WO1992016154A1 - Material-paring device by means of laser light - Google Patents

Material-paring device by means of laser light

Info

Publication number
WO1992016154A1
WO1992016154A1 PCT/DE1992/000219 DE9200219W WO9216154A1 WO 1992016154 A1 WO1992016154 A1 WO 1992016154A1 DE 9200219 W DE9200219 W DE 9200219W WO 9216154 A1 WO9216154 A1 WO 9216154A1
Authority
WO
Grant status
Application
Patent type
Prior art keywords
laser
optical
fibers
pulse
light
Prior art date
Application number
PCT/DE1992/000219
Other languages
German (de)
French (fr)
Inventor
Kristian Hohla
Johannes Agethen
Original Assignee
Technolas Lasertechnik Gmbh
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

Links

Classifications

    • BPERFORMING OPERATIONS; TRANSPORTING
    • B23MACHINE TOOLS; METAL-WORKING NOT OTHERWISE PROVIDED FOR
    • B23KSOLDERING OR UNSOLDERING; WELDING; CLADDING OR PLATING BY SOLDERING OR WELDING; CUTTING BY APPLYING HEAT LOCALLY, e.g. FLAME CUTTING; WORKING BY LASER BEAM
    • B23K26/00Working by laser beam, e.g. welding, cutting or boring
    • B23K26/02Positioning or observing the workpiece, e.g. with respect to the point of impact; Aligning, aiming or focusing the laser beam
    • B23K26/06Shaping the laser beam, e.g. by masks or multi-focusing
    • B23K26/064Shaping the laser beam, e.g. by masks or multi-focusing by means of optical elements, e.g. lenses, mirrors or prisms
    • B23K26/0643Shaping the laser beam, e.g. by masks or multi-focusing by means of optical elements, e.g. lenses, mirrors or prisms comprising mirrors
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B18/18Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves
    • A61B18/20Surgical 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
    • A61B18/22Surgical 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
    • A61B18/26Surgical 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 for producing a shock wave, e.g. laser lithotripsy
    • BPERFORMING OPERATIONS; TRANSPORTING
    • B23MACHINE TOOLS; METAL-WORKING NOT OTHERWISE PROVIDED FOR
    • B23KSOLDERING OR UNSOLDERING; WELDING; CLADDING OR PLATING BY SOLDERING OR WELDING; CUTTING BY APPLYING HEAT LOCALLY, e.g. FLAME CUTTING; WORKING BY LASER BEAM
    • B23K26/00Working by laser beam, e.g. welding, cutting or boring
    • B23K26/02Positioning or observing the workpiece, e.g. with respect to the point of impact; Aligning, aiming or focusing the laser beam
    • B23K26/06Shaping the laser beam, e.g. by masks or multi-focusing
    • BPERFORMING OPERATIONS; TRANSPORTING
    • B23MACHINE TOOLS; METAL-WORKING NOT OTHERWISE PROVIDED FOR
    • B23KSOLDERING OR UNSOLDERING; WELDING; CLADDING OR PLATING BY SOLDERING OR WELDING; CUTTING BY APPLYING HEAT LOCALLY, e.g. FLAME CUTTING; WORKING BY LASER BEAM
    • B23K26/00Working by laser beam, e.g. welding, cutting or boring
    • B23K26/02Positioning or observing the workpiece, e.g. with respect to the point of impact; Aligning, aiming or focusing the laser beam
    • B23K26/06Shaping the laser beam, e.g. by masks or multi-focusing
    • B23K26/064Shaping the laser beam, e.g. by masks or multi-focusing by means of optical elements, e.g. lenses, mirrors or prisms
    • B23K26/0648Shaping the laser beam, e.g. by masks or multi-focusing by means of optical elements, e.g. lenses, mirrors or prisms comprising lenses
    • BPERFORMING OPERATIONS; TRANSPORTING
    • B23MACHINE TOOLS; METAL-WORKING NOT OTHERWISE PROVIDED FOR
    • B23KSOLDERING OR UNSOLDERING; WELDING; CLADDING OR PLATING BY SOLDERING OR WELDING; CUTTING BY APPLYING HEAT LOCALLY, e.g. FLAME CUTTING; WORKING BY LASER BEAM
    • B23K26/00Working by laser beam, e.g. welding, cutting or boring
    • B23K26/02Positioning or observing the workpiece, e.g. with respect to the point of impact; Aligning, aiming or focusing the laser beam
    • B23K26/06Shaping the laser beam, e.g. by masks or multi-focusing
    • B23K26/064Shaping the laser beam, e.g. by masks or multi-focusing by means of optical elements, e.g. lenses, mirrors or prisms
    • B23K26/0652Shaping the laser beam, e.g. by masks or multi-focusing by means of optical elements, e.g. lenses, mirrors or prisms comprising prisms
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00Surgical instruments, devices or methods, e.g. tourniquets
    • A61B2017/00017Electrical control of surgical instruments
    • A61B2017/00022Sensing or detecting at the treatment site
    • A61B2017/00106Sensing or detecting at the treatment site ultrasonic
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B90/00Instruments, implements or accessories specially adapted for surgery or diagnosis and not covered by any of the groups A61B1/00 - A61B50/00, e.g. for luxation treatment or for protecting wound edges
    • A61B90/06Measuring instruments not otherwise provided for
    • A61B2090/064Measuring instruments not otherwise provided for for measuring force, pressure or mechanical tension

