the present invention is directed to a method and apparatus for detecting the presence of cancerous tissue using native visible luminescence . an experimental arrangement used to measure the luminescence spectra from the various tissues is shown in fig1 . a 10 mw argon ion laser 1 operating a 488 nm was focused on the front surface of the tissue 2 to a spot size of about 100 μm . the native luminescence from the front surface was collected into a double spex - 1 / 2 m grating scanning spectrometer 3 blazed at 500 nm . a photomultiplier tube ( pmt ) rca 7265 ( s - 20 ) 4 located at the exit slit of the spectrometer 3 measured the intensity at different wavelengths . the spectral bandwidth was 1 . 8 nm . the output of the pmt was connected to a princeton applied research lock - in recorder combination 5 to display the spectrum . both the laser and reference signal from light 7 and detected by a pmt 6 were chopped at 200 hz . the spectra were not corrected for the spectrum response of the system . each sample emission spectrum was run three times for reproducibility . the measured spectra were stable in time and different regions yielded similar spectra . the luminescence emitted from cancerous and normal tissues from rat prostate and kidney were investigated . the spectra from a rat female bladder tumor and a mouse bladder tumor were also measured . all tumors were subcutaneously implanted . rat prostate tumors were implanted in fischer / copenhagen male ( f 1 ) rats and were five weeks old at the time of the testing . rat kidney tumors were implanted in wistor / lewis rats and were four weeks old . rat bladder tumor was implanted in a female fischer rat and was four weeks old at the time of testing . mouse bladder tumor was implanted in a female c3hhe mouse and was also four weeks old . all tissue samples were nonnectrotic , clean free and approximately 1 gm in weight . all tissue samples were solid chunks but not cut to any particular specificity , and were few millimeters thick . each tissue sample was placed in a clean pyrex test tube for these luminescence studies . the spectral curves for the cancerous and normal tissues are displayed in fig2 - 4 . one notices the differences in the spectra between the normal and cancerous tissues . the prominent maxima in the spectra from rat prostate tumor [ fig2 ( a )] and rat normal prostate [ fig2 ( b )] are located at 521 and 533 . 5 nm ., respectively . the prostate tumor spectrum has two subsidiary maxims located at 552 and 593 nm while no additional maxima are recorded in the normal prostrate spectrum . in the prostate tumor spectrum there are four points of inflections located at 538 . 3 , 571 . 7 , 587 . 0 , and 619 . 5 nm . on the decreasing side of the normal prostate curve there are two points of inflection located at 571 . 7 and 603 . 3 nm , as shown in fig2 ( b ). the main maxima in the spectra from male rat kidney tumor [ fig3 ( a )] and normal male rat kidney [ fig3 ( b )] are also located at 522 . 0 and 530 . 6 nm ., respectively . after the first prominent peak , the spectrum from the rat kidney tumor decreases monotonically and there are three small peaks located at 592 , 612 , and 638 nm . along this declining side of the curve there are four inflectionary points located at 548 . 7 , 559 . 3 , 581 . 3 , and 604 . 2 nm . however , after the first prominent peak for the normal male kidney , the spectrum declines monotonically until it reaches a wavelength at 590 . 8 nm where it starts to increase . along the declined portion of the curve there are three smaller peaks located at 562 , 600 and 622 nm . the spectrum also contains three inflectionary points located at 522 and 595 nm . similar spectral differences have been observed in human tissues of the lung and breast . the salient features of the rat bladder tumor spectrum are its four peaks . [ fig4 ( a )]. the first prominent peak is located at 519 . 1 nm ; other smaller peaks are located at 554 , 590 , and 634 nm . the spectrum also contains two inflectionary points locate at 567 . 0 and 605 . 2 nm . after the minimum at 614 . 7 nm the curve starts rising to the last peak at 634 . 0 nm , after which there is a fall off to zero intensity . the salient features of the mouses bladder tumor spectrum are its two wide peaks [ see fig4 ( b )]. the first prominent peak is located at 521 . 0 nm , and the other at 600 . 0 nm . the spectrum starts declining from 610 to 648 nm after which its slope changes and decays slowly to zero . there are two points of inflection in the spectrum , one located at 559 . 2 nm and the other at 648 . 2 nm . the summary of the results from the fluorescence measurements shows the following salient features that are found in common among the tumor spectra : 1 . location of the prominent maxima of the tumor spectra all occur at about 521 . 0 nm . 2 . the width of the prominent maxima are virtually the same , approximately spanning 1 . 5 nm . 3 . secondary peaks which are in common to all tumors occur between 590 - 640 nm . 