Patent Publication Number: US-2015065845-A1

Title: Measuring apparatus and its method

Description:
TECHNICAL FIELD 
     The present invention relates to a measuring apparatus and its method which are for example suitably applied to the case where an inner condition of an object to be measured is noninvasively measured. 
     BACKGROUND ART 
     Conventionally, in the case where a human body is measured as an object to be measured, as measuring methods for noninvasively measuring an inner condition of the human body, there have been proposed, for example, X-ray radioscopy, X-ray computed tomography (CT), magnetic resonance imaging (MRI), ultrasonic echo method, Doppler method (see for example Patent Document 1), dielectric spectroscopy (see for example Patent Document 2), near infrared spectroscopy (NIRS) (see for example Non-Patent Document 1) and the like.
     Patent Document 1: Japanese Patent Publication No. 6-53117   Patent Document 2: Japanese Patent No. 3367279   Non-Patent Document 1: “Evaluation on Intermittent Claudication using Near Infrared Spectroscopy”, H. Tsuchida, et al., Japanese Journal of Vascular Surgery, 1998, VoL. 7, No. 3, pp. 475 to 487   

     However, the X-ray radioscopy and the X-ray CT, in which radiation rays are used, have a problem of a non-negligible extent of radiation exposure as well as a problem due to temporal and environmental restrictions. Further, in the X-ray CT, in the case of measuring a bloodstream and the like, it is necessary to separately inject a contrast agent and the like. As a result, the bloodstream distribution can be recognized by the contrast agent, but for example the action potential of a nerve (hereinafter referred to as nerve action potential) itself cannot be measured. The nerve action potential is a transient potential change (about +20 (mV)) caused in the inside and the outside of the membrane of a neurone serving as a basic cell of the nerve system when the neurone is stimulated. The nerve action potential is transmitted without attenuation along a nerve axon to its end, and further serves as a stimulus to a subsequent neurone via a synapse (this flow of the nerve action potential is hereinafter referred to as nerve flow). 
     In the MRI, the distribution of water molecules in a living-body tissue is statically measured by utilizing the nuclear magnetic resonance of water in the living-body tissue. Thus, in order to measure electric phenomena such as the nerve action potential and the nerve flow, or a blood flow in the tissue, some kinds of algorithm to derive the electric phenomena, the blood flow and the like on the basis of the distribution of the water molecules, are required in the MRI, which causes a difficulty. 
     The ultrasonic echo method, in which the resolution is low and the reflection is caused on the surface of the tissue, is not suitable for a uniform tomographic operation reaching the deep part of the tissue. In addition, in the ultrasonic echo method, for example when the uterus is photographed, clear tomograms cannot be obtained without the urine being stored in the urinary bladder, because of adverse effects of the bladder wall and the like, as a result of which a prescribed restriction of storing the urine in the urinary bladder is forced on a person to be measured. Further, the nerve action potential itself cannot be measured by the ultrasonic echo method either. 
     In the dielectric spectroscopy, the tissue can be identified better than in the MRI on the basis of the bonded states of water molecules (the states of free water, quasi-bonded water, bonded water) in the tissue. However, in the dielectric spectroscopy, it is difficult to continuously measure a bloodstream and the like for a long period of time. In addition, the dielectric spectroscopy is complicated because it is necessary to perform control of the electrical length and to fix electrodes to the surface of a human body so as to prevent an air gap and a positional deviation from being caused. Further, the nerve action potential itself cannot be measured by the dielectric spectroscopy either. 
     The Doppler method, in which the Doppler shift due to a bloodstream is measured by irradiating a blood vessel with for example laser light, is a method for individually measuring the bloodstream at a pinpoint of the blood vessel. Therefore, in this method, it is difficult to obtain the distribution of the bloodstream and the blood vessel over a large area. Further, the nerve action potential itself cannot be measured by the Doppler method either. 
     The near infrared spectroscopy is a method which has been widely recognized in recent years, and in which the fact that light of a specific wavelength in a near-infrared band is hardly absorbed by a living-body tissue and transmitted therethrough, and that the light of the specific wavelength is selectively and specifically absorbed by deoxidized hemoglobin (venous blood) is utilized so as to noninvasively measure the bloodstream distribution of the living-body tissue and the like on the basis of the transmission and the reflection of the light. The near infrared ray has high transmittance, but in practice, is not transmitted in a simple manner as in the case of X-ray due to scattering, refraction and the like in the living body. As a result, in the near infrared spectroscopy, the image in the body tissue except optically shallowly existing or exposed portions such as superficial veins and the retina is difficult to be measured because the near infrared ray is scattered in an extremely complicated manner. 
     Further, in the near infrared spectroscopy, the main purpose is to measure deoxidized hemoglobin (venous blood), and hence, it is difficult to measure oxidized hemoglobin (arterial blood). That is, the near infrared spectroscopy, in this case, needs complicated estimation algorithm such as for making up in advance a scattering model of a target living-body tissue, and hence, is complicated as well as uneasy in accuracy. Further, the nerve action potential itself cannot be measured by the near infrared spectroscopy either. 
     On the other hand, there is a method such as magnetoencephalography, which measures a magnetic field caused by the nerve action potential. In this method, when an ion current flows in a living body in accordance with an electrical activity of the living body, such as the nerve action potential, a magnetic field is induced by the ion current as in the case of current flowing through an electric wire, so that the state of the nerve action potential is noninvasively measured by capturing the magnetic field using a highly precise magnetic field sensor. This method is suitable for measuring the two dimensionally distributed nerve action potential of the cerebral neocortex. However, in this method, it is difficult to perform control in the depth direction, such as to three-dimensionally obtain the state under the cortex, so that this method is limited to applications for obtaining the surface activity. Further, in this method, it is difficult to measure a bloodstream simultaneously by the same means. Thus, for this purpose, this method needs to be used in combination with the MRI and the like. 
     On the other hand, there is known a patch clamp method which is a kind of the voltage-clamp method, as a potential measuring method for the nerve and other cells. The patch clamp method is a method in which a micropipette made of glass is put on a cell membrane under an optical microscope and thereby the open/close state of a targeted ion channel is checked by the channel current. Accordingly, in the patch clamp method, it is necessary not only to control the micropipet under the optical microscope to make the micropipet in contact with the cell membrane, but also to dissect the tissue. For this reason, a noninvasive and non-contact measuring technique is required in this method. Naturally, in the patch clamp method, a bloodstream and the like cannot be measured. 
     As described above, conventionally, the method for simultaneously measuring different biological reactions such as the bloodstream, the nerve action potential or the like has not yet existed. For this reason, the conventional methods are insufficient for simultaneously obtaining much information on the inner condition of the human body. 
     DISCLOSURE OF THE INVENTION 
     The present invention has been made in view of the above described circumstances. An object of the present invention is to provide a measuring apparatus and its method which make it possible to more accurately grasp the inner condition of an object to be measured. 
     In order to solve the above described problems, according to the present invention, there is provided a measuring apparatus comprising: quasi-electrostatic field generating means generating a quasi-electrostatic field of higher field strength as compared with a radiated electric field and an induced electromagnetic field; quasi-electrostatic field detecting means detecting a result of interaction between the quasi-electrostatic field generated by the quasi-electrostatic field generating means and applied to an object to be measured and an electric field corresponding to a potential change caused by a dynamic reaction inside the object to be measured; and extracting means extracting the potential change from the result of interaction detected by the quasi-electrostatic field detecting means. 
     Further, according to the present invention, there is provided a measuring method comprising: quasi-electrostatic field generating step generating a quasi-electrostatic field of higher field strength of compared with a radiated electric field and an induced electromagnetic field; a quasi-electrostatic field detecting step detecting a result of interaction between the quasi-electrostatic field generated in the quasi-electrostatic field generating step and applied to an object to be measured and an electric field corresponding to a potential change caused by a dynamic reaction inside the object to be measured; and an extracting step to extract the potential change from the result of interaction detected in the quasi-electrostatic field detecting step. 
     According to the present invention, the measuring apparatus to measure a predetermined object to be measured, comprises: quasi-electrostatic field generating means generating a quasi-electrostatic field of higher field strength as compared with a radiated electric field and an induced electromagnetic field; quasi-electrostatic field detecting means detecting a result of interaction between the quasi-electrostatic field generated by the quasi-electrostatic field generating means and applied to an object to be measured and an electric field corresponding to a potential change caused by a dynamic reaction inside the object to be measured; and extracting means extracting the potential change from the result of interaction detected by the quasi-electrostatic field detecting means, whereby different dynamic reactions can be simultaneously measured and hence much information inside the object to be measured can be simultaneously obtained. 
     According to the present invention, the measuring method to measure a predetermined object to be measured, comprises: a quasi-electrostatic field generating step generating a quasi-electrostatic field of higher field strength as compared with a radiated electric field and an induced electromagnetic field; a quasi-electrostatic field detecting step detecting a result of interaction between the quasi-electrostatic field generated in the quasi-electrostatic field generating step and applied to an object to be measured and an electric field corresponding to a potential change caused by a dynamic reaction inside the object to be measured; and an extracting step extracting the potential change from the result of interaction detected in the quasi-electrostatic field detecting step, whereby different dynamic reactions can be simultaneously obtained and hence much information inside the object to be measured can be simultaneously obtained. 
    
