hereafter , the embodiment of the present invention is explained with reference to figures . fig1 is a conceptual view showing an entire constitution of a diagnostic apparatus 1 which adopted the optical probe . as shown in this figure , diagnostic apparatus 1 is apparatus which diagnoses the disease state ( for example , the kind of a disease and infiltration range ) such as the degeneration of a physiological tissue , and the cancer in lumen k in the living body , and has light source 10 , optical probe 2 , spectroscope 11 and spectral - analysis device 12 . the light source 10 generates excitation light such as xenon light , and is connected with the optical probe 2 through the wavelength selection filter . the optical probe 2 is inserted in lumen k in the living body along the direction of an axis x , and has the objective optical system 4 and optical fiber group 3 in the tubular sheath 20 as shown in fig2 a . the objective optical system 4 in the embodiment shown in fig2 and below - mentioned fig3 consists of plus lenses ( converging lens ) which has plus refractive power . the plus lens is sufficient whether constituted with a single lens or a lens system constituted with two or more lenses . this objective optical system 4 is arranged towards the tip side of the optical probe 2 , and coincides the optical axis j of the objective optical system 4 ( plus lens ) with the central axis of the optical probe 2 in the present embodiment . in addition , as such an objective optical system 4 , a well known lens system from the former can be used . the optical fiber group 3 irradiates with excitation light generated by light source 10 to the observation object part of a physiological tissue , and receives the fluorescence which originated in this excitation light and is emitted from a physiological tissue or a drag beforehand injected into living body . this optical fiber group 3 has a plurality of optical fiber 30 b for receiving the fluorescence . these plural optical fiber 30 b are directed toward the tip surface 300 to the objective optical system 4 , are arranged by the position offset from the optical axis j of the objective optical system 4 , and receives the fluorescence passing the objective optical system 4 from the tip surface 300 . a plurality of the tip surface 300 is arranged in the shape of a concentric circular about the optical axis j of the objective optical system 4 , the mutual position of the tip surface 300 is shifted along the optical axis j ( the direction of an axis x of the optical probe 2 ) of the objective optical system 4 according to the amount of offset from the optical axis j of the objective optical system 4 , and in the present embodiment , when the tip surface 300 is arranged closer the tip side of the optical probe 2 , the tip surface 300 is close to the optical axis j of the objective optical system 4 , that is the amount of offset is small . however , the tip surface 300 is arranged by the other embodiment as long as the position of the tip surface 300 of the optical fiber 30 b of which amounts of offset from the optical axis j of the objective optical system 4 differ mutually at least among the plurality of optical fiber 30 b . the optical fiber group 3 has optical fibers 30 a for irradiating the excitation light which is generated by the light source 10 and irradiated as an emission light , parallel light or convergence light to the observation object part of physiological tissue through the objective optical system 4 . this optical fiber 30 a is sufficient the same as that of optical fiber 30 b for receiving light as shown in fig2 a , it is sufficient the separate as shown in fig2 b and 2 c . in addition , in fig2 b , the only one optical fiber 30 a is formed on the optical axis j of the objective optical system 4 , and a plurality of optical fiber 30 a is arranged side by side to each optical fiber 30 b in fig2 c . however , the optical fiber 30 a of fig2 c irradiates an excitation light ( convergence light ) which amount of the diffusion degree is small only to the observation object part through the objective optical system 4 , in contrast , the optical fiber 30 a of fig2 b irradiates the excitation light ( emission light ) which amount of the diffusion degree is larger than the optical fiber 30 a of fig2 c through the objective optical system 4 , since it is necessary to irradiate the excitation light with the observation object part corresponding to each optical fiber 30 b . in addition , as for the above optical fiber 30 a and 30 b are desirable to consist of bundle fibers . moreover , the optical probe 2 is provided with the moving mechanism section 25 which moves at least one of the objective optical system 4 ( plus lens ) and optical fiber group 3 along the optical axis j of the objective optical system 4 , this moving mechanism section 25 is connected with controller 21 for an operator to operate . this moving mechanism section 25 optimizes the intensity of the fluorescence received by the optical fiber 30 b ( convergence degree by the objective optical system 4 ) and the position of the observation object part by moving the objective optical system 4 or the optical fiber group 3 . in addition , fig2 and below - mentioned fig3 are illustrating