as showed by figures , where identical numeric references identifying equivalents parts , the system for obtaining a fundus image , object of present invention is constituted basically by two different optical means , which are typical of a retinograph , and called lighting means and capturing means . these means are described separately and present optical coaxial paths 1 , with the superposition in a passage of its distances between the fundus 16 and the arrangement outlet end of the optical fibers 7 . the optical means are implemented in a equipment that has mechanical structures , fixed and adjustable , to support the components , besides electronic circuits , computer and applicable program , used for control the equipment , images acquisition , image processing and displaying the results . the first optical mean has the function to illuminate the fundus with a light beam that , must present two essential characteristics , whereas the first characteristic is to pass the frontal part of the eye by its peripheral region , while the second characteristic is to reach the fundus with a uniform distribution of energy . the requisite that the beam trajectory is contained exclusively in the peripheral region of the frontal part of the eye has the objective in avoid the reflection and light scattering in the intraocular medium , leaving the pupil central region free of intense lighting . the second optical means has function in capturing the image produced in the lighting process being constituted by two lenses sets and a high sensibility digital camera . these lenses sets form a system characterized like an altered afocal telescope , in that the first set is called of capturing lens , or eyepiece , and the second set is constituted by its lens , working like the afocal complement of the capturing lens . the fig1 shows the used technique showing a complete scheme of the two main optical means , and its basic working principles , whereas the elements 7 , 8 , 9 , 10 , 11 and 13 correspond to the optical components of the principal part of the lighting means , and its optical axis 1 . the elements 14 , 15 and 16 represent the eye being deeply illuminated ; with the beam reaching the fundus wall 16 , after passes by the frontal part of the eye 14 , which includes the cornea , anterior camera , iris , lens and pupillary opening 15 . the complete capturing means includes the elements 2 , 3 , 4 , 5 , 6 , 8 and 13 herein represented by the digital camera 2 , 3 ; and by capturing lens , or eyepiece of the mean 13 , its afocal complement , or means lens 6 , optical set of filters 5 and light polarizer 4 , which proceed the image acquisition formed by the light reflected on the fundus 16 . the camera is constituted by a focal lens 3 , which registers the image formed on a ccd image sensor type 2 . the optical axis 1 common in both optical means must be adjusted during the measure proceeding in order to approximately coincide with the optical axis of the eye in examination 14 , 15 , and 16 . also in the fig1 there are the distances that define the plans of the pupil 15 and the arrangement outlet end of the optical fibers 7 as conjugated distances by actuation of the capturing lens 13 , when considered as an integrant element of the lighting means . however , when considered as an integrant element of the capturing means , the capturing lens 13 collects the light that goes out from the pupil 15 and a fundus primary real image 12 is formed between this capturing lens 13 and the passage orifice 8 of the capturing beam , in a position 12 that can present a small variation depending on the patient eye diopter 14 , 15 , 16 . said primary real image 12 , is focused on the image sensor 2 , by the afocal system lens 6 together with camera focal lens 3 , after the capturing beam passes the orifice 8 of the optical fibers arrangement 7 , 8 , 9 , 10 . it should be observed that the eye optical element 14 acts together with the capturing lens 13 in the formation of the primary real image 12 . in the fig2 it is shown in details , the complete lighting means in a lateral view , whereas the used technique in this means is shown up , in that an annular light beam is produced to penetrate the eyeball 14 , 15 , 16 through the periphery of the eye anterior part 14 and illuminates uniformly the whole extension of the fundus 16 . the called optical fibers arrangement is obtained from a piece 7 , 8 , 9 , 10 made with a bundle of optical fibers 9 shaped in a curved geometrical form and lengthened , been like a pipe , which ends 7 and 10 are fixed by steel rings , in order to obtain the coupling of the light source at the end 10 , a light emitting object with ring form at the end 7 and an opening 8 for the passage of the capturing beam by the centre of this ring . the annular beam is projected from the fibers outlet end 7 passing the light polarizer 11 , also in a ring form , in order to not obstructing the orifice 8 , whereas the capturing beam passes . the light source used in this specific projector is a halogen lamp 23 coupled to the entry end 21 of an intermediary optical fibers bundle 19 , 20 , 21 associated to a concave mirror 22 , which has the function in focusing the maximum possible amount of light emitted by the lamp in the entry of the fibers bundle , considering the