JPH03140166A - Method and apparatus for strengtening growth of blood vessel and other tissue - Google Patents

Abstract

PURPOSE: To increase the number of cells without causing photo solidification, photon optical optical histolysis, light evaporation and light removal and resolution by applying two laser beams to an area where the tissue is affected, and setting the irradiation in such a manner that the collision strength to the tissue is weak, and has a specified wavelength of visible red or infrared ray. CONSTITUTION: A first laser A sends an output beam on a first optical axis 10, a second laser B sends an output beam on a second optical axis 11, and the optical axis 11 is bent to the axis 10 in the direction intersecting perpendicularly to the axis 10 by a beam splitter 12. Both laser beams bend laser energy on a transmit axis 15 by use of a common axis 13 and an interference filter 14. A phase shifter 36 is adjusted in such a manner that the combination output is shifted in phase at the same wavelength. The transmitted energy is converged on a small area connected to a fiber optics transmission system in the case of using an endoscope by a converging lens means 16. The respective lasers A, B generate visible red or infrared ray at a very small power in order to avoid local heating and solidification of a tissue and/or tissue and/or cell.

Description

DETAILED DESCRIPTION OF THE INVENTION Field of the Invention The present invention relates to the use of laser radiation to promote or enhance blood vessel or other growth in irradiated localized areas of biological tissue.

[Conventional technology]

J.J., Marshall, et al., Dr. W. The Hague, Junk Publishers, Ophthalmic Surgery Series Documents, entitled "Some New Discoveries in Retinal Radiation with Krypton and Argon Lasers", Volume 36, pp. 21-37.198
4 years ('Some New Findings on
I? etlnal Irradiatlon t
+y Kryptor+and Argon Les
ers, Docum, 0phthal, Pro
c.

5eries, Vol. 36. [1, 21-37
, 1984, Dr. W.

Junk Publishers, The Hagu
The paper by S. J. Marshall, et. It is attached. While emphasis was placed on laser photocoagulation, a ``remarkable discovery'' was reported related to the proliferation of highly vascular endothelial cells near the reaction site. and a subsequent paper, J. Marshall.
) Co-authored, Burwood Academic Publishing Co., Ltd., Lasers in Life Sciences 1 (
2), pp. 125-134. 1986 ('He-Ne
La5er 5tiIIlulation of'H
ua+anFlbroblast Prollfer
atlon and attachment I
nVltro, La5ers in the L
ife 5sciences 1(2).

198B, pp, 125-134. tla
rwood AcademicPublishers
Gmb)! ) reported an experimental study on laser-irradiated culture of excited human tissue, in which the irradiation source was a 1 mW helium φ neon laser providing a coherent source of 633 nm, and the irradiation was 50% In each experiment, the comparative work was performed using a 640 nm interference filter (
(bandwidth 9 nm) with monochromatic, non-coherent light modulated in intensity compared to that of laser delivery to the same culture. The reported results showed that at 24 and 48 hours after 15 minutes of irradiation, certain laser-irradiated cultures showed a significant increase in cell number compared to their respective non-irradiated controls; No significant changes in cell numbers were observed between irradiated and control cultures in non-coherent source experiments.

[Problem to be solved by the invention]

It is an object of the present invention to provide improved methods and means for in-vivo laser irradiation of living tissue.

A particular aim is to achieve this by using perturbation effects caused by multiple laser beam radiations delivered to the affected biological tissue.

Another particular objective is to achieve the above objectives without causing photocoagulation, photonic optical tissue degradation, photoevaporation or photoablative degradation of the affected biological tissues and/or cells.

[Means to solve the problem]

The present invention achieves the above object by emitting at least two laser beams to the affected area of biological tissue, the radiation being: (a) tissue impingement of low intensity; (b) preferably visible red or It has a specific wavelength of infrared radiation. The perturbation is
occurs in the affected cells, directly due to differences in the physical properties of each beam, and indirectly due to the interaction between the two beams at or near the delivery site to the affected tissue. .

〔Example〕

Embodiments of the present invention will now be described with reference to the drawings.