situation that the objective optical system 4 among the objective optical system 4 and optical fiber group 3 moves by the moving mechanism section 25 ( refer to the arrow in a figure ). moreover , the objective optical system 4 is desirable to move in the sealed space in the optical probe 2 . moreover , as the above moving mechanism section 25 , well - known mechanisms , such as a cam mechanism or voice coil motor , is applied , for example . a spectroscope 11 measures intensity of some wavelength from the detected fluorescence by optical fiber 30 for receiving light which is provided in the optical probe 2 ( henceforth “ spectrometry ”), outputs the measurement result as electronic information ( spectroscopic spectrum signal ). a spectral - analysis device 12 analyses the optical spectrum signal outputted by the spectroscope 11 , converts the optical spectrum signal into image data of a spectroscopic spectrum graph , diagnoses disease state . moreover , an image data and a diagnostic result of the spectroscopic spectrum graph which are generated by the spectral - analysis device 12 are displayed on to monitor 120 . in addition , well known things is applied for example , such as a disclosed thing of japanese unexamined patent application publication no . h7 - 155286 , japanese unexamined patent application publication no . h7 - 204156 , japanese unexamined patent application publication no . h10 - 239517 , japanese unexamined patent application publication no . h10 - 295632 , japanese unexamined patent application publication no . h11 - 223726 , japanese unexamined patent application publication no . 2005 - 319212 , as light source 10 , spectroscope 11 , and spectral - analysis device 12 . since the optical probe 2 of diagnostic apparatus 1 is applied the objective optical system 4 arranged towards the tip side of the optical probe 2 and a plurality of optical fiber 30 b to receive fluorescence from the tip surface 300 through the objective optical system 4 , a plurality of optical fiber 30 b is arranged by the position which directed toward the tip surface 300 to the objective optical system 4 , and is offset from the optical axis j of the objective optical system 4 , as a dashed line shows in fig2 a , when the optical probe 2 is inserted in lumen k such as an esophagus , the fluorescence from the wall surface located in the side of the optical probe 2 is converged to the tip surface 300 of each optical fiber 30 b . and since the position of the tip surface 300 of the optical fiber 30 b where the amounts of offset from the optical axis j of the objective optical system 4 differ mutually at least among a plurality of optical fiber is mutually shifted along the optical axis j of the objective optical system 4 , the fluorescence from the wall surface of the probe side in each different position along the optical axis j of the objective optical system 4 is converged ( image formation ) to the tip surface 300 of each optical fiber 30 b . therefore , the fluorescence from the wall surface of the side of the optical probe is certainly receivable . moreover , fluorescence can be detected from plural part , without moving the main part portion of the optical probe 2 in the direction of optical axis j of the objective optical system 4 . moreover , since the tip surface 300 of a plurality of optical fiber 30 b for receiving light is provided , the fluorescence from a plurality of a observation object part is detectable , respectively . therefore , diagnostic speed is accelerable . moreover , when the tip surface 300 of a plurality of optical fiber 30 b for receiving light is arranged closer the tip side of the optical probe 2 , the tip surface 300 is close to the optical axis j of the objective optical system 4 , the fluorescence from the wall surface of the probe side in each different position along the optical axis j of the objective optical system 4 is certainly converged ( image formation ) to the tip surface 300 of each optical fiber 30 b . therefore , the fluorescence from the surface of a wall located in the probe side is certainly receivable . moreover , since the tip surface 300 of a plurality of optical fibers 30 b is arranged in the shape of a concentric circular about the optical axis j of the objective optical system 4 , the fluorescence is detectable from the annular observation object part . moreover , at least one of the objective optical system 4 and a plurality of optical fiber 30 b moves along the optical axis j of objective optical system 4 , the position of the observation object part and the degree of converging ( image formation ) can be changed . in addition , an embodiment which can apply the present invention can be suitably changed in the range which does not deviate from the meaning of the present invention , without being limited to the above - mentioned embodiment . for example , although the optical probe 2 is explained as providing the moving mechanism section 25 , it is good also as not providing . in this case , it is desirable that the tip surface 300 of the optical fiber 30 b is arranged at an image formation position of the fluorescence by a plus lens beforehand . moreover , as shown in fig3 a , it is desirable that the optical probe 2 is equipped a