preferred embodiments of this invention will be described hereunder with reference to the accompanying drawings . fig3 is a schematic view of a first embodiment of the laser beam generating device used in a cancer diagnosis and treatment device according to this invention . as shown in fig3 the laser beam generating device according to this embodiment comprises a solid - state laser generator 60 for emitting a monochromatic laser beam , a laser - wavelength varying unit 61 for converting the laser beam emitted from the solid - state laser generator 60 to two laser beams having desired wavelengths suitable for cancer diagnosis and treatment , and a dichroic filter 62 for separating the laser beams having the desired wavelengths , which are used for cancer diagnosis and treatment , respectively . in this embodiment , the solid - state laser generator 60 is substituted for the excimer laser generator used in the conventional laser beam generating device because the solid - state laser generator can carry out a more stable oscillating operation for a long time and requires no exchange of laser gas ( in this point , the excimer laser generator requires exchange of laser gas ). as described hereinafter , the laser - wavelength varying unit 61 may have various constructions in accordance with the kind of the solid - state laser generator 60 and / or the kind of photosensitive material to be injected into the vein of the patient . fig4 shows a concrete construction of the laser beam generating device as shown in fig3 . in this embodiment , the photosensitive material and the solid - state laser generator 30 are specified to hpd and a nd - yag laser generator for emitting a monochromatic laser beam having a wavelength of 1064 nm , respectively . further , the laser - wavelength varying unit 61 of this embodiment comprises a first harmonic generator 31 and an optical parametric oscillator 32 . the harmonic generator 31 includes a potassium dihydrogen phosphate ( kdp ) crystal , and produces laser beams having higher harmonics along with a fundamental laser beam incident thereto . the optical parametric oscillator 32 includes a collimator lens 32a , two mirrors 32b and 32c and a nonlinear optical crystal such as β - bab 2 o 4 ( bbo ) disposed between the mirrors 32b and 32c and generates two coherent beams whose wavelengths can be varied continuously over a broad range in accordance with the change in an incident angle of a laser beam to the surface of the crystal when pumped by the incident laser beam . an operation of producing two laser beams having different wavelengths suitable for cancer diagnosis and treatment will be described hereunder . as shown in fig4 the laser beam emitted from the nd - yag laser generator 30 is incident to the harmonic generator 31 to output therethrough three harmonic laser beams of 355 nm ( third harmonic laser beam ), 532 nm ( second harmonic laser beam ) and 1064 nm ( fundamental laser beam ). of these laser beams , only the third harmonic laser beam of 355 nm is extracted by means of a prism ( not shown ). the third harmonic laser beam of 355 nm is irradiated as a pump wave to the optical parametric oscillator 32 to output two laser beams having different wavelengths ( 630 and 813 nm ) different from the wavelength of the pump wave . as described above , the wavelengths of the output laser beams from the optical parametric oscillator 32 are variable by changing an incident angle of the pump wave to the surface of the nonlinear optical crystal . for example , when the pump wave ( the laser beam of 355 nm ) is incident to the optical parametric oscillator 32 in such a manner that an intersecting angle ( θ ) between an incident direction of the pump wave and an optical axis ( c - axis ) of the bbo crystal is equal to 32 . 7 °, the output laser beams have wavelengths of 630 nm and 813 nm . the angleθ may be varied in a range of - 0 . 5 to 0 . 5 ° in accordance with the kind of the nonlinear optical crystal . the output laser beams from the optical parametric oscillator 32 are separated from each other through a dichroic filter 33 the laser beam of 630 nm is directly guided as a treating laser beam through a convergent lens 34 and an optical fiber 35 to the cancer focus 21a , while the laser beam of 813 nm is reflected from a reflector 36a to a second harmonic generator 36 comprising kdp crystal to output only a second harmonic laser beam ( 407 nm ) of the incident laser beam thereto and then the laser beam of 407 nm is guided as a diagnostic laser beam through a convergent lens 37 and an optical fiber 38 to the malignant tissue 21 . in the above embodiment , the laser beams obtained by the optical parametric oscillator 32 are separately guided through the individual focusing lens 34 and 37 and the individual optical fibers 35 and 38 , respectively . however , as shown in fig5 by switching both laser beams emitted from the optical parametric oscillator 32 to each other with a change - over unit 29 , these laser beams may be selectively guided through one