4 . the secondary peak which is also in common with the rat prostate tumor and the rat bladder tumor is in the range of 552 - 554 nm . 5 . the secondary peak which is also in common with the rat kidney tumor and the rat bladder tumor fall in the range of 634 - 638 nm . upon analysis of the data between the two normal spectra , one recognizes the prominent maxima are located at 530 - 533 nm and the width of the prominent maxima are broad , each spanning 38 nm . the most salient differences between the cancerous and the normal tissues are that the spectral profiles are very different and that the cancerous prominent maxima are shifted and located around 521 nm , whereas the prominent maxima of the normal tissues spectra are located at about 531 nm . as can be seen , when protein containing fluorphors either gain positive charge ions or lose negative charge ions the fluorescence from the fluorphors have been noted to be blue shifted . the prominent maxima of all cancerous spectra exhibit in our results a 10 nm blue shift , suggesting an accumulation of positive ions , or a depletion of negative ( or positive ) ions in the mitochrondria of cancerous cells , thus causing the flavins to emit at 521 nm instead of 531 nm . the emission from 590 - 640 nm is attributed to porphyrins . in cancerous tissue the relative intensity of porphyrins bands are different , usually smaller in intensity from its normal counterpart . the spectral changes can be caused by other species such as hemoglobin . similar differences have been observed in human lung and breast tissues . referring now to fig5 . there is illustrated an embodiment of an apparatus for detecting cancerous tissue according to the teachings of this invention . the apparatus includes a source 11 of white light , such as a tungsten - halogen filament lamp , and a narrow band filter 13 . alternatively , source 11 may comprise a laser . light source 11 has power coupled to it from a conventional power supply ( not shown ). narrow band filter 13 has a bandwidth of less than about 30 nm and preferably less than about 10 nm and is designed to pass light at a wavelength 1 . light from source 11 that is passed by filter 13 is passed through a chopper 14 which removes any ambient light present and is then fed into an input leg 15 of a fiber optic probe 17 . the light entering fiber optic probe 17 emerges at the probing end 19 and impinges on tissue ts to be tested . light from tissue ts enters probing end 19 and is conducted out of fiber optic probe 17 through output legs 21 , 23 , and 24 , which are located at the same end as input leg . 15 . alternatively , the light from tissue ts can be imaged into a spectrograph or optical filters coupled to a video silicon intensified target camera computer for displaying the entire spectra . the light can be collected and imaged using a lens or a fiber optic bundle into a video camera . fiber optic probe 17 is made up basically of a bundle of optical fibers . the diameter of the bundle is preferably about 1 / 2 to 5 nm . the fibers within the bundle are preferably randomly arranged to reduce any geometrical collection effects . fiber optic probe 17 may include a lens or lens system ( not shown ) at the probing end 19 so that non - contact probing may be achieved . light emerging from output leg 21 is passed through a narrow band filter 25 having a bandwidth of less than about 10 nm , and designed to pass light at a wavelength λ 2 , and impinges on a photodetector 27 . light emerging from output leg 23 is passed through a narrow band filter 29 having a bandwidth of less than about 10 nm and designed to pass light at a wavelength λ 3 , and impinges on photodetector 31 . light emerging from output leg 24 is passed through narrow band filter 30 having a bandwidth of less than 10 nm and designed to pass light of wave - length λ 4 and impinges on photodetector 32 . the value of λ 1 is between 350 and 500 nanometers . photodetectors 27 , 31 and 32 are conventional photodetectors having maximum sensitivity in the regions of interest , namely at wavelengths λ 2 and λ 3 and λ 4 respectively of the fluorescence spectra . the wavelengths are chosen where the largest difference in intensity occurs for cancerous and normal tissues , i . e . λ 2 = 531 nm , λ 3 = 522 nm , λ 4 = 633 nm . by using more detectors at more wavelengths one can more accurately determine differences in the spectra . comparing the entire spectra using video spectroscopy such as shown in fig7 results in a more accurate way to find cancer . photodetectors 27 , 31 and 32 each produce an electrical signal output whose magnitude s1 , s2 and s3 respectively , is proportional to the intensity of the incident light . the electrical output signals from photodetectors 27 , 31 and 32 are each fed into an electronic circuit 33 which produces three output signals s4 , s5 and s6 , one corresponding to the ratio of s1 and s3 and the third corresponding to the ratio of s2 to