text: fig1 is a longitudinal sectional view of a probe 10 according to the present invention which is mounted at the terminal or output end portion of a laser optical waveguide fiber 32 . probe 10 is made of a laser transmissive material such as a natural or artificial ceramic material , for example , sapphire , quartz , or diamond . polymeric materials may also be employed . in the embodiment as illustrated , the probe 10 comprises a conically tapered laser diffusing portion 12 having , at the tip end thereof , a semispherical portion 12a and a main body portion 14 . the laser diffusing portion 12 and the main body portion 14 are formed integrally with each other and a flange 16 is formed between the laser diffusing portion 12 and the main body portion 14 . the probe 10 is fitted in a cylindrical female connector 18 and fixed integrally thereto by caulking the mating surfaces thereof or using a ceramic type adhesive between the mating surfaces . the female connector 18 has , on the internal surface thereof , a thread 20 which is adapted to mate with complementary threads 30 of a male connector 22 . the female connector 18 has two holes 24 through the cylindrical connector wall which facilitate the passage of cooling water w or other fluids therethrough . the two holes are circumferentially disposed at angular spaces of 180 ° although only one of them is shown in fig1 . on the other hand , the male connector 22 is pressedly fitted into a flexible tube of jacket 26 fabricated of , for example , teflon ( trademark ). for this press fitting , the male connector 22 has stepped portions 28 at the base portion of the male connector 22 by which the male connector 22 is firmly held within jacket 26 so as to prevent the former from being disengaged from the latter . as noted , male connector 22 is externally threaded at 30 to mate with the internal thread 20 of the female connector 18 . an optical fiber 32 for transmitting the laser beam is inserted in the male connector 22 . the optical fiber 32 is disposed concentrically within the jacket 26 , leaving a gap 34 therebetween for passage of cooling water or other fluids . although the fiber 32 is closely fitted in the male connector 22 adjacent the stepped portion of the male connector , the stepped portion 28 has for example two slits 28a formed circumferentially at angular spaces of 180 ° for letting the cooling water w pass therethrough . a passage 36 for the cooling water w is further provided between the inner face of the tip end portion of the male connector 22 and the optical fiber 32 . the assembled tip may then be inserted into an endoscope or otherwise positioned as required for the laser surgical procedure to be performed . the fiber 32 is optically connected to a laser generating unit ( not shown ). according to necessity , cooling water w is fed through the gap 34 ; slit 28a ; passage 36 then , in turn , discharged through the opening 24 to cool the tissue to be treated . the laser beam from the laser generating unit is guided through the optical fiber 32 and coupled from the end thereof into the base 38 of probe 10 . the laser beam is thereafter emitted , as discussed in more detail below , from the diffusing portion 12 of the tip to the tissue m to be treated . fig2 illustrates the dispersion and diffusion of laser beam when the probe of the present invention is employed . as will be described later , the outer surface of the laser diffusing portion 12 of the probe 10 is frosted or roughened , thereby widely dispersing the laser energy as illustrated in fig2 . fig6 best illustrates the comparative radiation energy densities between a prior art probe tip and the probe tip of the present invention . probe 10 &# 39 ; represents both the present and prior art laser tips when viewing the solid 21 , 23 and dotted 13 , 17 line curves , respectively . curve 13 represents the laser energy or power density distribution in a plane spaced below the probe tip and perpendicular to the longitudinal axis thereof . more specifically , the power density is shown to be greatest at 15 , a point along the extended longitudinal axis of the probe tip , and to diminish rapidly as the distance from this axis is increased . curve 17 very roughly approximates the laser power density distribution in a cylindrical surface surrounding the probe and having a common axis thereto . this curve essentially depicts the radial component of laser radiation which , as can be seen , is extremely low in a conventional tip due to the fact that substantially all of the laser energy is radiated longitudinally downwardly from tip 12a &# 39 ;. curve 17 , therefore , is merely intended to depict this low level of radial radiation rather than to accurately illustrate the actual power distribution . curves 19 and 21 represent the laser power density distributions for the probe of the present invention corresponding , respectively , to prior art probe curves 13 and 17 . as can be seen from curve 19 , the peak power density 23 along the probe center axis is substantially lower than that of the prior art tip and , importantly , the power density drops less rapidly as a function of distance from this axis . this produces a broad area