converging lens and one optical fiber to the malignant tissue 21 . photosensitive materials other than hpd ( or dhe ( dihematoporphyrin ether / ester )), such as ph - 1126 , npe6 , phthalocyanine and other materials , can not be used in the cancer diagnosis and treatment device of the above embodiment because the wavelength ( 630 nm ) of the treating laser beam originated from the nd - yag laser generator is the absorption wavelength inherent to hpd ( dhe ) and the nd - yag laser generator generates a monochromatic laser beam which is used to produce only the laser beams of 405 nm and 630 nm for cancer diagnosis and treatment with hpd ( dhe ). that is , the photosensitive materials as described above have different absorption wavelengths for cancer treatment from that of hpd ( dhe ), and thus the photosensitive materials other than hpd ( dhe ) have no sensitivity to the laser beam of 630 nm . for example , the absorption wavelengths of hpd ( dhe ), ph - 1126 , npe6 and phthalocyanine for cancer treatment are 630 nm , 650 nm , 660 nm and 680 nm , respectively . on the other hand , the absorption wavelengths of these photosensitive materials for cancer diagnosis are substantially equal to one another ( 405 nm ). a manner of preparing hpd and chemical structures of the other photosensitive materials are described below . this photosensitive material is prepared by dissolving hematoporphyrin hydrochloride ( a mixture of twenty and several kinds of porphyrins ) in a mixture of sulfuric acid and acetic acid and keeping it at ph 7 . 4 . the absorption wavelength of this photosensitive material for cancer treatment is 630 nm . dhe ( dihematoporphyrin ether / ester ) is obtained by extracting only active ingredients from hpd , and has the substantially same optical characteristic as hpd . ## str1 ## aluminum phthalocyanine is also used as a photosensitive material having affinity to cancer , and is formed by substituting zinc metal located in the center of the above chemical structure by aluminum . this material , has the substantially same optical characteristic as zinc phthalocyanine . as described above , the wavelength of a laser beam emitted from the solid - state laser generator of the above embodiment is fixedly set to 630 nm , and therefore only the specific photosensitive material such as hpd or dhe is used as cancer diagnosis and treatment . accordingly , in the above embodiment , if a kind of photosensitive material is required to be changed to another kind of photosensitive material a solid - state laser generator which has been used must be exchanged to another one in order to obtain a laser beam suitable for the new photosensitive material . however , the following embodiment of the cancer diagnosis and treatment device can perform cancer diagnosis and treatment without exchanging a solid - state laser generator to another solid - state laser generator even though the kind of photosensitive material is changed . fig6 is a schematic view of a second embodiment of the laser beam generating device used in the cancer diagnosis and treatment device according to this invention . as shown in fig6 the laser beam generating device according to this embodiment comprises a solid - state laser generator 63 capable of performing a laser oscillation in a broad wavelength range to generate a laser beam whose wavelength is variable over the broad wavelength range , a laser - wavelength varying unit 64 for converting an incident laser beam thereto to two laser beams having desired wavelengths different from that of the incident laser beam , a control unit 65 for controlling the solid - state laser generator 63 to select one of the laser beams having various wavelengths in the broad wavelength range and emit the selected laser beam to the laser - wavelength varying unit 64 and for controlling the laser - wavelength varying unit 64 to adjust an incident angle of the laser beam to the laser - wavelength varying unit 64 , whereby two laser beams having desired wavelengths in accordance with the change of the wavelength of the selected laser beam are outputted from the laser - wavelength varying unit 64 , and a dichroic filter 66 for separating the laser beams having the desired wavelengths , which are used for cancer diagnosis and treatment , respectively . as solid - state laser generators capable of emitting laser beams having various wavelengths in a broad wavelength range , an alexandrite ( cr 3 + : beal 2 o 4 ) laser capable of generating a laser beam having a wavelength of 700 to 830 nm , or a titanium sapphire ( ti 3 + : a1 2 o 3 ) laser capable of generating a laser beam having a wavelength of 680 to 900 nm may be used . fig7 shows a concrete construction of the laser beam generating device as shown in fig6 . the laser beam generating device of this embodiment has the substantially same construction as that of fig4 except that the solid - state laser generator 63 of this embodiment can generate a laser beam whose wavelength is selectively changeable in a broad range ( nd - yag laser generates