diameter of these fibers and its numerical opening . the intermediary optical fibers bundle 19 , 20 , 21 , has the outlet end 19 coupled to a entry end of the optical fibers arrangement 10 , with the set of condensing lenses 18 , whose function is focuses the light emitted by the intermediary bundle in the entry of fibers arrangement by coupling its respective numerical openings and diameters . said halogen source 23 , emits light in a wide specter of wavelengths , including the ultraviolet band , all near the visible and near infrared , optical filters are used to blockade the ultraviolet band . the intermediary couplings between the halogen lamp 23 and the entry end 10 of optical fibers arrangement 9 were designed in order to maximize the light entry in the said optical fibers 9 and homogenize the distribution of light along the line of the ring formed in the optical fibers outlet end 7 . the optical filters set 17 of the lighting means is positioned immediately before the optical fibers arrangement 7 , 8 , 9 , and 10 . it is possible through mechanical adjusts set the focal distances and placing the couplings ends between the optical fibers bundles 9 , 20 , in order to allow the maximum insertion of energy in the fibers . alternatively , it can be used as a light source , a set of light emitting diodes ( led ) covering a wide band , which would allow the midriatic use , in that the fundus is illuminated by a set of infrared led &# 39 ; s . in order to obtain a colorful fundus image or “ red free ”, with visible radiation , the led is blinked quickly , offering more comfort to a patient . said means projects an annular light beam relatively intense , when compared with the quantity of light that returns reflected by the fundus 16 , in the same optical path 1 , which represents a small fraction of the intensity of the lighting beam . the beam has the form of an extremely fine ring in its passage by the pupil 15 , with a diameter slightly less than the pupillary opening and approximately concentric to the optical axis of the eye . as observed in the fig2 , in a lateral view , this light beam been emitted peripherical in the outlet end 7 of the optical fibers arrangement , reaching the capturing lens 13 , being focused in the circle that defines the periphery of the pupil 15 , and diverging from that , in order to illuminating uniformly the fundus 16 . the fig3 shows in details a lateral view of the complete capturing means formed by elements 2 , 3 , 4 , 5 , 6 and 13 , that should capture and register a good quality image of fundus 16 . the capturing lens 13 is placed against the eye in examination 14 , 15 , 16 , and should receive the whole light that passes by the pupillary opening 15 bringing back from the fundus 16 , subtended by an angle less than 22 . 5 ° of semi - opening , while the afocal lens 6 , projects in front the afocal beam produced . the capturing lens 13 must be positioned quite near and in front of the eye 14 , 15 , 16 , so it is necessary that said capturing lens 13 , be a common component to the two optical means , and that combines the two beams in a unique optical path whose axis 1 coinciding . the most appropriate construction to become the beams be coaxial , is that the capturing beam passes by the ring orifice 8 formed by the optical fibers arrangement 7 , 8 , 9 , 10 proposed in this technique . the functional project of the capturing lens 13 and of central orifice 8 of the optical fibers arrangement must be satisfactory to the requisites of these two means simultaneously . the digital camera 2 , 3 that also composes the capturing means is constituted by a set of lenses that form the camera focal lens 3 , which project the fundus image 16 on a sensor 2 made with a matrix of photosensitive elements . in the capturing means , the set of optical filters 5 and the light polarizer 4 are strategically positioned between the afocal system 6 and 13 and the camera focal lens 3 , because in this region the rays of the capturing beam are parallel having just surfaced the afocal system . the focusing lens set 3 of the image , placed in front of the image sensor 2 , as well as the lens 6 of the afocal system , do not interfere in the performance of the lighting means since they are not in the same optical path . the system magnification is maintained fixed by the self - characteristics of the afocal system 6 , 13 , whose lenses are maintained rigidly in its positions , in that important bonds of the system are not altered . however , the focuses adjust in the focal lens of camera 3 produces a small alteration in the magnification . the fig4 a shows an inferior view of the optical fibers geometrical arrangement 7 , 8 , 9 , 10 . the fig4 b shows a frontal view of the optical fibers geometrical arrangement 7 , 8 , 9 , 10 and an opening e in the optical fibers bundle , the fig4 c shows a lateral view of the optical fibers geometrical arrangement 7 , 8 , 9 , 10 and an opening e in the optical fibers bundle , the fig4 d shows a superior view of the optical fibers geometrical arrangement 7 , 8 , 9 , 10 . the fibers of the bundle , in the figures above mentioned , are configured in a geometrical curved and lengthened form , producing a piece 9 that is likened to a pipe , where in the outlet end 7 , or superior , the fibers are positioned