Abstract

A device for paring material, in particular biological tissues, has a laser system that generates laser pulses and a fiber-optic light guide system with fiber-optic light guides (1) gathered into a bundle (2) to which the laser pulses (6) are coupled and that guide the laser pulses (6) to the spot where material is to be pared. The bundle (2) is subdivided into at least two groups of fiber-optic light guides (1) and each laser pulse (6) is not coupled to at least one group of fiber-optic light guides (1).

Description

An apparatus for removing material with laser light

Description

technical field

The invention relates to an apparatus for Abtra¬ gene of material and in particular of biological tissue, comprising a laser system producing laser pulses, and a light guide means having a bundle summarized optical fibers into which the laser pulses are eingekop¬ pelt, and directing the laser pulse to the spot to be ablated in the material.

For example, in laser surgery laser systems are used which evaporate due to their high light output tissue in such a short time and clear away the fact that prak¬ table occurs no heat load on the surrounding nichtbe- radiated tissue. For such laser-induced processes a variety of laser systems, including for some time to be strengthened so called. Excimer laser used that emit light in the UV range.

The removal processes described above are also referred to as photoablation and found mainly in microsurgery (angioplasty, ophthalmology, Ortho¬ pädie etc.) application to ablate in a gentle manner possible tissue.

In addition, however finds the photoablation also applicable to machining of workpieces or the like. prior art

The known devices for photoablation generally have a light guide means, the light passes the Laser¬ to the site to be ablated at the material beispielswei¬ se tissue.

With microsurgical operations, the light guide Ein¬ direction in the so-called. Operation handpieces or flexible Kathe¬ is integrated and therefore must have a lot of flexibility.

Therefore be used as a light guide device usually thin optical fibers. Since optical fibers are destroyed by the laser light if this exceeds a certain specific power density, the light guide means comprises a plurality of fibers, which are combined to form a bundle. Thus laser pulses of high energy can be transported.

Especially in the field of angioplasty, that is, however, the Gefä߬ surgery following problem arises:

Each laser pulse detects and removes a limited tissue depth. This tissue specific depth corresponding approximately to the depth of penetration of the laser light is around a few. So far it has been committed to providing a mög¬ lichst large area with the highest possible energy or Lei¬ stung to apply in order to remove as much tissue per laser pulse.

but the operation speed reached is not dependent (Rate Repititions-) only on the energy per laser pulse and the applied area, but also by the repetition rate of the laser pulses from. The repetition rate is at be¬ generic devices for the removal of Ma¬ known TERIAL and in particular of biological tissues in the union wesent¬ not possible by the physical Repitionsra- te of the laser system, but limited by the ten at higher Pulsra¬ excessive thermal damage to tissue ,

Typically, the repetition rate is less than about 25 Hz in known generic device for removing material.

Furthermore occurs in the procedure, as known in be¬ generic devices for removing material is common, the following additional problem:

For example, in angioplasty is carried out with excimer lasers, which ben on the fiber bundle output abge¬ (depending on Faserbün¬ deldurchmesser) total energies between 30 and 80 mJ. The individual fibers in the bundle are thereby gleich¬ time and as uniformly as possible aufschlagt be¬ with the laser beam. but still much higher Laserpulsener¬ technologies must be used lasers in laser systems with other wavelengths, such as neodymium-YAG lasers, holmium or Dye, len to erzie¬ an ablation effect.