camera 22 which takes a photograph along the direction of an axis x . in this case , the state in lumen k can be sighted . moreover , as shown in fig3 b , it is desirable that the optical probe 2 is equipped a balloon 23 which inflates in the diameter direction ( the rectangular direction to the direction of an axis x ) and sticks to the inner wall of lumen k . in this case , the observation object part can be prevented from shifting during observation . in 1st embodiment , the fluorescence from the wall surface of side of the optical probe in each different position along the optical axis j is made to converge ( image formation ) to the tip surface of each optical fiber , and certainly receiving the fluorescence from the wall surface of side of the optical probe , when an objective optical system 4 which provided with single plus lens is used , and the tip surface 300 of the plurality of optical fiber which the amount of offset from the optical axis j is differ mutually has composition from which the position of the tip surface 300 is mutually shifted along the optical axis j . in 2nd embodiment , the same effect as the 1st embodiment is acquired when an objective optical system 4 which provided with at least two plus lenses are used , and the moving mechanism section which moves at least one of the optical fiber and the two plus lenses along the optical axis j is provided . it explains below . the optical probe 2 concerning the 2nd embodiment is also inserted in lumen k in the living body along the direction of an axis x , and has the objective optical system 4 and optical fiber group 3 in the tubular sheath 20 as shown in fig4 a . in addition , detailed explanation is omitted by giving a same sign to below about the same function member as fig2 and fig3 . the objective optical system 4 has two plus lenses 40 , 41 which have plus refractive power . these plus lenses 40 and 41 are arranged towards the tip side of the optical probe 2 in the state where it countered mutually , and are coinciding the optical axis j with the central axis of the optical probe 2 respectively , in this embodiment . in addition , as such an objective optical system 4 , a zoom lens well known from the former can be used . in addition , although explained as having the two plus lenses 40 , 41 as the objective optical system 4 , it is not limited to this , has three or more lenses , or is good also as a negative lens being included . a plurality of optical fiber 30 b is arranged by the position which directed toward the tip surface 300 to the objective optical system 4 , and is offset from the optical axis j of the objective optical system 4 , and receives the fluorescence passing the objective optical system 4 from the tip surface 300 . moreover , as a desirable embodiment , a plurality of the tip surface 300 is arranged in the shape of a concentric circular about the optical axis j of the objective optical system 4 , and the mutual position of the tip surface 300 is shifted along the optical axis j ( the direction of an axis x of the optical probe 2 ) of the objective optical system 4 according to the amount of offset from the optical axis j of the objective optical system 4 . furthermore , as a more desirable embodiment , when the tip surface 300 of a plurality of optical fiber 30 b for receiving light is arranged closer the tip side of the optical probe 2 , the tip surface 300 is close to the optical axis j of the objective optical system 4 . however , the tip surface 300 is arranged by the other embodiment as long as the position of the tip side of the optical fiber 30 b of which amounts of offset from the optical axis j of the objective optical system 4 differ mutually at least among the plurality of optical fiber 30 b . moreover , the optical fiber group 3 has optical fibers 30 a for irradiating the excitation light which is generated by the light source 10 and irradiated as an emission light , parallel light or convergence light to the observation object part of physiological tissue through the objective optical system 4 like the 1st embodiment . this optical fiber 30 a is sufficient the same as that of optical fiber 30 b for receiving light as shown in fig4 a , it is sufficient the separate as shown in fig4 b and 4 c . in addition , in fig4 b , the only one optical fiber 30 a is formed on the optical axis j of the objective optical system 4 , and a plurality of optical fiber 30 a is arranged side by side to each optical fiber 30 b in fig4 c . however , the optical fiber 30 a of fig4 c irradiates an excitation light ( convergence light ) which amount of the diffusion degree is small only to the observation object part through the objective optical system 4 , in contrast , the optical fiber 30 a of fig4 b irradiates the excitation light ( emission light ) which amount of the diffusion degree is larger than the optical fiber 30 a of fig4 c through the objective optical system 4 since it is necessary to irradiate the excitation light with the observation object part corresponding to each optical fiber 30 b . in addition , as for the above optical fiber 30 a and 30 b is desirable to consist of bundle fibers . moreover , as shown in fig1 , the optical probe 2 is provided with the moving mechanism section 25 which