of relatively uniform laser illumination while simultaneously avoiding the excessive on - axis power densities which result in tissue charring . curve 21 reveals that substantial laser energy is emitted radially from the probe of the present invention and , further , that such radiation is not limited to the tip region 12a &# 39 ;, but occurs along the entire length of the conical diffusing portion 12 &# 39 ; of the probe . however , as discussed in more detail below , the laser power distribution depicted by curve 21 is , in reality , achieved by the random refraction and scattering of laser energy within the probe tip and , therefore , this radiation , while illuminating tissue along the side of the tip , is not necessarily emitted radially therefrom . as best shown in fig3 and 4 , the outer surface of the laser diffusing portion 12 is frosted or roughened to form an uneven , pseudo - random contour defined by generally convex protuberances and concave recesses . the surface irregularity or recess depth is between about 1 to 100 μm , preferably 10 to 60 μm . the frosting or roughening process is preferably carried out by use of a computer controlled grinding wheel . more specifically , the probe undergoing surface treatment is rotated and then brought into contact with a diamond grindstone . the grindstone traces the unroughened contour of the probe , commencing from the tip 12a of the probe , as far rearward along the conical surface as desired to define the diffusing portion 12 thereof . the computer controls , in a conventional manner , the position and speed of travel of the grindstone . in one preferred arrangement , a grindstone having particles of between 10 and 20 μm is utilized while the grindstone is moved along the probe between 3 and 6 mm / second . a roughened surface condition defined by approximately 10 μm recesses results . it will be appreciated that the depth of the recesses may be varied by utilizing grindstones of appropriate diamond particle size . however , as the recess depth is lowered , particularly below the preferred range set forth above , increasing percentage of the laser energy will be internally reflected within the probe tip thereby resulting in a correspondingly lesser amount laser energy being refracted and diffused radially outwardly . such a tip will not exhibit the desired broad and uniform radiation patterns . as the other extreme , increasing the surface roughness beyond the preferred limits results in the tissue becoming entangled in the concaved recesses when the probe is inserted into the tissue thereby inhibiting withdrawal of the probe . operation of the present probe can best be understood with reference to fig4 where the laser beam coupled into the probe from the optic guide is shown to be internally impinging the roughened surface 12b of the probe tip . this laser energy is illustrated by rays 31 and 33 . it will be noted that these rays do not arrive in parallel relationship , but rather , impinge from differing angles representative of the fact that each has travelled its own independent path including , in the general case , having undergone unpredictable internal reflections from the irregular surface thereabove . depending upon both the incident angle and the specific point of intersection of the incoming ray with the roughened surface 12b , the ray is either reflected internally , to again strike the surface 12b , or refracted externally to radiate from the probe . in the general case , the laser energy may , in fact , split ; that is , some energy is reflected while the rest is refracted and radiated . fig4 depicts several representative ray tracks illustrating complete reflection , complete refraction , and a combination of both modes . it is significant that the laser energy radiated from the probe is not directed in any particular direction , but rather , radiates in virtually all directions . in this manner , laser energy is emitted radially from the probe and , unlike conventional laser probes , can penetrate tissue lying radially adjacent the probe tip . it is , in short , this pseudo - random scattering or diffusing of laser energy which accounts for the significant radiation along the probe tip as depicted at 21 in fig6 . fig7 shows typical dimensions of one embodiment of the present probe . it will be appreciated that these dimensions are merely illustrative and the probe may advantageously be dimensioned according to specific treatment requirements . for example , the length of the laser diffusing portion 12 of the probe 10 may be suitably selected according to the insertion depth of the probe into the tissue m and it may in general be within a range of about 1 . 0 to 7 . 