Due to the rapid evaporation of the fabric - the dampfungsvorgänge Ver¬ run typically from the microsecond range - is formed from a shock wave which penetrates into the surrounding tissue. The occurring high pressure gradients can cause significant disruptions and damage in the area. so that damage to the tissue and cell layers that are relatively far from the off latierten area removed is often unavoidable. It comes to traumatic changes that can lead to significant tissue irritation. As a result, re-growth of the cell layers is observed wo¬ may set by a restenosis (re-narrowing).

The laser, originally designed as atraumatic tool, therefore proves to the area to be quite damaging.

Description of the Invention

The invention has the object to provide a device for removing material, and in particular biologi¬ schem tissue with a laser system, wherein the ablation process is carried out gently so that it no or only a negligibly small damaging effect on the environment, such as the healthy tissue environment has.

One inventive solution to this problem is defined in An¬ demanding first Further developments of the invention are subject of the dependent claims

The invention is based on the recognition that the cause is likely to be for the traumatic damage to the environment of the ablatier- th region of the ablation process per se, but the shock wave associated with the ablation with conventional procedure. According to the invention, therefore, the procedure is such that the generation of shock waves during ablation is avoided as much as possible.

This can surprisingly be achieved by the fact that it is considered still reached by a device for removing material, and in particular of biological tissue according to the preamble of claim 1, and these Vorrich¬ tung accordance with the invention is further developed such that the bundle into at least two groups of optical fibers is divided, and in that each laser pulse is not coupled into at least one group of optical fibers.

In other words, the Lichteinkoppelung takes place in the optical fiber bundle in such a temporally and spatially separates ge that the individual optical fibers or groups separated in time and are applied selectively in serial spatial sequence of at least one laser pulse.

The invention is based on the idea that the formation of the shock wave is a direct result of the high energy per laser pulse, the erfor¬ at a Applizierung of light over the entire KätheterguerSchnittsfläche is sary to achieve "useful" removal rates.

therefore, fiber in a single Lichtleit¬ or group of fibers is respectively coupled only one pulse Laser¬ According to the invention, which only radiates a small area be¬ and whose energy is so small that it causes no or no traumatic shock wave. By the scanning movement of the light spot on the position to ablatie- in power range the thermal load of each acted upon by the light spot area is small, so that, in an inventive device, the pulse repetition rate can be increased significantly compared to the prior art (claim 7). This allows the reduced energy per laser pulse, the same or even higher removal rates are achieved as in the prior art despite the "Abtastbewe¬ supply" that performs the laser beam on the position to be ablated Ge samtbereich, and. Here, it is advantageous if the energy pulse of each Laser¬ dimensioned such that the depth of its effect in the tissue in approximately the spot diameter corresponds to (claim 11).

The maximum achievable pulse repetition frequency is therefore no longer by the traumatic effect, but (except by the performance of the laser), only determined by the time interval between two Laser¬ pulses must be chosen such that the shock wave of the first laser pulse is already so has diluted far that interference with the shock wave generated by the transported by the optical fiber or group be¬ adjacent laser pulse, causing no traumatic effect more.

Since pressure waves typically with some 1000 m / sec. spread and the tissue depth within which a Schädi¬ should be avoided supply is not more than 1 mm, berech¬ net so a minimum time between two pulses lake to about 10th

Be so that the individual fibers having a pulse train frequency of less than 10 Hz applied light, then the resulting pressure waves do not overlap. Auf¬ due to the reduced power each Druckwel¬ le is substantially smaller, so that it does not cause pain effect or no traumatic effect.

The basic idea of ​​the invention, therefore, is to subject the individual optical fibers of the bundle sequentially with laser pulses, for example in the field of angioplasty with a typical pulse repetition frequency for each fiber ca per second (but not substantially more) is 25 laser pulses, so that deposited the same total energy obtained than if a conventional Vor¬ direction with 25 laser pulses would be operated per second.

Since the operating data, for example excimer lasers operating a shape in which the individual optical fibers are subjected to a pulse frequency of 25 Hz allow this form of gentle treatment with known laser systems is possible.

so that the basic concept of the invention differs not only because of the fact that the laser beam - is "a scanning" coupled into an optical fiber bundle, but also in principle from the devices in the prior art, in which also a '- in contrast to the prior art scanning movement "of Laser¬ will beam used:

Thus, in the described Vor¬ 4,538,608 direction to the turns in the US-PS "Scan" movement of the scanning beam ver¬ to ablate an area that is substantially larger than the area of ​​the "stationary" with a beam could be thera¬ and a correspondingly widened beam spot peutically processed.