a monochromatic laser beam having a fixed wavelength ) and the control unit for controlling both of the solid - state laser generator and the laser - wavelength varying unit 64 newly provided . the solid - state laser generator 40 of this embodiment includes a laser selecting member 67 such as a movable prism , by which a laser beam having a desired wavelength within the broad wavelength range is selectively outputted from the laser generator 40 to a harmonic generator 41 . like the laser beam generating device as shown in fig4 the laser - wavelength varying unit 64 of this embodiment includes a first harmonic generator 41 comprising kdp crystal , and an optical parametric oscillator 42 comprising a collimator lens 43 , two mirrors 44 and 45 and a nonlinear optical crystal 46 such as bbo or lbo disposed between the mirrors 44 and 45 . however , unlike the laser beam generating device as shown in fig4 the first harmonic generator 41 of this embodiment outputs only a second harmonic laser to the optical parametric oscillator 42 , and the optical parametric oscillator 42 of this embodiment further includes a rotating member 68 such as a motor for rotating the nonlinear crystal 46 to change an incident angle of a laser beam emitted from the harmonic generator 41 to the surface of the crystal 46 . the selecting member 67 and the rotating member 68 are controlled by the control unit 65 to selectively output the laser beam having the desired wavelength from the solid - state laser generator 40 and set the incident angle of the laser beam to the nonlinear optical crystal 46 to a predetermined angle . the control unit 65 comprises , for example , a mechanical member or a microcomputer to which an information on the kind of a photosensitive material to be used is inputted . the laser beam having wavelength of λ 0 emitted from the solid - state laser generator 40 is incident to the first harmonic generator 41 to obtain a second harmonic laser beam having wavelength of λ 0 / 2 , and then the second harmonic laser is incident to the nonlinear optical crystal 46 of the parametric oscillator 42 . the nonlinear optical crystal 46 of the optical parametric oscillator 42 is rotated by the rotating member 68 to change an incident angle θ of the second harmonic laser to the crystal 46 and the optical parametric oscillator 42 outputs two laser beams having desired wavelengths of λ 1 and λ 2 on the basis of the incident second harmonic laser beam . these laser beams outputted from the optical parametric oscillator 42 are separated from each other by a dichroic filter 47 . one laser beam having wavelength of λ 1 is converged through a convergent lens 48 to an optical fiber 49 and is used as a treating laser beam , while the other laser beam having wavelength of λ 2 is reflected from a reflector 50 to a second harmonic generator 51 comprising kdp crystal to obtain a second harmonic laser beam having wavelength of λ 2 / 2 . the second harmonic laser beam thus obtained is converged through a convergent lens 52 to another optical fiber 53 and is used as a diagnostic laser beam . as described above , by switching both laser beams emitted from the optical parametric oscillator 42 to each other with a change - over unit as shown in fig5 these laser beans may be selectively guided through one converging lens and one optical fiber to the malignant tissue 21 . an operation of adjusting the wavelengths of the diagnostic and treating laser beams in accordance with the kind of the photosensitive material will be described below . the following equation shows a relationship between the wavelength ( λ 0 / 2 ) of the incident laser beam to the nonlinear optical crystal 46 and the wavelengths ( λ 1 and λ 2 ) of two laser beams outputted therefrom . as described above , it is not necessary to change the wavelength of the diagnostic laser beam ( λ 2 / 2 ) in accordance with the kind of the photosensitive material to be used because the absorption wavelength of each photosensitive material for the diagnostic laser beam is broad and thus the fixed wavelength of 405 nm ( or 407 nm ) can be used for every photosensitive material irrespective of the kind thereof . accordingly , the wavelength of λ 2 may be fixed in the above equation . on the other hand , as the incident angle of the laser beam to the nonlinear optical crystal is increased , the wavelengths ( λ 1 and λ 2 ) of the laser beams outputted from the parametric oscillator are changed in such a manner as to be approached to each other insofar as the wavelength of the incident laser beam is not changed . in addition , the relationship represented by the above equation is not changed irrespective of the change of the incident angle of the laser beam to the nonlinear optical crystal . accordingly , if the wavelength ( λ 2 ) of one of the output laser beams is fixed and the above equation is satisfied , in other words , if the wavelength ( λ 1 of the treating laser beam is changed while the wavelength ( λ 2 ) of the diagnostic laser beam is kept constant , as is apparent