s3 , another corresponding to the ratio of s1 and s2 . the three output signals are fed into a display where they are displayed 34 . the difference in the signals ( i . e . the difference between signals s1 and s2 or s2 and s3 ) could also be used and compared . light source 11 , narrow band filters 13 , 25 , 29 and 30 and photodetectors 27 , 31 and 32 are preferably all situated in a light - tight comparmented housing 37 . in detecting the presence of cancerous tissue in accordance with this embodiment of the invention , the ratios of the three probe signals s1 , s2 and s3 are first determined for a known noncancerous region for the particular organ containing the tissue under test . any changes in the ratios between signals s1 and s2 and s3 will indicate that the tissue is cancerous . instead of taking the ratios between signals s1 and s2 and s3 , the differences or ratios of any two as opposed to three signals , such as s1 and s2 may be used to determine the relative change of the spectra . this may be achieved using any conventional type of difference circuit for differences or a divider circuit for ratios . referring now to fig6 there is illustrated a simplified diagram of another embodiment 102 of the invention . monochromatic light from a source 101 is transmitted by a fiber optic probe 103 for a sample tissue st6 to be tested . light from the sample tissue st6 is transmitted by fiber optic probe 103 to a spectrograph ( i . e . dual zero dispersion ) 105 constructed so as to detect native luminescence emitted light from the sample tissue st6 . the output of the spectrograph 105 is imaged by a video camera 107 whose output is fed through a digitizer 109 into a computer 111 . the spectrum of emitted light along with a spectrum of emitted light for a normal tissue ( for the particular organ in question ) are both displayed on a display ( such as a tv monitor ). the difference in spectra is obtained by a computer and then displayed to determine if the tissue is cancerous . in fig7 there is shown another embodiment 110 of the invention . light from a source 111 is passed through a narrow band filter 113 where it is transmitted by a fiber optic probe 115 to the tissue st7 to be tested . native luminescence emitted from tissue st7 is imaged by a lens 117 through a filter wheel 119 having two or more filters where it is imaged on the eye 121 . instead of a filter wheel and eye , the light from lens 117 may be imaged onto the slit of a spectrograph ( i . e . dual zero dispersion ) and then processed as in the fig6 embodiment . in fig8 there is shown another apparatus constructed according to this invention , the apparatus being identified by reference numeral 131 . apparatus 131 includes a first laser 133 whose output beam is used to detect the cancerous tissue and a second laser 135 whose output beam is used to destroy the cancerous tissue after it has been detected as will hereinafter be described . laser 133 is a low or medium power laser such as an argon laser or a helium - cadmium laser . laser 135 is a high power laser such as a q - switched laser , a copper vapor laser , a gold vapor laser , a nitrogen laser or a dye laser . light from laser 133 is transmitted by an optical fiber bundle 137 to a filter 139 which filters out all light but the preselected wavelength . light passed by filter 139 is transmitted by an optical fiber bundle 141 to a dichroic coupler 143 which is designed to transmit light from laser 133 and reflect light from laser 135 . light transmitted through coupler 143 from laser 133 is transmitted by an optical fiber bundle 145 to a beamsplitting coupler 147 . light transmitted through coupler 147 from coupler 143 is transmitted by an optical fiber bundle 149 to a beam splitting coupler 151 . light transmitted through beamsplitting coupler 151 is transmitted by an optical fiber bundle 153 which functions as an endoscope and strikes sample tissue st8 which is being examined . light subsequently emitted from sample st8 ( i . e . the native luminescent radiation ) and striking bundle 153 is transmitted back to beamsplitting coupler 151 where it is reflected to an optical fiber bundle 155 which transmits the light to a spectrograph 157 . the output of spectrograph 157 is imaged by a video camera 159 . the output of video camera 159 is fed through a digitizer 160 into a computer 161 where it is compared with a spectrum of emitted light for a normal tissue to see if the tissue is cancerous . the results obtained in computer 161 ( i . e . the difference in spectra ) are displayed in a display 163 . if the results are positive , computer 161 sends a signal to activate laser 135 . light from laser 135 is transmitted through fiber bundle 169 to coupler 143 and is then reflected by coupler 143 through bundle 145 , coupler 147 , bundle 149 , coupler 151 and endoscope 153 where it strikes sample st8 and destroys the cancerous tissue by ablation . a vacuum pump ( not shown ) can be used to draw out the cancerous