In WO 87/01819, however, the continuous, ie non-pulsed laser beam to a small spot is focused way in order to obtain a large opening angle of the beam and thereby a therapeutic effect substantially only in the focal plane. The scanning motion is used exclusively occur to be able to work with this focused beam a comparably as large spot. Reducing the pulse power or the -energy while increasing the pulse repetition frequency for avoiding Ver¬ traumatic effective shock waves is not addressed in two publications.

In claim 2 is claimed that the optical fibers are aligned such that the Lichtaustrittsflä¬ surfaces of optical fibers, the light entry surfaces are nachbart be¬ are adjacent. To this end, the conductive fibers in the bundle can Licht¬ regularly and in particular line¬ ar arranged (claim 3).

This arrangement of the optical fibers has a number of advantages:

Is according to claim 4, a scanning device provided, each acts on a particular group of optical fibers with a laser pulse, the "scan" of the scanning means is imaged onto the light entry surfaces of the optical fibers to the light exit surfaces, so that even when applying a plurality of optical fibers with a laser pulse at the output the optical fibers are given defi¬-defined and reproducible conditions.

The fact that the launching of a laser pulse in certain optical fibers pulses to an exit Laser¬ this leads to a precisely defined place, can be used further to realize a spatially resolved detection of the ablated material:

In the described in claim 8 embodiment, a shock or pressure wave sensor is provided which detects the induced by each laser pulse shock wave or pressure wave. An evaluation unit detects the respective shock or pressure wave in correspondence with the applied with the triggering pulse laser optical fiber or group of optical fibers. The maximum value and the amplitude of the induced by a laser pulse with a particular pulse duration and with a certain energy shock wave depend namely on the material to which the laser pulse impinges:

For example, result in plaque and other tissue calcined shock wave curves than in normal tissue. Thus, the detection of the shock wave produced in association with each acted upon allows optical fiber or group of optical fibers and so - that, due to the features of claims 2 and 3, respectively - to the place to which the laser pulse is incident, a statement about the type of ablative formatted material.

When shock or pressure wave sensor in principle belie¬ bige pressure sensors, such as intracorporeal sensors can be used which are arranged in a ring around the distal end of the optical fiber bundle.

In a further development is characterized in claim 9, wherein it is not necessary to dispose a sensor intracorporeally. Rather, the shock or pressure wave sensor can be located extracorporeally, as it detects the transmitted through the bundle of optical fibers shock or pressure wave.

The property of a device according to the invention that the pulsed laser beam scans sequentially the region to be ablated may also be used for optical determination of the kind of the ablated material: For this purpose, an optical sensor is provided which lenlängenverteilung the Wel¬ the triggered by each laser pulse the fluorescent light detected. An evaluation unit determines from the wavelength distribution in association with the acted upon by the laser pulse triggering Licht¬ leitfaser or group of optical fibers, the material of the applied field. For details of the determination of the ablated material from the "zurücklau¬ fenden" in the light guide light is made for example to WO 88/08279, on which the rest of the explanation of all details not explained in detail here incorporated by reference.

As a scanning device which generates the "scanning" movement of the pulsed laser beam over the optical fiber bundle, in principle any sampling means, for example, the scanning process described in WO 87/01819 can be used.

In view of the fact that processing in the inventive Vorrich¬ a pulsed laser beam is used, however, it can provide itself, the use in the claims 5 and 6 gekennzeich¬ Neten simple scanning.

According to these claims, the scanning device may comprise a mirror or a angebrach¬ on a rotating disk te prism assembly.

Brief Description of Drawing

The invention will now be described by way of example without restricting the all¬ common inventive concept, based on exemplary embodiments with reference to the drawings. In the drawings: Figure 1 is a simplified diagram for explaining the operation for tissue ablation with a her¬ conventional multi-fiber bundle.

Fig. 2 shows a conventional arrangement for simultaneous Laser¬ beam coupling in a multi-fiber bundle,

Fig. 3 is a simplified diagram for explaining the function of a device of the invention with mirror deflection, and

Fig. 4 shows a cross section through an inventive Vor¬ direction with a rotating prism sheet.

