WO2009052847A1 - Dispositif de vaporisation de tissus par rayonnement laser - Google Patents

Dispositif de vaporisation de tissus par rayonnement laser Download PDF

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Publication number
WO2009052847A1
WO2009052847A1 PCT/EP2007/009246 EP2007009246W WO2009052847A1 WO 2009052847 A1 WO2009052847 A1 WO 2009052847A1 EP 2007009246 W EP2007009246 W EP 2007009246W WO 2009052847 A1 WO2009052847 A1 WO 2009052847A1
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Prior art keywords
pulse
laser
tissue
pause
generated
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PCT/EP2007/009246
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German (de)
English (en)
Inventor
Lothar Limmer
Original Assignee
Limmer Laser Gmbh
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Priority to PCT/EP2007/009246 priority Critical patent/WO2009052847A1/fr
Publication of WO2009052847A1 publication Critical patent/WO2009052847A1/fr

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    • 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
    • A61B18/203—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 applying laser energy to the outside of the body
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B18/18—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves
    • A61B18/20—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using laser
    • A61B18/22—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using laser the beam being directed along or through a flexible conduit, e.g. an optical fibre; Couplings or hand-pieces therefor
    • A61B18/26—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 for producing a shock wave, e.g. laser lithotripsy
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B2018/00315—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body for treatment of particular body parts
    • A61B2018/00452—Skin
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B2018/00571—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body for achieving a particular surgical effect
    • A61B2018/00625—Vaporization