In FIG. 1, a first laser A emits an output beam on a first optical axis 10, and a second laser B emits an output beam on a second optical axis 10.
1, the second optical axis 11 is bent with respect to the axis 1o at a beam splitter 12 in a direction perpendicular to the axis 1o for interaction. As a result, both laser beams utilize a common axis of therapeutic energy delivery 13, and in the manner shown, the therapeutic energy delivery uses an interference filter 14 to bend the laser energy projected onto the delivery axis 15. . The emitted energy, in the form of a parallel beam, impinges on the biological tissue to be irradiated with a circular or otherwise shaped spot; alternatively, as shown by the converging lens means 16, the laser energy
It is focused into a small area for coupling to a fiber optic delivery system 17, such as when using an endoscope.

Each of the lasers A, B is preferably of very low power in the visible red or infrared, in terms of the energy delivered to the living tissue and thus to avoid local heating and coagulation of the tissue and/or cells. Occur. Suitable and moderately priced helium-neon, krypton, and diode lasers are available for this purpose, and the mode of use will determine the particular choice.

Furthermore, to facilitate the particular desired mode of use, the optical elements on the shaft 10 include attenuator means 20 (which is selectively variable), shutter means 21 (which is mechanically and electromagnetically driven, or electro-optically and electronically driven), a beam stretcher 22 (with manual means 23 for adjusting the expansion), a field adjustment device 24, and a beam displacement optic 25 (as indicated by the double-headed arrow). , with its adjustable slope with respect to ITol 0)
including. Similarly, the optical element on the axis 11 is connected to the attenuator means 3
0, shutter means 31, beam expander 32 (adjustment means 3
3), a field adjustment device 34, and an adjustable tilt beam displacement optical element 35; in addition, the optical elements on axis 11 (with lasers A and B being identical)
and means 37 for selective angular shifting of the polarization from one of the beams 10-11 to the other. A suitable polarization rotator manufactured by New Boat Co., Ltd. is available with catalog number R for the visible spectrum.
P-550 or near infrared (700-120
0 nm) by catalog number RP-950.

To complete the description of the components shown in FIG. 1, the area illumination system 40 maintains the light on the delivery axis 15 and projects the light through a reflector 41 and a beam splitter 42;
An observation device such as a stereoscopic observation microscope 43 has a straight line of sight along the tube 15. With the area adjustment device 24.34 adjusted to restrict their respective beams to the same circular cross-section, and with the two beam displacement optics 25.35 set to zero inclination! ! With these parallel planes perpendicular to their respective optical axes 10.11, the system described above delivers equal and coincident areas of radiation from both lasers A, B. On the other hand, if one of the area adjusters 24.34 were set to a larger beam-limiting cross-section than the other, the concentric overlapping radiation emitted from the two lasers would be as shown in FIG. That is,
Both lasers have a central region 44 that is both responsive, which is surrounded by a clasp 45 that is responsive to only one of the two lasers. The latter situation can be utilized in cases where a buffer zone 45 of slightly irradiated tissue is required between the central, maximally treated zone and the outer adjacent area of untreated tissue.

As stated above, it is generally the intent and purpose of the present invention to utilize a combination of the features shown to cause perturbations to affected tissue.
That is, effectively using the interaction between co-existing but dissimilar laser beams, whereby the growth of blood vessels etc. is promoted beyond that which can be achieved by radiation from a single laser. In the device described above, such differences are achieved by various combinations of one or more beams on axes 10 and 11 as follows.

A, using identical lasers A and B, for example two helium-neon lasers, with axis 10.1
1 is used.

(1) The combined output on the delivery shaft 15 is 2 at the same wavelength.
The phase shifter 36 is adjusted so that the sum of the two spatially and temporally coherent radiations is the same, but out of phase with each other.

(2) polarization rotation such that the combined output on the delivery axis 15 is the product of a predetermined difference in the direction of the plane of polarization for each of the two spatially and temporally coherent radiation of the same wavelength; Adjust the container 37.

(3) Beam 13a (15a) for laser A radiation
(10 each) are focused onto the treated tissue on the first axis 18a and the beam 13b (15b) for laser B radiation is focused onto the treated tissue on the first axis 18b. to 10' and from 11 to 11') to equal and opposite offset displacements of their respective axes.

(4) In a selected one of the above modes (1), (2), or (3), operate the shutter (chopper) synchronously according to the selected one of the following mode improvements.

(a) Open/close the shirt shutter in simultaneous synchronization with both axes 10.11.

(b) Shirt open/shutter closed in a time-intersecting relationship on each axis 10.11.