tissue fragments . apparatus 131 also includes a lamp 171 for illuminating the area being examined ( or treated ) at an appropriate time , so that it can be visually observed through an eyepiece 173 by a person such as a doctor . light from lamp 171 is fed into coupler 147 through a fiber bundle 175 , a filter 177 , a fiber bundle 179 , a beamsplitter 181 and a fiber bundle 183 . from coupler 147 the light is fed into endoscope 153 . the illuminated area is viewed through eyepiece 173 which is coupled to beamsplitter 181 through optical fiber bundle 187 . instead of comparing the spectrum obtained with a spectrum for normal tissue the spectrum could be compared with a spectrum for known cancerous tissue and the differences displayed . also , instead of simply displaying differences , the spectra themselves can be displayed and the decision made by the viewer as to whether it is cancerous . in another arrangement the spectrum obtained is compared with spectra for normal and for cancerous tissue and a determination made as to which of the two spectra the sample spectrum more closely represents . in another embodiment of the invention , excitation spectra are generated and used for detecting the presence of cancerous tissue in a similar manner as the luminescense spectra . the excitation spectra are obtained by measuring the intensity of the native luminescence at a preselected emission wavelength as the excitation wavelength is varied . excitation spectroscopy provides information on which bands are responsible for the observed spectroscopic differences . experimental results have shown that the differences in the excitation spectra for the normal and cancerous tissues are pronounced . an apparatus 201 for obtaining excitation spectra and also for destroying the tissue examined if desired if it is cancerous is shown in fig9 . the apparatus includes means 203 for illuminating a sample st9 with a beam of monochromatic light whose wavelength is varied and means 205 for measuring the intensity of emitted light at a preselected wavelength . apparatus 201 is similar to apparatus 131 , the differences being that laser 133 is replaced by a light source 207 , a spectrometer 209 and a chopper 211 and the spectrograph 157 and video camera 158 are replaced by a spectrometer 213 , a photodetector such as a photomultipler tube 215 , an optical fiber bundle 217 and a lock - in amplifier 219 . light source 207 is a source of white light and may be for example a tungsten - halogen lamp . in using apparatus 201 , light from source 207 is chopped and fed into spectrometer 209 . the output of spectrometer 209 is transmitted through the various beamsplitters and optical fiber bundles and strikes sample st9 . the wavelength of the output of spectrometer 209 is varied by turning a knob ( not shown ) or scanning with a motor in spectrometer 209 . the intensity of the emitted light is fed into spectrometer 213 whose output is detected by detector 215 . the output of detector 215 is fed into lock - in amplifier 219 whose output is fed into computer 161 . the excitation spectra so obtained is then compared with excitation spectra for normal and / or cancerous tissue and a determination made if the tissue is cancerous based on the comparison . instead of a lock - in amplifier 219 , a dc meter could be employed . the light emitted from spectrometer 209 is monochromatic and varied over a range of wavelengths . accordingly , means 205 measures the intensity of emitted light at a preselected wavelength as the excitation wavelength is varied . laser 135 is used to destroy to tissue if it is deemed desirable . spectrometer 213 can be replaced by an appropriate filter , if desired . experimental apparatus used to obtain excitation spectra from a sample native human breast tissues was a perkin - elmer ls - 5 fluorescence spectrometer . frontal excitation was used to pump the tissue samples . the excitation spectra were scanned from 300 nm to 500 nm for an emission peak at 520 nm , from 300 nm to 530 nm for an emission peak at 550 nm and from 300 nm to 580 nm for an emission peak at 600 nm . the emission peaks were chosen to be 520 nm , 550 nm , and 600 nm because these peaks are prominent in the emission spectra of the native breast tissues . the tissue samples were put in plastic square cells which did not generate strong background in the excitation spectrum region from 300 nm to 580 nm after nd filters were placed in the emission spectrum path to reduce emission . three pairs of human breast normal and tumor ( cancerous ) tissues were measured . the excitation spectrum profiles were consistent with each other . typical excitation spectra from native normal and tumor ( cancerous ) human breast tissues emitted at 520 nm , 550 nm , and 600 nm are shown in fig1 through 15 . one notices that the excitation spectrum profiles are quite different from the normal and tumor tissues . the excitation spectra consists of two wide bands , centered in the ultraviolet ( uv ) and visible . the uv band of the excitation spectra for the normal breast tissues in fig1 and fig1 consist of three sharp peaks located at 336 nm , 352 nm , and 371 nm . the major peak is centered at 352 nm . however , there are no clear sharp peaks in the uv bands of the excitation spectra of cancer tissues . in fig1 and fig1 a very small peak at 352 nm can be observed . the cancer spectra are broader with a characteristic feature existing at 396 nm . the main peak in the visible band of the excitation spectra in fig1 and fig1 for normal tissues is located at 473 nm . the intensities of the visible band are about four times weaker than the uv bands . however , for the tumor breast tissues in fig1 and fig1 , the intensities of the visible bands are higher than the uv bands . the excitation spectra for emission wavelength at 600 nm for normal and tumor tissues are shown in fig1 and fig1 . the larger difference between the structures in the excitation spectra for normal and tumor tissues can be easily noticed . structures exist in uv spectra for normal tissue while a broad band with a peak at 396 nm exists for cancer tissues . a visible band at 473 nm exists in both spectra . the intensity differences for the excitation spectra of tumor tissues from normal tissues are displayed in the table in fig1 for emissions at 520 nm , 550 nm , and 600 nm . the ratios between the excitation intensities for tumor and normal tissues can serve as a diagnostic marker . the excitation spectra in the uv band from normal tissues consist of three peaks while the tumor excitation spectra are without much distinct peaks . the uv band of the tumor excitation spectra are much wider than the uv band of the normal tissues due to the existence of the 396 nm peak . we should point out that the broad spectrum and the peak at 396 nm may be a characteristic of cancer in the excitation spectra which may be used to distinguish cancer from normal tissues . these differences suggest that the electronic states of fluorophores are altered in cancer cells in comparison to those molecules in the normal cells . the visible bands of the excitation spectra show clear differences in the electronic band centered at 473 nm for the excitation spectra intensity . the intensity of the tumor tissue for 520 nm is 5 . 38 times larger at 457 . 9 nm and 2 . 59 times larger at 488 nm than for the normal tissues . the excitation spectrum intensity for 550 nm is 5 . 16 times stronger at 457 . 9 nm and 3 . 53 times stronger at 488 nm that that of the normal tissues . however , the differences are much weaker for uv . these results support the fact that the cancer fluorescence emission spectra are different and stronger than normal tissue spectra for 488 nm excitation and only slightly different for uv excitation . thus , excitation spectroscopy can be used as a diagnostic tool for the detection of pathological changes in tissues . in the fig6 embodiment the fiber optic bundle could be replaced by a microscope for microscopic analysis of normal and cancerous tissue . also in fig9 the photodetector 215 could be replaced by a video system . the embodiments of the present invention is intended to be merely exemplary and those skilled in the art shall be able to make numerous variations and modifications to it without departing from the spirit of the present invention . all such variations and modifications are intended to be within the scope of the present invention as defined in the appended claims .
a method and apparatus for detecting the presence of cancerous tissue using native visible luminescence . the tissue to be examined is excited with a beam of monochromatic light that causes the tissue to fluoresce over a spectrum of wavelengths . the intensity at which the excited tissue fluoresces can be measured either over a spectrum or at a predetermined number of preselected wavelengths . by determining the wavelength at which maximum intensity are attained for the tissue in question and by comparing these peak wavelengths , either visually or electronically , to the peak wavelength derived from a known non - cancerous tissue , or by comparing the luminescence spectrum of the excited tissue with the luminescence spectrum of a known noncancerous tissue and / or known cancerous tissue or the excitation spectra of the excited tissue with the excitation spectra of known cancerous and / or known non - cancerous tissue one can determine the carcinomatoid status of the tissue in question . once it has been determined that the tissue is cancerous , it may by destroyed by ablation by exposing it to a beam of light from a high power laser . the invention is based on the discovery that the visible luminescence spectra for cancerous and non - cancerous tissue are substantially different and that the differences are such that visible luminescence from tissue can be used to detect the presence of cancer and also on the discovery spectral profiles of excitation spectra are similarly different .