Definitions

  • the invention relates to a device for the vaporization of tissue by means of laser radiation according to the preamble of claim 1.
  • EP 1349509 A1 shows methods for the laser treatment of soft tissue.
  • a method for the treatment of soft tissue, in particular prostate tissue which provides a solid-state laser which emits light having a wavelength of 200 to 1000 nm or 1100 to 1800 nm and having a laser element which is arranged to pump energy of one Pump power source to receive.
  • the radiation source is modulated such that the laser element is caused to emit laser light with a pulse duration between 0.1 and 500 ms and pulse frequencies between 1 and 500 Hz.
  • the laser light is applied to the target tissue.
  • the solid-state laser is preferably designed as a frequency-doubled neodymium-YAG laser in a known manner, which emits laser light having a wavelength of 532 nm.
  • the pump energy source e.g. a Zündlampe, an arc lamp or a laser diode serve.
  • the solid-state laser itself can also be designed as a laser diode pumped by means of electrical energy.
  • the difficulty arises that the green wavelength (532 nm) obtained due to the frequency doubling is particularly strongly absorbed by blood or the hemoglobin (Hb) contained therein.
  • the blood is increasingly coagulated under the influence of laser radiation, but changes its color due to carbonization, which results in a reduction in the absorption of green light or no further absorption.
  • Hb hemoglobin
  • the green wavelength of a frequency-doubled Nd: YAG laser leads to difficulties in visualization during tissue treatment. Since the green laser beam is in the visible part of the spectrum, it leads to strong Transitions of the optics or camera used for visualization by the surgeon, so that additional aids such as filters are required. This makes the documentation of an operation significantly more difficult.
  • frequency-doubled Nd YAG lasers, which have a Q-switch operation, must be pulsed at high frequency, eg, 1800 Hz, to produce the green wavelength of 532 nm due to the inherent crystal properties of the crystal , They are bound to a constantly high operating frequency, so they can only be operated in "quasi-continuous operation", whereby inevitably the average power down limits are set, so you can not work with low average power
  • YAG Lasers also have a comparatively high power dissipation and therefore a very unfavorable efficiency, and they have an enormous energy requirement for providing a laser power suitable for the vaporization of soft tissue, which is located at the limit of the power supply usually available via the power stations or even beyond.
  • diode lasers have the disadvantage that they can not be operated in high power operation, ie above 100 watts, in order to vaporize especially soft tissue in a satisfactory manner.
  • High-power diode lasers are hitherto known only from the industrial environment for the purpose of material processing. However, such laser devices are not suitable for the vaporization of tissue for many reasons, especially since no precautions to avoid unwanted carbonization can be made, so that the quite available high performance of such industrial laser devices not in a meaningful and secure way can be used for medical purposes.
  • Nd YAG laser nor known from the medical technology diode laser before a mode in which in a predetermined manner, carbonization of remaining tissue can be satisfactorily avoided without affecting the quality of the vaporization of the tissue to be ablated.
  • US Pat. No. 5,632,739 discloses a two-pulse device for the lateral irradiation of tissue by means of laser light, wherein a first light pulse transmitted through a first optical waveguide serves to irradiate a liquid-containing region to form a vapor bubble and a second through a second Optical fiber transmitted pulse can be passed through the vapor bubble and used to ablate tissue of a patient.
  • the device preferably employs a Ho.YAG laser, but may for example be designed as an infrared diode laser.
  • the duration of the first and second pulses of light and the intervening pulse pause may be varied to maximize the energy to be transmitted to the target tissue.
  • the two-pulse principle used here is to exploit the so-called “Moses effect” to reduce the absorption of infrared light in liquids, such as water, where the first pulse causes the expansion of a vaporization bubble in the water to create a "tunnel "for the energy of the second laser pulse.
  • the purpose of this is to prevent the laser beam from being absorbed too soon by the water.
  • a higher energy can be transferred to the target tissue, ie a higher penetration depth into the tissue can be achieved in order to eliminate as much tissue as possible.
  • the invention is therefore based on the technical problem of providing an improved device for the vaporization of tissue by means of laser radiation, which enables only a small damage of the tissue surrounding the target tissue, in particular with a consistently high ablation quality.
  • the invention is based on the finding that current-pumped laser diodes with appropriate control and configuration can overcome the disadvantages of the known from the prior art devices and methods for vaporization in particular of soft tissue.
  • a device for the vaporization of tissue by means of laser radiation comprising at least one laser unit for generating at least one laser beam having a wavelength in the near infrared region, wherein the laser unit is designed as a diode laser and to avoid carbonization of the tissue in pulsed operation is operable, by the laser unit in the pulse mode laser light pulses and / or pulse packets with a variable pulse-pause ratio can be generated and successive pulses and / or pulse packets different Have benefits.
  • a pulse packet is to be understood as meaning a sequence of an arbitrary number of individual laser pulses of the same intensity and duration.
  • the solution according to the invention consists, in particular, of providing a device in which successive laser pulses and / or pulse packets have different powers.
  • the type of successive "power sequence" ie eg the stepwise increase and decrease of the laser power
  • the solution according to the invention therefore does not lead to a maximization of the penetration depth of the laser beam, but rather to its limitation.
  • the duration of the laser light pulses ie, the pulse width
  • the length of the pulse pauses varies within a pulse or Pulsbrise to achieve a variable pulse-pause ratio.
  • the power supply used to provide the pumping current or necessary for controlling the power supply driver software is the limiting factor.