(c) The shirt flap is opened on one axis (lO), which overlaps in a cyclical manner, and the shirt flap is closed on the other axis (11).

(d) Recovery of affected cells during irradiation with a frequency of 15 Hz or less.

(e) Suppress the recovery of crushed cells during the treatment cycle at a cycle of 15 Hz or higher.

B. As lasers A and B, different lasers are used, for example, a helium neon laser on the shaft 10 and a krypton laser on the shaft 11.

(5) adjusting the attenuator 20 or 30 so that the beam intensity at one wavelength on one axis (1) is equal to or greater than the beam intensity at the other wavelength on the other axis (11); .

(6) polarization such that the combined output on the delivery axis 15 is the product of a predetermined difference in the direction of the plane of polarization for each of the two spatially and temporally coherent radiation of different wavelengths; Adjust the rotator 37.

(7) Beam 13a (15a) for laser A radiation is focused on the first axis 18a on the treated tissue, and beam 13b (15b) for laser B radiation is focused on the treated tissue on the first axis 18a; The beam displacement optics 25.35 are adjusted to equal and opposite offset displacements of their respective axes (from 10 to 10' and from 11 to 11', respectively) so that they are focused on the axis 18b of .

(8) In a selected one of modes (5), (6) or (7) above, operate the shutter (chopper) according to a selected one of the mode improvements mentioned in mode A (4) above. Works synchronously.

Whatever type of laser A or B is chosen, the combined intensity of the beam energy that can be delivered to the affected area of biological tissue is on the order of microwatts/C-, preferably between 100 and 150 microwatt/cm2
It is recommended that it be within the range of .

In the embodiment of FIG. 3, the output beam from a single laser 49 is split by a beam splitter 50 into beams 51, 52 on separate paths and then recombined by beam splitter means 53 onto a single axis 54 and filtered by an interference filter. At 55, it is bent to a delivery shaft 56. The means for operating on beam 52 are similar to those described for beam 10 from laser A in FIG. 1, and the means for operating on beam 51 are as described for beam 11 from laser B in FIG. It is similar to that. Like the illumination and viewing means, these means are therefore provided with the same reference symbols as in FIG. 1.

The single laser embodiment of FIG. 3 is essentially functionally equivalent to the same laser case described in connection with FIG. The differences occurring in the split beams 51, 52 of FIG. 3 therefore include those summarized under node A for the same laser on axes 10 and 11 of FIG.

For biological tissue applications, the multiple beam irradiation described here can be performed either directly as a parallel beam, where the aperture of the region conditioning device determines the size and shape of the delivered spot, or within fiber optics to a region of internal tissue. It is sent out through the endoscope.

For delivery into the eye 57, FIG. 4 shows the use of convergent optics 58 to extend the illumination to a relatively large area of the retina, and FIG. The use of contact lens element 59 in conjunction with convergent lens element 60 to provide the desired effect. Optical element 58 (or 5
The beam cross-sectional area delivered to
It can be seen that the area adjustment size limit is determined.

Inserted references are made for this purpose to equivalent choppers of shutters with electrical or electronic controls for their specific synchronized adjustment, and as such controls are well understood, they are not included here. I won't explain it. Time-interlaced chopping motion between two lasers of different characteristics delivered to biological tissue is accomplished by a rotating chopper with a flat mirror surface, which (1) directs one beam to the other; 45 so that the axis can be bent in line with the beam
(2) the mirror surface is interrupted to provide an open fan-shaped space for the unreflected direct delivery of said other beam to intersect with the reflected delivery of said one beam; FIG. In , such a mirror chopper is understood to be represented by a plane-parallel device inclined at 45'', implemented as beam splitter 12 in FIG. 1 or beam splitter 53 in FIG.

It can be seen that the effect of the reflectance in each of the interference filters, 14 (55), limited spectral width is dependent on the particular selected lasers A, B and 49.

Therefore, for helium neon and krypton lasers, the limited width of the interference filter reflectance is suitably 610
nm to 660 nm, thereby allowing area illumination (from 40 nm) and observation through the sufficient remainder of the visible spectrum (from 43 nm).