side by side , forming a fine and circular line , while in another extremity of the piece 10 , or inferior , the fibers are accumulated on an intense light source . the optical fibers arrangement has an optimized geometry to capture the maximum of light in its entry end 10 and conformed to produce a light ring in its outlet 7 , by placing of the fibers side by side , in a circular line with diameter of 7 millimeters and with a line width from 50 to 200 microns , since they are formed by fibers of this diameter . the fig5 a , shows the frontal view of the outlet end , of the optical fibers arrangement , with an opening e of optical fibers bundle , details of the endings of the fibers bundles , in that the outlet end of the bundle with the fibers aligned side by side form a ring . the fig5 b , shows a frontal view of the entry end , in that the bundle end entry with the fibers is accumulated around a point . the fig6 shows a lateral crossed view of the system integrated and mounted on its compartment . the system has a fixed base of sustenance from which it is possible to adjust the body of the system with the projection and capturing means . these means are mounted in a sliding base in the body of the system , in the horizontal plan when in images acquisition operation . the system can be configured in four operational ways that carry out four types different of opthalmologic examinations , increasing its applicability . the selection of the spectral band of work is effectuated by a specific combination of optical filters in accordance with the type of examination to be carried out . the optical means of lighting and capturing were optimized to correct aberrations , mainly the chromatic aberration in the band between the blue and the infrared , between 400 and 950 nanometers , due to four types of examinations that will be effectuated . which are : examination with normal colorful image , also called colorful retinography or “ color ”, where light polarizers are used and a combination of optical filters which allow lighting and capturing in the whole range of the visible ; examination with absence of red light , called aneritry retinography or “ red free ”, also with the use of light polarizers and combination of optical filters which promote lighting with green light and capturing in the whole range of the visible ; examination called fluorescein angiography , in that is used the property of fluorescence of this substance , which injected in the blood current makes possible an accented contrast of the image obtained in examination of the superficial blood vessels fundus , when filters are used for projection of blue light and capturing of light in the green - yellow band ; and examination in the infrared band , so - called indocianine green ( icg ), where the property of fluorescence is used in the infrared band of this substance , which injected in the blood current makes possible a contrast accented in examination of the deep blood vessel fundus , when filters are used for projection and capturing of infrared light , respectively in different bands of wavelength , in that this examination allows a deep examination of the choroids since the retina is semitransparent to the infrared . the program that controls the acquisition and processing of images , besides displaying results obtained from the images , also was developed for the scheme of operational compatible mode with the configurations described above . this program ( software ) allows , from each digital image produced and its processing , obtain points to outline the profile of anomalies present in the retina and in the structures of the wall fundus , resulting in the determination of its form and dimension , including dimensional measures for diagnosis . the equipment handling has total operational comfort because it is portable and suitable to be placed where it will be more convenient for the execution of the work . the appropriate adjust to the patient eye is carried out through a gauntlet .
the present invention is related to a system for obtaining a fundus image , constituted by optical means implemented in an equipment to observe and photograph the image of the wall fundus , comprising a capturing optical means composed by high sensibility digital camera , constituted by an image sensor and focal optical system , said digital camera being used to register a captured image by an afocal optical system , composed by a capturing lens and its afocal complement ; a lighting optical means provided from a arrangement conformed with optical fiber bundle , , and , halogen light source or light emitting diode source ; wherein said light beam from the halogen light or light emitting diodes has an annular form when it pass in the anterior part of eyeball and focus in the pupil plan ; both the means having the optical path partially common over the optical axle from the optical fibers arrangement , , and to the fundus , region in that both the beams are coaxial ; in that both the optical means are equipped with light polarizers and , being integrated with mechanical , electronics and computerized components , and applicative program , which allow control the equipment and its multiple operational configurations , conducing image acquisition and processing , and displaying the results .