Representation of exemplary embodiments

In the following figures like elements are provided with the same reference numerals and so will be omitted recent conception occurs again these elements.

Fig. 1 shows the distal portion of an apparatus for ablating tissue 4. The apparatus comprises a plurality of optical fibers 1, which are integrated into a bundle 2 angeord¬ net and into a catheter 2 1.

Fig. 2 shows that in known devices for Photoab¬ lation 1, the individual fibers in multi-fiber bundles 2 are applied si¬ Multan with laser light. For this purpose, a current generated by an unillustrated laser system Laser¬ beam is 6 se by an optical imaging or Fokussierlin- 7 (or a lens system) on the coupling surface 8 'of the multi-fiber bundle 2 with the simultaneous adjustment of the beam spot of the size and shape the coupling surface 8 'ready. Thus, all individual optical fibers 1, which are guided within the multi-fiber bundle 2, irradiated simultaneously and as uniformly as possible with laser light. By exiting at each laser pulse at the output 8 "of the multi-fiber bundle 2 light energy directly applied to the (distal) catheter head layers of fabric 4 are heavily loaded thermally so that the fabric evaporates.

Due to this explosively expanding fabric material 3, the ablated material is displaced in front of the catheter head to one side to one side and formed on the other in the surrounding tissue area aus¬ wide shock wave 5, which can lead to tissue and Zeilagenschädi¬ conditions.

Fig. 3 shows a device according to the invention, in which the individual laser pulses of the laser system, in turn, not shown are sequentially injected in single contained in the Multifibre bundle 2 optical fibers. 1

For this purpose, the laser beam 6 through the focusing lens 7 and a deflection unit which has a about a pivot axis D rotatably mounted mirror 9, respectively on einzel¬ ne optical fibers or groups 1 is imaged in such a way that different optical fibers sequentially or -grup¬ pen acted become. To simplify design the mirror guide, are, for example, the individual optical fibers zusam¬ in a non-illustrated catheter to a multi-fiber bundles 2 are quantitatively interpreted in the shown Ausführungs¬, linearly arranged. Deviating therefrom, regular spatial arrangements of optical fibers are also possible (for example, triangle, rectangle, etc.). By clock-wise, that is, with the laser pulses synchronized rotation of the mirror 9 about the rotation axis D all optical fibers sequentially 1 or groups are illuminated or be¬ aufschlagt. However, the clock frequency of the mirror adjustment need not necessarily coincide with the repetition rate of the laser system, that is, per-ray imaging leitfaser a Licht¬ 1 or group more than one light impulse can be transmitted.

According to the invention a shock or Druckwellen¬ sensor 10 is further provided, which detects the induced by each Laser¬ pulse shock wave or pressure wave. 5 The shock or pressure wave sensor 10 is extracorporeally angeord¬ net and detects through the bundle 2 of fibers 1 Lichtleit¬ transmitted shock or pressure wave 5 detects. An evaluation unit, not shown, determines the respective shock or pressure wave in correspondence with the applied with the triggering pulse Laser¬ optical fiber 1 or group of optical fibers from the output signal of the sensor 10th

Fig. 4 shows a further embodiment of the Erfin dung, the un¬ differs from the Ausfüh¬ shown in Fig. 3 approximately, for example by the formation of the deflection unit, which in this embodiment as a rotatable about an axis R disc 11 with prisms 12 ' , is formed .. 12 ".

The laser beam 6 also passes through an optical imaging lens 7 and then passes through a recessed into the edge region of the rotating around the axis R disc 11 prism 12 ', which deflects the beam 6 onto an optical fiber 1 or group of the bundle. 2

The prisms are (in the cross sectional view only two are shown, namely 12 ', 12 ") arranged in the edge region of the plate 11 radially so that the laser beam the prisms (12,12', ...) one after the other in time and happened the Rota¬ tion speed of the disc is deflected differently. then to the average pulse rate of the arrangement.

The methods of sequential scanning can also be used to activate only portions of the catheter section. Here optical fibers are specifically excluded from irradiation, which is technically easy to implement in the dargestell¬ th deflectors. This is especially then of interest if a suitable detection method is used, which allows to identify the tissue located in front of the catheter.