0 mm . although the tip end of the laser diffusing portion 12 is not always required to be in semispherical shape , a pointed end would possibly be broken and therefore the tip end of the laser diffusing portion is preferably rounded . in the embodiment described above , substantially the entire conically tapered portion function to diffuse laser energy therefrom . alternatively , any limited or fractional portion of this conical section , including the tip end 12a , may serve as a laser diffusing portion by correspondingly restricting the degree of surface roughness . the flange 16 as described before functions as an abutment or stop for positioning of the probe 10 in the tissue m when the probe 10 is injected into the tissue m until the forward end face of the projected flange 16 abuts against the tissue m . however , the flange 16 may of course be omitted as the case may be . fig9 and 10 illustrate a further embodiment of the present invention in which a particulate diffusing layer 112 is applied and bound to the smooth outer surface 114 of a conical probe tip 116 , preferably sapphire . the particulate layer comprises a plurality of irregularly shaped particles 118 of a laser transmissive material bonded to the probe tip 116 by a ceramic bonding agent 120 . preferably particles 118 of the diffusing layer 112 will be diamond due to the high refractive index thereof . thus , where the diffusing particles are diamond and the probe tip is sapphire substantial laser energy , which would otherwise be reflected internally at the sapphire / air interface , is coupled from the probe tip 116 , that is , refracted into a diamond particle of the diffusing layer 112 , in turn , being radiated randomly therefrom as shown in fig1 . it will be understood that diffusing particles 118 having a refractive index less than that of diamond , but preferably still relatively high ( e . g . sapphire , quartz , etc . ), may be used by reason that the laser energy impinging the probe / diffusing layer interface 122 will , with greater probability , be refracted into the diffusing layer . this is due to the fact that the lowered ratio of refractive indices of the two adjoining materials will favor refraction at incident angles where ( absent a diffusing portion ) internal reflection would normally occur . it is preferred that , in general , the size of the diffusing particles 118 be at least about equal to one half the wavelength of the laser energy produced by the laser employed ; in the case of the nd : yag laser , wavelength is about 1060 nm . in a further of its aspects , the invention is a method of making a probe having a laser diffusing particulate layer 112 bonded to a probe tip 116 . although , as mentioned above , both the probe tip and the particulate layer may be made of any of several laser transmissive materials , which may have the same or different refractive indices , the preferred embodiment of such a probe comprises a sapphire probe tip and a diamond particle diffusing layer . hereinafter , reference may therefore be made to the sapphire probe tip and the diamond particle diffusing layer ; and it should be understood that other combinations of materials could be employed for the probe tip 116 and the diffusing particles 118 of the diffusing layer 112 . in the probe of the invention , comprising a diamond particle layer 112 , the diamond particles 118 are held in laser transmissive communication with the probe tip 116 by a ceramic material 120 . powdered ceramic materials which when heated to a high temperature bind sapphire and diamond , for example , are well known in the art . the ceramic powder ( i . e . the ceramic bonding agent 120 before being exposed to thermal cycling ) and diffusing particles 118 are admixed in a ratio appropriate to result , after the ceramic 120 is baked onto the probe , in a diffusing layer 112 , wherein the diffusing particles are tightly adherent to the probe tip and in laser - transmitting communication therewith . to make a probe of the invention having a refractive particulate diffusing layer , a slurry is made by mixing suitably sized refractive particles , generally in the range of about 0 . 5 μm to about 50 μm , with a ceramic powder which will bind the diffusing particles to the probe tip , in the presence of a suitable ceramic binder , such as a cellulose ester based binder , which binder will be substantially completely volatilized during the heating step causing , in turn , the particulate containing ceramic to bind to the probe tip . the slurry is applied and baked onto the probe tip at high temperature as described in detail immediately below . a preferred method for making a sapphire probe of the invention having a diamond particle diffusing layer is performed as follows : a slurry is made by mixing 0 . 04 g of natural diamond powder ( average size 1 - 3 μm ), 0 . 04 g ceramic powder ( 83 . 5 % silicone oxide ; 1 % potassium ; 15 . 5 % lead oxide ), 0 . 17 g ceramic binder ( astro - met associates , inc ., woodlawn , ohio ; product no . 3 . 0 %- 228 - 97 ) and 0 . 