  • pulses or pulse packets of different and / or same pulse width and / or pulse pauses of different and / or the same length to a virtually arbitrary pulse sequence and best possible to the desired treatment and the target chromatograph, ie tune the laser light to be irradiated tissue.
  • no specific working frequency is decisive, but an arbitrarily adjustable sequence of preferably different pulse widths and pauses to achieve particularly favorable tissue reactions.
  • the device according to the invention for providing a laser power suitable for the vaporization of tissue has no energy requirement beyond the usual level, which would not be covered by the voltage normally provided by the power stations.
  • the device according to the invention To provide the energy required to operate the device according to the invention, no high voltage is necessary, but rather, for example, the commonly available AC mains (in Europe eg 230V) is sufficient for the power supply. Since diode lasers have a comparatively low power loss and therefore a very favorable efficiency, the device according to the invention also requires no particularly expensive cooling, which would entail a consumption of cooling liquid. Since the wavelength of the laser light of the device according to the invention is in the near infrared range, for example, not only can blood be coagulated without undesired carbonization, but also tissue can be vaporized. Although infrared light is also absorbed to some extent by blood (or hemoglobin), it is weaker than in the green region of the visible spectrum.
  • the absorption is carried out to a greater extent by water or water-containing constituents, so that with sufficient power rapid vaporization can be achieved.
  • Blood is thus preferably evaporated before coagulation and thus a change in its color occurs, ie the absorption of the laser light is hardly reduced even after treatment of tissue layers lying on top.
  • the wavelength of the device according to the invention is aimed less at the absorption of the laser light by blood (or hemoglobin) than at water as the target chromatophore, which is why, in particular, the vaporization of soft tissue, which is highly hydrous, can be carried out in an advantageous manner.
  • the pulse width and / or the length of a pulse pause and / or the pulse-pause ratio can be varied as desired.
  • the "pulse width” can either be the duration of a single pulse or a pulse packet.
  • Pulse Pause can be understood as the pause before or after a single pulse as well as the pause before or after a pulse packet.
  • the parameters for determining the respective operating mode, ie, depending on the type of tissue to be treated with regard to the expected tissue reactions most favorable combination of pulse sequences of individual pulse width and pulse pauses individual length may preferably be pre-selected by the operator and further preferably set by means of an input unit via a user interface.
  • the pulse widths of successive pulses and / or pulse packets and / or the pulse pauses between successive pulses and / or pulse packets are of different lengths.
  • the variation of the pulse width of successive pulses or pulse packets and / or the variation of the length of successive pulse pauses has proven to be effective, since a targeted cooling of the target tissue between a plurality of pulses in achieved in a controlled manner and can be adjusted individually depending on the tissue type.
  • the power varies within a pulse and / or pulse packet itself.
  • the variation of the power would not be discrete, i. e.g. stepwise, but quasi-continuously, i. occurs under almost constant increase or decrease in power, for example, within a laser pulse and / or -pulseveres.
  • the different powers of successive pulses and / or pulse packets can be assigned in a predetermined manner to different pulse widths.
  • a highly flexible design of the pulse sequences can be realized.
  • an extremely flexible and optimally adaptable tissue treatment with respect to the desired tissue reaction to the respective target tissue can be achieved.
  • the different power of successive pulses and / or pulse packets is arbitrarily variable and can be selected in advance by the surgeon and individually adjustable via a user interface.
  • the settings of one or more certain preferred modes of operation each having different pulse sequences with regard to pulse width, pulse pause and respectively assigned power stored in the associated memory of a control unit and are retrievable by means of a control software as preset work programs.
  • a control software as preset work programs.
  • the Power in connection with the pulse mode of the device according to the invention almost arbitrarily variable and adjustable.
  • the laser unit with an average power of at least 100 watts, preferably between 100 and 250 watts, more preferably between 150 and 180 watts, operable. Due to the comparatively high average power (and thus likewise comparatively high pulse peaks of, for example, at least 200 W), shorter pulses can be used for the same power transmission. In addition to less heating of the deeper layers, this also allows a higher operating speed, i. It is a particularly fast and gentle removal or evaporation of tissue possible.
  • the pulse width of at least one pulse and / or at least one pulse packet and / or at least one pulse pause is less than 1 ms.
  • the extremely short, but very high-energy pulses achieved in this way have less damaging effect on the tissue, since almost no heating takes place in the layers lying below the target tissue.
  • the shorter the pulse width the more accurate can be vaporized without extensive unwanted carbonization.
  • the pulse widths and / or pulse pauses are preferably in the microsecond range, i. approx. between 1 and 1000 ⁇ s.
  • the pulse width of at least one pulse and / or at least one pulse packet and / or the at least one pulse pause is between 50 and 200 ⁇ s.
  • the shorter the pulse width the more accurate the vaporization can be without unwanted heating of the layers lying below the target tissue.
  • pulses with a pulse width shorter than 50 ⁇ s are difficult and can be realized at great expense at the present time. Therefore, in the range between 50 and 200 ⁇ s, the device according to the invention can be operated particularly efficiently in view of the rising costs with even shorter pulses. Because with these pulse widths and pauses Even if extremely satisfactory vaporization results can be achieved, the cost-benefit ratio in this area reaches a maximum.
  • At least one successive pulse width and pulse pause have essentially the same length. This has been demonstrated in experiments for certain types of tissue with regard to the desired tissue responses, i. maximum vaporization of the target tissue with minimal damage to the surrounding tissue has been found to be particularly advantageous.