moves at least two of the plus lens 40 , 41 and optical fiber group 3 along the optical axis j of the objective optical system 4 independently , this moving mechanism section 25 is connected with controller 21 for an operator to operate . this moving mechanism section 25 optimizes the intensity of the fluorescence received by the optical fiber 30 b ( convergence degree by the objective optical system 4 ) and the position of the observation object part by moving ( refer to the allow in fig4 ) the at least two of the plus lens 40 , 41 and optical fiber group 3 along the optical axis j . moreover , the plus lens 40 , 41 and optical fiber group 3 are desirable to move in the sealed space in the optical probe 2 . moreover , as the above moving mechanism section 25 , well - known mechanisms , such as a cam mechanism or a mechanism using a plurality of a voice coil motor , is applied , for example . since the optical probe 2 of the 2nd embodiment is provided with the objective optical system 4 which has two plus lens 40 , 41 which are arranged towards the tip side of the optical probe 2 in the state which countered mutually , a plurality of optical fiber 30 b which tip surface 300 is arranged towards the objective optical system 4 and in a position offset from an optical axis j of the objective optical system 4 and receives the fluorescence passing the objective optical system 4 from the tip surface 300 , and the moving mechanism section 25 which moves at least two of a optical fiber 30 b and plus lens 40 , 41 along the optical axis j of the objective optical system 4 , as a dashed line and allow shows in fig4 a , so the optical probe 2 changes the degree of converging ( image formation ) and focal length of the objective optical system 4 , and converges the fluorescence from the wall surface of the optical probe 2 side to the tip surface 300 of each optical fiber 30 b . therefore , when the optical probe 2 is inserted in lumen k , the fluorescence from the wall surface located in the side of the optical probe is certainly receivable . since a plurality of the optical fiber 30 b is provided same as the optical probe 2 of the 1st embodiment , fluorescence from a plurality of the observation object part is detectable , respectively . therefore , diagnostic velocity is accelerable . and since the position of the tip surface 300 of the optical fiber 30 b where the amounts of offset from the optical axis j of the objective optical system 4 differ mutually at least among a plurality of optical fiber is mutually shifted along the optical axis j of the objective optical system 4 , the fluorescence from the wall surface of the probe side in each different position along the optical axis j of the objective optical system 4 is converged ( image formation ) to the tip surface 300 of each optical fiber 30 b . therefore , the fluorescence from the wall surface of the side of the optical probe is certainly receivable . moreover , fluorescence can be detected from plural part , without moving the main part portion of the optical probe 2 in the direction of optical axis j of the objective optical system 4 . moreover , when the tip surface 300 of a plurality of optical fiber 30 b is arranged closer the tip side of the optical probe 2 , the tip surface 300 is close to the optical axis j of the objective optical system 4 , the fluorescence from the wall surface of the optical probe 2 side is certainly converged ( image formation ) to the tip surface 300 of each optical fiber 30 b by the objective optical system 4 . therefore , the fluorescence from the surface of a wall located in the probe side is more certainly receivable . tip surface 300 of a plurality of optical fiber 30 b is arranged in the shape of a concentric circular about the optical axis j of the objective optical system 4 , the fluorescence is detectable from the annular observation object part . moreover , it is good as composition of fig5 a and fig5 b as well as fig3 a and fig3 b , so the state in lumen k is sighted . moreover , in fig5 a , the optical probe 2 is provided a camera 22 which takes a photograph along the direction of an axis x , in this case , the state in lumen k can be sighted . moreover , in fig5 b , the optical probe 2 is provided a balloon 23 which inflates in the diameter direction ( the rectangular direction to the direction of an axis x ) and sticks to the inner wall of lumen k , so the observation object part can be prevented from shifting during observation .
a probe which is inserted into a lumen of inside of a body , irradiates an observation object part of a physiological tissue with excitation light , and detects fluorescence resulting from the excitation light , wherein the probe including : a plus lens arranged facing toward a tip side of the probe ; and a plurality of optical fibers receiving the fluorescence at tip surfaces through the plus lens , wherein the tip surface are directed toward the plus lens and arranged in positions offset from an optical axis of the plus lens , wherein positions of the tip surface of at least optical fibers of which an amount of offset from the optical axis of the plus lens differ mutually among plurality of optical fibers are shifted mutually along the optical axis of the plus lens .