025 g distilled h 2 o . although this slurry composition is preferred , varying the ratio of diamond particles to ceramic powder from a ratio of about 3 : 1 to about 1 : 3 is within the scope of the invention . the slurry is applied by clasping the sapphire probe with a device adapted to hold the probe , with the tip 116 exposed in such a way that the probe and clasping device may be rotated very slowly about a horizontal axis , while the slurry is applied to the probe tip , for example , using a drill revolving at a very low speed . the slurry is worked onto the slowly - revolving probe tip with a very fine tipped paint brush or other instrument , until a thin , even coat is achieved , as determined with the aid of a low power objective ( e . g ., ˜ 10 × magnification ). the slurry is applied to a sapphire probe tip 116 along that portion of the outer surface 114 of the probe where laser emission is desired , and allowed to air dry . the diamond particles 118 are caused to adhere to the probe during a thermal cycle , wherein the air - dried , slurry - coated probe is heated in an oven to a temperature sufficient to melt the ceramic powder , which allows said ceramic 120 to flow into the interstices between the diamond particles . upon cooling , the ceramic material 120 hardens and causes the diamond particles 118 to adhere to the surface of the sapphire probe tip 116 . during the cycle , the oven is heated at a stepped - rate of 2 . 7 ° f ./ min from 70 ° to 1475 ° f . ( 8 . 7 hrs ) and held at 1475 ° f . for 20 min , before it is cooled back to 70 ° by steps of 2 . 7 ° f ./ min . thus , a full thermal cycle takes approximately 173 / 4 hours . in an alternative method for making the particle - coated probes of the invention , the probe is coated with a thin layer of a low viscosity cyanoacrylate ester ( e . g ., formula no . 18014 ; loctite corp ., newington , conn . 06111 ) or similar adhesive . a low viscosity adhesive allows a very thin layer of diamond particles to be coated onto the probe tip 116 . 0 . 04 g of natural diamond powder ( average size 1 - 3 μm ) and 0 . 04 g ceramic powder ( 83 . 5 % silicone oxide ; 1 % potassium ; 15 . 5 % lead oxide ) are admixed and applied to the probe as it is slowly rotated horizontally about its axis . the admixed powders can be applied for example by sprinkling or sifting or by blowing them onto the probe tip 116 with air pressure . because the cyanoacrylate dries quickly , the application of the mixture will be time - sensitive . the so - treated probes are heated using the same thermal cycling protocol as described above . the cyanoacrylate ester substantially vaporizes in the heating process , leaving the diamond particles 118 bound by the ceramic material 120 to the surface of the probe tip . operation of the probe comprising a diamond or other highly refractive particulate diffusing layer 112 can best be understood with reference to fig1 where the laser beam coupled into the probe from the optic guide is shown to be internally impinging the particulate diffusing layer 112 . this laser energy is illustrated by rays 131 - 137 . as previously noted these rays do not necessarily arrive in parallel relationship , but , rather , impinge from differing angles , having undergone a combination of internal reflection at the probe / diffusion layer interface 122 , and , in certain instances , internal reflection ( s ) within individual diamond particles 118 of the diffusion layer which latter reflections may direct the laser energy back into the probe tip 116 , as best visualized in fig1 , by ray 135 . depending on the ratio of the refractive indices between the diffusing particles and the probe tip , the location where the laser energy impinges the interface 122 between the probe tip and the particulate layer , laser energy will either be internally reflected or refracted into the diffusing particles . because of the high refractive index of the diffusing particles 118 , a significant portion of laser energy , which would otherwise be internally reflected by a smoothly contoured laser probe tip , is refracted into a diffusing particle 118 . and depending on the shape of the individual diffusing particle 118 , the incident energy may be directly refracted and radiated from the particle along the side of the probe or it may be first reflected within said particle one or more times . where the laser energy impinges at the probe tip / ceramic interface , the ray may be internally reflected depending upon the refractive index of said ceramic 120 . this is depicted by ray 137 in fig1 . it is this random diffusion , enabled by the high refractive index of the particulate diffusing material , and the irregular shapes of these particles which result in the broad radial diffusion of laser energy attained . fig8 illustrates yet another embodiment of the present invention . probe 50 has a substantially u - shaped cross - section and comprises a receiving portion 52 on the periphery of the base portion thereof for connection with the female connector 18 as described above . the outer and inner face of the probe have a semispherical shape and a frosted or roughened face is formed on the inner semispherical face and a part of a cylindrical portion adjacent to said inner semispherical face to provide a laser diffusing portion 54 . another portion of the inner face and the outer face remain smooth . the optical fiber 32 is disposed in the receiving portion of the probe 50 . most of the laser beam radiated from the tip end face of the optical fiber 32 enters the laser diffusing portion 54 where it is diffused and thereafter radiated from the outer surface of the tip end portion . this probe , which is brought into contact with the tissue rather than being inserted therein , is utilized for local hyperthermia , coagulation or photochemical therapy .