  • At least one successive pulse width and pulse pause have substantially different lengths. This has been demonstrated in experiments for certain other types of tissue with respect to the desired tissue responses, i. maximum vaporization of the target tissue with minimal damage to the surrounding tissue has been found to be particularly advantageous.
  • the individual design of the pulse-pause sequences both with the same and with different lengths can be realized by means of the device according to the invention without much effort.
  • At least one successive pulse width and pulse pause together have a length of approximately 100 ⁇ s.
  • a tolerance range of +/- 10% can be subsumed under the term "about 100 ⁇ s.” It has been shown that, in particular for soft tissue with a total duration of about 100 ⁇ s, particularly favorable evaporation properties are associated with as little damage to the surrounding as possible This depends on the respective thermal relaxation time of the target or surrounding tissue, with a local optimum in particular for prostate tissue with a total duration of about 100 ⁇ s.
  • At least one pulse packet has between 500 and 5000 individual pulses. This corresponds to an order of magnitude in which the target conflict that occurs can best be handled, that higher frequencies (ie shorter pulses) allow faster tissue removal, but too high frequencies without intervening pause transmit too much energy per pulse packet and heat the surrounding Tissue then becomes too high.
  • the wavelength of the means of At this wavelength in the near infrared range for example, at a sufficient average laser power - eg, preferably at least 100 W - not only coagulated blood, but particularly readily vaporized directly, since in this wavelength range, the absorption
  • the laser light is predominantly carried out by water, so that with sufficient power rapid vaporization can be achieved. Blood is thus preferably vaporized before coagulation and thus a change in its color occurs, ie the absorption of the laser light is hardly reduced even after treatment of top tissue layers due to unwanted coagulation.
  • the wavelength of the laser light producible by the laser unit is between 910 nm and 990 nm.
  • this wavelength range preferably at the wavelengths of e.g. 940 nm or e.g. 980 nm or e.g. 915 nm, can be achieved with appropriate timing of the pulse sequences, i. achieve a particularly favorable evaporation properties without unwanted carbonization at a pulse-pause ratio to be determined in advance.
  • a variation within a tolerance range of +/- 20 nm is to be assumed due to the system-inherent properties of laser diodes.
  • the wavelength of the laser light which can be generated by means of the laser unit is between 1450 nm and 1490 nm, preferably 1470 nm.
  • the diode laser wavelength of 1470 nm +/- 20 nm as can be achieved with the wavelength of 980 nm.
  • the high-power diode laser can operate between approximately 800 nm and 1500 nm, depending on which laser head is used at which wavelength.
  • the 980 nm and 1470 nm (+/- 20 nm) wavelengths are beneficial for urological and thoracic surgery because of their absorption behavior in the target tissue.
  • the diode laser has a continuous wave power of at least 200 watts, preferably 200 to 400 watts.
  • continuous wave ("continuouswave) is an operating state to understand in which a constant laser beam is generated without pulse pauses and pulse widths.
  • a continuous wave power of at least 200 W on the one hand enables a high operating speed and on the other hand in pulsed operation a comparatively low heating deeper layers and thus a reduced occurrence of unwanted carbonization, since shorter pulses can be used for the same power transmission than at lower continuous wave powers ,
  • At least one light guide is provided for applying the laser beam which can be generated by means of the laser unit, wherein the laser beam emerges laterally from the light guide at a distal end.
  • the optical axis is perpendicular to the fiber axis and has an opening angle of up to 120 degrees. This is particularly advantageous in the treatment of urological diseases, for example prostate hyperplasia, since the optical fiber passes through the patient's urethra directly to the site of the disease, i. e.g. to the prostate, can be introduced and then a targeted vaporization of the diseased tissue with the best possible handling of the laser beam can be performed by the side emerging from the light guide laser beam.
  • the opening angle may preferably be up to 30 degrees.
  • At least one pilot beam in the visible wavelength range can be generated, which is directed in the direction of the laser beam that can be generated by the laser unit.
  • the target direction of the infra-red laser beam which is invisible to the naked eye, can be made visible to the surgeon, so that the latter can precisely and precisely apply the laser beam to the target tissue.
  • a pilot beam can be generated, for example, by laser light in the milliwatt range, preferably using e.g. Red or green laser light with a power not greater than 5 mW is used to avoid unwanted crossfades.
  • conventional colored light is used to generate the pilot beam.
  • At least one shock wave to Fragmentation of concrements, in particular urinary stones, producible Pulsed Ho: YAG lasers have hitherto generally been used in laser lithotripsy devices known from the prior art. In this application, the wavelength plays a minor role. The effect is based primarily on the photomechanical effect of a short-pulse, high-energy laser radiation. By a so-called. Photodisruption generates a shockwave that, for example, completely shatters a hard and chemically consistent urinary stone.
  • the pulse energies of up to 2.5 J and a pulse duration of up to 400 ms generated with a Ho: YAG laser can also be realized using the described high-power diode laser, whereby the mentioned disadvantages of a solid-state laser such as inferior efficiency, lower variability, etc. can be avoided.
  • Fig. 1 is a schematic representation of a device according to the invention for
  • Fig. 2 is a diagram illustrating the absorption curves of various
  • Fig. 3 shows a schematic representation of an exemplary pulse sequence of the device according to the invention
  • Fig. 4 is a schematic representation of another exemplary pulse sequence of the device according to the invention.
  • Fig. 1 shows schematically a device according to the invention for the vaporization of tissue by means of laser radiation.
  • a laser unit 1 for generating a laser beam 3 with a wavelength in the near infrared range, for example, preferably 980 nm, is provided.
  • the laser unit 1 comprises a laser diode (not shown), which is pumped by the current and can be operated in pulse mode to avoid carbonization of the tissue.