Furthermore, different sites can be irradiated with the light of different lasers.

a further advantage, this beam deflection method is that each individual fiber can be applied with the same energy. This is very difficult at a gleichzeiti¬ gen lighting of the bundle, as each more or less laser beam has nitäten pronounced Inhomoge¬. The total mean power which is thus transported through a fiber 1 can be increased not negligible in this manner, so that a considerable increase of the cutting speed is obtained.

The frequency of the laser pulses must be increased accordingly, the energy of each laser pulse is lowered correspondingly.

The above-mentioned consideration will be illustrated with the following Zahlen¬ example: In a typical angioplasty catheter 50 optical fibers 1 are arranged.

At a pulse repetition rate of 25 Hz per fiber 1, the laser must with a total repetition rate of 1250 Hz betrie¬ be ben. At the same time the individual pulses must be mapped to each have a single fiber or a group of Fa¬ fibers. The laser beam must be scanned so to speak, on the entrance surface 8 'of the fiber bundle. 2 The laser pulse frequency is in orders of magnitude below the above-estimated cut-off frequency of 10 Hz.

The inventive device can thus be easily realized in practice in that any scanning or scanning device is the light-entrance side (proximal) end 8 'of the optical fibers arranged for deflecting the laser pulses such that the laser pulses, the light entry surfaces of the individual fibers 1 "scans".

commercial Applications

The invention can be used both in the medical technology and for material processing of technical Werk¬ breakfast.

Claims

P atentanspr ü che
comprising 1. An apparatus for ablating material (4) and insbe¬ sondere of biological tissue, with a laser system that produces the laser pulses, and a light guide means to form a bundle (2) summarized optical fibers (1), in which the laser pulses are coupled, and guiding the laser pulse to the spot to be ablated in the material, characterized in that the bundle (2) is divided into at least two groups of optical fibers, and in that each laser pulse into at least one group of Licht¬ not conductive fibers is coupled.
2. Device according to claim 1, characterized in that the optical fibers (1) are aligned such that the light exit surfaces (8 ") of optical fibers (1), the light entry surfaces (8 ') are adjacent, are adjacent.
3. A device according to claim 2, characterized in that the optical fibers (1) in the bundle are arranged regularly and in particular, linear.
4. Device according to one of claims 1 to 3, characterized in that a scanning device is seen vorge, each having a specific set of Licht¬ conductive fibers (1) with a laser pulse applied.
5. The device according to claim 4, characterized in that the scanning device comprises a pivotal mirror (9).
6. The device according to claim 4, characterized in that the scanning device mounted one on a rotating disk (11) Prismenanord¬ voltage (12 ', 12 ", ...) has.
7. Device according to one of claims 1 to 6, characterized in that the maximum repetition rate per optical fiber (1) or group is 25 Hz.
8. Device according to one of claims 1 to 7, characterized in that a shock or Druckwellen¬ sensor (10) is provided which detects the induced by each laser pulse shock wave or pressure wave, and that an evaluation unit the respective shock or Druck¬ wave in association with the acted upon by the laser pulse triggering optical fiber (1) or group of light routing fibers detected.
9. Device according to claim 8, characterized in that the impact or Druckwellen¬ sensor (10) is arranged outside the body, and through the bundle (2) detects transmitted by optical fibers (1) Sto߬ or pressure wave.
10. Device according to one of claims 1 to 9, characterized in that an optical sensor is hen vorgese¬ which detects the wavelength distribution of the triggered by each laser pulse the fluorescent light, and that an evaluation unit from the wavelength distribution in association with the triggering of the laser pulse acted upon estimated optical fiber (1) or group of fibers Lichtleit¬ the material of the applied field determined.
11. Device according to any one of claims 1 to 10, characterized in that the energy of each laser pulse is such that the depth of its effect within the fabric (4) corresponds approximately to the spot diameter and / or that it no traumatic effective impact or triggers blast.
12. Device according to one of claims 1 to 11, characterized in that the laser system comprises an excimer laser.
PCT/DE1992/000219 1991-03-13 1992-03-13 Material-paring device by means of laser light WO1992016154A1 (en)

Priority Applications (2)

Application Number Priority Date Filing Date Title
DEP4108146.3 1991-03-13
DE19914108146 DE4108146C2 (en) 1991-03-13 1991-03-13 An apparatus for removing material with laser light

Publications (1)

Publication Number Publication Date
WO1992016154A1 true true WO1992016154A1 (en) 1992-10-01

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WO (1) WO1992016154A1 (en)

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DE4108146A1 (en) 1992-09-17 application

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