〔Effect of the invention〕

As is clear from the above description, according to the present invention, at least two laser beams are irradiated to the affected area of biological tissue, and the irradiation has a weak impact strength on the tissue, preferably visible red or infrared rays. Because it has a specific wavelength of , it is possible to increase the number of cells without causing photocoagulation, photon optical tissue decomposition, photoevaporation, or photoelimination decomposition.

[Brief explanation of the drawing]

1 is an optical diagram schematically showing the components of the device of the invention; FIG. 2 is an enlarged view showing an embodiment of beam delivery; FIG. 3 is a view similar to FIG. 1 showing a modification; Figures and Figure 5 are
4A and 3B are simplified partial optical diagrams of two different techniques of laser beam delivery for either the embodiment of FIG. 3 or FIG. DESCRIPTION OF SYMBOLS 10... First optical axis, 11... Second optical axis, 12.
...Beam splitter, 13...Common axis, 14...
Interference filter, 15... Delivery axis, 16... Converging lens means, 17... Fiber optics delivery system, 20... Attenuator means, 21... Shutter means,
22... Beam extender, 23... Manual means, 24...
...Area adjustment device, 25...Beam displacement optical element, 3
0... Attenuator means, 31... Shutter means, 32.
... Beam expander, 33... Manual means, 34... Area adjustment device, 35... Beam displacement optical element, 36...
- adjustable phase shifter means, 37... selective angle shifter means, 40... area illumination system, 41... folding reflector, 42... beam splitter, 43...
Three-dimensional observation biological microscope, 44... central area, 45...
Clamp ring, 49...Single laser, 50...Beam splitter, 51.52...Split beam, 53...
Beam splitter means, 54... single axis, 55...
Interference filter, 56... Sending axis, 57... Eye, 58
... Convergence optical element, 59 ... Contact lens element, 60 ... Convergence optical element. Engraving of drawings (no changes to the same content) FIG, 2゜FIG. Procedural amendment (method) % formula % Display of the case 1999 Patent Application No. 276163 Name of the invention Method and device for strengthening blood vessels and other tissue growth Person who makes the amendment Relationship to the case Patent applicant

Claims (1)