  • a cooling unit 4 a diode driver 6, which comprises an integrated power supply unit (not shown), and a control unit 10 are provided, which are arranged together with the laser unit 1 in a housing 12.
  • a light guide 15 is provided for the application of the laser beam 3 that can be generated by means of the laser unit 1, the laser beam 3 preferably exiting the light guide 15 laterally at a distal end 16.
  • the diode driver 6 serves to provide the pump energy for the laser unit 1.
  • the control unit 10 controls By means of an electronic control unit the diode driver 6 and thus also the laser unit 1 and preferably also the cooling unit 4.
  • laser pulses and / or pulse packets with a variable pulse-pause ratio can be generated by the laser unit 1 in pulse mode (see FIGS ).
  • the respective operating mode of the laser unit 1 can be controlled by means of the control unit 10 and diode driver 6, it being possible to set almost any desired sequences of laser light pulses.
  • the pulse width 25, ie the duration of a laser light pulse or pulse packet, and / or the length of a pulse pause 26 and / or the pulse-pause ratio and / or the different power of successive pulses 22 and / or pulse packets 23 (see Figures 3 and 4) and / or the respective power in connection with the pulse mode almost arbitrarily variable and adjustable.
  • the parameters for defining the respective operating mode, ie the combination of pulse trains of individual pulse width 25 and pulse breaks 26 of individual length, which is most favorable depending on the type of tissue to be treated, can be selected in advance by the surgeon and can be pre-selected by means of an input unit (not shown) User interface.
  • the settings of one or more specific preferred operating modes, each having different pulse sequences with respect to the pulse width 25, pulse pause 26 (as in FIGS. 3 and 4) and respectively assigned power, are stored in an associated memory (not shown) of the control unit 10 and by means of a control software as default work programs available.
  • the laser unit 1 is operable with an average power of at least 100 watts and a continuous wave power of at least 200 watts.
  • a pilot beam (not shown), for example by red laser light with a power of approximately 5 mW, can be generated in the visible wavelength range, which is directed in the direction of the laser beam 3 that can be generated by the laser unit 1.
  • Fig. 2 is a diagram illustrating the absorption curves of various tissue constituents at different wavelengths.
  • the abscissa represents the wavelength in nm and the ordinate the respective absorption coefficient in logarithmic representation. Shown are the absorption curves of hemoglobin (Hb) 17, of HbO 2 (ie hemoglobin saturated with oxygen) 18, of melanin 19 and of water 20. It can be seen in particular that the light absorption of hemoglobin and HbO 2 is between 500 and 600 nm has a local maximum and subsequently decreases with increasing wavelength, while the light absorption of water between 500 and 1000 nm increases almost steadily and between 900 and 1000 nm reached local maximum.
  • Hb hemoglobin
  • HbO 2 ie hemoglobin saturated with oxygen
  • laser light having a wavelength of, for example, 532 nm is absorbed to a much greater extent by hemoglobin or HbO 2 than by water
  • laser light having a wavelength in the near infrared range, ie of 980 nm, for example, to a much greater extent is absorbed by water than hemoglobin or HbO 2 .
  • FIGS. 3 and 4 each show a schematic representation of an exemplary pulse train of laser light pulses or pulse packets of the device according to the invention.
  • the abscissa represents the time axis while the ordinate represents the power of the light pulses.
  • different pulse packets 23, 23a, 23b, 23c, 23d, 23e are shown, each having a specific pulse width 25, 25a, 25b, 25c, 25d, 25e and each interrupted by pulse pauses 26, 26a, 26b, 26c, 26d ie are separated in time.
  • a pulse packet 23, 23a, 23b, 23c, 23d, 23e is to be understood as a sequence of an arbitrary number of individual pulses 22, 22a, 22b, 22c, 22d, 22e of equal intensity and duration.
  • the individual pulses 22, 22a, 22b, 22c, 22d, 22e of a pulse packet 23, 23a, 23b, 23c, 23d, 23e are indicated schematically only for illustrative purposes and the number of individual pulses shown within a packet does not correspond to the actual number in reality. Rather, a pulse packet 23, 23a, 23b, 23c, 23d, 23e actually each preferably has between 500 and 5000 individual pulses 22, 22a, 22b, 22c, 22d, 22e.
  • a wavelength of the laser light in the near infrared range is to be assumed, for example preferably between 800 nm and 1000 nm, more preferably between 910 nm and 990 nm and more preferably for example 980 nm can be generated by means of the device according to the invention.
  • Fig. 3 it can be seen that within the pulse sequence, a variation of the pulse-pause ratio, ie the ratio of the duration of a laser light pulse to the duration of the subsequent pause, takes place.
  • the first pulse packet 23 having the pulse width 25 and the pulse pause 26, which follow one another have substantially the same length, namely, for example, 100 ⁇ s each, ie the pulse-pause ratio is 1: 1.
  • the second pulse packet 23a with the pulse width 25 and the subsequent pulse pause 26a have substantially different lengths and thus also a different pulse-pause ratio.
  • both the duration of the laser light pulses ie the pulse width 25, 25a, 25b, 25c, 25d, 25e
  • the length of the pulse pauses 26, 26a, 26b, 26c, 26d vary within the pulse or pulse packet sequences.
  • the pulse widths 25, 25a of the successive pulse packets 23a, 23b and the pulse pauses 26a, 26b between the successive pulse packets 26a, 26b have different lengths. While in FIG. 3 the pulses of the pulse packets 23, 23a, 23b all have the same power, in contrast FIG. 4 shows a pulse sequence in which the pulse packets 23c, 23d, 23e contained therein (including the successive pulse packets 23c, 23d ) each having laser light pulses with different amplitude, ie with different powers, have. The different powers of the pulse packets 23c, 23d, 23e are assigned in a predetermined manner in each case to specific pulse widths 25c, 25d, which are at least partially different. In both FIG. 3 and FIG.
  • the pulse width 25, 25a, 25b, 25c, 25d, 25e of a pulse packet 23, 23a, 23b, 23c, 23d, 23e and a pulse pause 26, 26a, 26b, 26c, 26d are each between 50 and 200 ⁇ s.
  • a successive pulse width 25c and pulse pause 26c together have a length of approximately 100 ⁇ s. In the same way as illustrated merely by way of example for pulse packets in FIG.
  • any individual pulses such as the pulse width 25b shown in FIG. 3 or, for example, the pulses 22c, 22d, 22e shown in FIG the interval to the preceding or succeeding pulse or pulse packet and / or be varied as desired with respect to their respective performance.