from the above equation , it is required to change the wavelength ( λ 0 ) of the incident laser beam to the parametric oscillator 42 . as described above , the wavelength of the laser beam emitted from the solid - state laser generator 40 is variable over the broad wavelength range by the selecting member 67 , and thus the wavelength of the incident laser beam to the parametric oscillator 42 can be changed over the broad wavelength range ( for example , λ 0 / 2 : 350 to 415 nm for the alexandrite laser generator and 340 to 450 nm for the titanium sapphire laser generator ). that is , the solid - state laser beam generator used in this embodiment satisfies the above requirement . the wavelength λ 0 of the laser beam to be selected in the solid - state laser generator 40 is determined by calculating the above equation under the condition that λ 2 is constant ( that is , λ 2 / 2 is constantly equal to 405 nm ) and λ 1 is the absorption wavelength for cancer treatment when each photosensitive material is used . assuming that bbo crystal having a lattice constant as shown in fig8 ( a = b = 12 . 532a and c = 12 . 717a , α = 90 ° and β = 120 °) is used as the nonlinear optical crystal , the wavelength ( λ 0 ) for each photosensitive material is obtained as follows . in the following calculation , θ and φ represent intersecting angles between the incident direction of the laser beam and the c - axis of the crystal and between the incident direction and the a - axis of the crystal , respectively , and φ is 0 ° when bbo crystal is used . accordingly , when hpd or dhe is used as a photosensitive material , a laser beam of 709 nm is selected by the selecting member . further , in order to obtain the output laser beams of 630 nm and 810 nm , the incident angle of the laser beam ( the intersecting angle θ between the incident direction and the c - axis of the crystal ) may be set to 32 . 7 °. the following table shows the absorption wavelengths of the above photosensitive materials to the diagnostic and treating laser beams , the incident angles of the laser beams to obtain these laser beams and the selected wavelengths of the laser beams to be emitted from the solid - state laser generator 40 . table______________________________________photosensitive λ . sub . 0 λ . sub . 0 / 2 θ λ . sub . 1 λ . sub . 2 λ . sub . 2 / 2material ( nm ) ( nm ) ( degree ) ( nm ) ( nm ) ( nm ) ______________________________________hpd ( or dhe ) 709 354 32 . 7 630 810 405ph - 1126 721 361 32 . 2 650 810 405npe6 727 364 31 . 9 660 810 405phthalocyanine 739 370 31 . 4 680 810 405______________________________________ in the above embodiment , the wavelength of the diagnostic laser beam is constantly fixed for any photosensitive material , however , may be changed to a desired wavelength to accurately match the wavelength with a peak of absorption spectrum of the photosensitive material to be used . as described above , according to the cancer diagnosis and treatment device having a laser beam generating device of this invention , a laser oscillation is stably carried out for a long time and it is not required to exchange laser gas to new one . further , the wavelengths of the laser beams for cancer diagnostic and treatment can be freely changed by a simple adjustment operation of the solid - state laser generator and the laser - wavelength varying unit , and therefore any photosensitive materials can be used in the cancer diagnosis and treatment device without changing the kind of the laser beam generator even though the absorption spectra of the photosensitive materials are different . accordingly , the diagnostic and treating procedures of cancer are smoothly and easily carried out .
a cancer diagnosis and treatment device comprising a solid - state laser generator such as an nd - yag laser , an alexandrite laser , or titanium sapphire laser for emitting a first laser beam having a first wavelength , a harmonic generator for generating higher harmonic laser beams of the first laser beam and outputting one of the higher harmonic laser beams , and an optical parametric oscillator for converting the harmonic laser beam outputted from the harmonic generator into second and third laser beams suitable for the cancer diagnosis and treatment , the second laser beam having a second wavelength stimulating a sterilizing photochemical reaction between the photosensitive material and the cancer foci to perform the cancer treatment and the third laser beam having a third wavelength inducing fluorescence inherent to the photosensitive material to enable the cancer diagnosis , an endoscope for guiding the second and third laser beams emitted from the laser beam source to the cancer foci and transmitting an image of the fluorescence of the photosensitive material to an outside of the body , and a cancer observing unit having a screen for receiving the image of the fluorescence of the photosensitive material al transmitted through the endoscope unit and displaying the image on the screen to thereby perform the cancer diagnosis .