[Claims] 1. By irradiating a local area of biological tissue with a laser,
An apparatus for enhancing blood vessel or other tissue growth comprising laser means for outputting first and second output beams of the same wavelength and a beam splitter for combining said beams for aligned delivery to said localized region. and means operable to determine a phase shift of one of the beams with respect to the other. 2. The intensity of the beam energy that can be emitted to the region is on the order of microwatts/cm^2.
, 15, 16, 18, 19 or 24. 3. Apparatus according to any one of claims 1, 11, 15, 16, 18, 19 or 24, wherein said wavelength is at least 600 nanometers. 4. Said laser means comprises means comprising a laser producing a single output and a beam splitter for receiving said output and splitting said output into said first and second output beams. , 16, 18, or 19. 5. The laser means includes a first laser that outputs the first output beam at a first wavelength and a second laser that outputs the first output beam at a second wavelength.
and a second laser outputting an output beam of . 6. The laser means includes a laser outputting a single output and a beam splitter for receiving the output and splitting the output into the first and second output beams; 20. The apparatus of any one of claims 1, 15, 16, 18, or 19, wherein is a helium neon laser. 7. The laser means includes a laser outputting a single output and a beam splitter for receiving the output and splitting the output into the first and second output beams. 20. Apparatus according to any one of claims 1, 15, 16, 18 or 19, wherein the laser means is a krypton laser. 8. The laser means has means including a laser outputting a single output and a beam splitter for receiving the output and splitting the output into the first and second output beams, the laser means Claim 1 is a diode laser.
, 15, 16, 18, or 19. 9. The apparatus according to claim 5 or claim 11, wherein the first laser is a helium neon laser and the second laser is a krypton laser. 10. The apparatus of claim 5 or claim 11, wherein at least one of the lasers is a diode laser. 11. In a device for enhancing the growth of blood vessels and other tissues by irradiating a localized region of living tissue with a laser,
a first laser outputting the first output beam at a first wavelength; a second laser outputting the second output beam at a second wavelength; and aligned firing of the beam to the localized region. and means including a beam splitter for coupling. 12. The emission of energy in at least one of said beams is spatially and temporally coherent.
, 15, 16, 18, 19 or 24. 13. The energy delivery of each of said beams is spatially and temporally coherent.
6, 18, 19 or 24. 14. The energy launches of each beam are on separate straight lines that converge to substantially intersect and overlap in the local region.
A device according to any one of the following. 15. In a device for enhancing the growth of blood vessels and other tissues by irradiating a localized region of living tissue with a laser,
laser means for outputting first and second output beams of the same wavelength; and means including a beam splitter for combining said beams for aligned delivery to said local region; and operating one of said beams in relation to the other. and means for determining a polarization shift of one of said beams relative to the other. 16. In a device for enhancing the growth of blood vessels and other tissues by irradiating a localized region of living tissue with a laser,
laser means for outputting first and second output beams of the same wavelength; and means including a beam splitter for combining said beams for aligned delivery to said local region; and operating one of said beams in relation to the other. and means for determining an intensity difference relative to one of said beams. 17. A device according to any one of claims 1, 15 or 16, wherein said last specified means are selectively adjustable. 18. In a device for enhancing the growth of blood vessels and other tissues by irradiating a localized region of living tissue with a laser,
means including laser means for outputting first and second output beams of the same wavelength; a beam splitter for combining said beams for matched delivery to said local region; and at least one of said beams before being incident on said beam splitter. Apparatus having means including an operable chopper on one side. 19. In a device for enhancing the growth of blood vessels and other tissues by irradiating a localized region of living tissue with a laser,
means including laser means for outputting first and second output beams of the same wavelength; and means including a beam splitter for combining said beams for coherent delivery to said local region; Apparatus having means including operable synchronized first and second choppers. 20. The apparatus of claim 19, wherein the chopper is an electro-optic chopper. 21. The apparatus of claim 19, wherein the chopper is operable to the beam in a phase-combined relationship. 22. The apparatus of claim 19, wherein the chopper is operable to the beam in phase. 23. The apparatus of claim 19, wherein the chopper is operable to the beams in phase-offset but at least partially overlapping relationship. 24. In an apparatus for enhancing blood vessel or other tissue growth by irradiating a localized region of biological tissue with a laser, a first laser outputting the first output beam at a first wavelength;
means including a second laser outputting said second output beam at a second wavelength; and a rotatable chopper having a mirror surface for coupling said beam to said region for matched combination of their firing. A device with 25. The apparatus of claim 5 or 11, wherein each of said wavelengths is at least 600 nanometers. 26. The intensity of the beam energy that can be delivered to said region is in the range of 100-150 microwatts/cm^2, the wavelength of each of said beams is at least 600 nanometers, and in addition to said beam splitter, said alignment The means for launching includes a dichroic mirror with substantially matched reflectance for beam wavelength limitation, whereby via said dichroic mirror, an axis for observing said area and an observation optical system on said axis are connected. Claim 1 establishing
, 11, 15, 16, 18, 19, and 24. 27. Any one of claims 1, 11, 15, 16, 18, 19, and 24, wherein the intensity of the beam energy that can be delivered to the region is in the range of 100 to 150 microwatts/cm^2. The device described in. 28. A method for enhancing or promoting the growth of blood vessels or other tissue in a living body, the method comprising: emitting two beams of low power laser radiation to impact the same area of the living tissue, said beams comprising at least one The combined intensity is at least sufficient to therapeutically affect the biological tissue and/or cells bombarded by the beam, but the combined intensity is at least sufficiently therapeutic to affect the tissue and/or cell photocoagulation, photoevaporation, photon A method that is weak enough not to cause optical tissue destruction or photoremoval decomposition. 29. The method of claim 28, wherein the intensity of the beam energy delivery to the area where the biological tissue is impacted is on the order of microwatts/cm^2. 30. The intensity of the beam energy emitted to the area where biological tissue is impacted is 100 to 150 microwatts/cm^
29. The method according to claim 28. 31. The method of claim 28, wherein the wavelength of the laser radiation is at least 600 nanometers. 32. The method of claim 28, wherein the beams have the same wavelength but impact the region from mutually different convergence directions. 33. The method of claim 28, wherein the beams have the same wavelength but are offset from each other. 34. The method of claim 28, wherein the beams are polarized in mutually offset planes. 35. The method of claim 28, wherein one of the beams impacts biological tissue over an area that is substantially greater than the area of impact by the other beam. 36. The method of claim 28, wherein the beams have different wavelengths. 37. The method of claim 28, wherein the beam is chopped and varied.