Abstract

L'invention concerne un dispositif de vaporisation de tissus par rayonnement laser, comportant au moins une unité laser (1) destinée à produire au moins un faisceau laser (3) ayant une longueur d'onde dans la gamme du proche infrarouge. L'unité laser (1) est conçue en tant que laser à diodes et peut fonctionner en mode pulsé pour éviter une carbonisation du tissu. En mode pulsé, l'unité laser (1) peut produire des impulsions de lumière laser ou des paquets d'impulsions de lumière laser avec un rapport impulsions-pauses variable et des impulsions et/ou des paquets d'impulsions consécutifs présentent des puissances différentes.
PCT/EP2007/009246 2007-10-25 2007-10-25 Dispositif de vaporisation de tissus par rayonnement laser WO2009052847A1 (fr)

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Cited By (4)

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Publication number Priority date Publication date Assignee Title
WO2010150175A1 (fr) * 2009-06-26 2010-12-29 Koninklijke Philips Electronics N.V. Profil de puissance de rayonnement, appareil et procédé de photothérapie
EP2451030A1 (fr) * 2009-11-16 2012-05-09 Omron Corporation Dispositif et procédé d'usinage laser
ITFI20110023A1 (it) * 2011-02-11 2012-08-12 El En Spa "dispositivo e metodo di trattamento laser della pelle"
GB2599418A (en) * 2020-09-30 2022-04-06 Elekta ltd A method of controlling operation of a radiotherapy device

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GB2599418B (en) * 2020-09-30 2023-08-09 Elekta ltd A method of controlling operation of a radiotherapy device

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