoyo Corporation Systems and methods for generating reproducible illumination
FR2834077A1 (fr) * 2001-12-20 2003-06-27 Rbe Endoscope a usage non medical
WO2003082075A3 (fr) * 2002-03-22 2004-01-22 Ethicon Endo Surgery Inc Systeme de visualisation integre
US6692431B2 (en) * 2001-09-07 2004-02-17 Smith & Nephew, Inc. Endoscopic system with a solid-state light source
EP1522253A1 (fr) * 2003-10-07 2005-04-13 Henke-Sass, Wolf GmbH Endoscope électronique
EP1961371A2 (fr) * 2007-01-30 2008-08-27 Fraunhofer-Gesellschaft zur Förderung der angewandten Forschung e.V. Dispositif d'éclairage pour un dispositif de détection d'image au niveau de l'extrémité distale d'un endoscope
WO2010019744A3 (fr) * 2008-08-13 2010-05-27 Lumination Llc Réflecteur à del, et lampe comprenant celui-ci
EP1982636B1 (fr) 2001-06-18 2012-02-22 Given Imaging Ltd. Dispositif de détection in vivo avec carte de circuit dotée de sections rigides et sections flexibles
CN104970756A (zh) * 2013-07-08 2015-10-14 全视技术有限公司 自发光互补金属氧化物半导体影像传感器封装
DE102015103331A1 (de) * 2015-03-06 2016-09-08 Schott Ag Hermetisch abgedichtete LED-Leuchte, Verfahren zur Herstellung einer hermetisch abgedichteten LED-Leuchte sowie ärztliches Instrument umfassend eine hermetisch abgedichtete LED-Leuchte
US10890318B2 (en) 2015-03-06 2021-01-12 Schott Ag Hermetically sealed LED light and method for manufacturing a hermetically sealed LED light

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US8029439B2 (en) 2005-01-28 2011-10-04 Stryker Corporation Disposable attachable light source unit for an endoscope
US7668450B2 (en) 2005-01-28 2010-02-23 Stryker Corporation Endoscope with integrated light source

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Cited By (23)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
GB2339926A (en) * 1998-07-07 2000-02-09 Winter & Ibe Olympus Endoscope with array of light sources
US6303916B1 (en) 1998-12-24 2001-10-16 Mitutoyo Corporation Systems and methods for generating reproducible illumination
WO2001049164A1 (fr) * 1999-12-29 2001-07-12 Keymed (Medical & Industrial Equipment) Ltd Source lumineuse pour endoscopes
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EP0734629A4 (fr) 1996-08-06
AU1292795A (en) 1995-06-13
CA2177178A1 (fr) 1995-06-01
AU694466B2 (en) 1998-07-23
EP0734629A1 (fr) 1996-10-02

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