    
     
       BRIEF DESCRIPTION OF THE DRAWINGS 
         FIG. 1  is a schematic diagram showing a simulation result (1); 
         FIG. 2  is a schematic diagram showing a simulation result (2); 
         FIG. 3  is a schematic diagram showing a simulation result (3); 
         FIG. 4  is a schematic diagram showing a relative change in each electric field strength (1 (MHz)) with respect to distance; 
         FIG. 5  is a schematic diagram showing a relative change in each electric field strength (10 (MHz)) with respect to distance; 
         FIG. 6  is a schematic diagram showing a quasi-electrostatic field scale (1). 
         FIG. 7  is a schematic diagram showing a quasi-electrostatic field scale (2). 
         FIG. 8  is a schematic block diagram showing a configuration of a measuring apparatus according to the present embodiment; 
         FIG. 9  is a schematic diagram showing a configuration of an electrode for surface measurement; 
         FIG. 10  is a schematic diagram showing an arrangement state of the electrode for surface measurement; 
         FIG. 11  is a flow chart showing a measurement processing procedure; 
         FIG. 12  is a schematic block diagram showing a configuration of a measuring apparatus according to a further embodiment; and 
         FIG. 13  is a schematic diagram showing a state of measurement according to the further embodiment. 
     
    
    
     BEST MODE FOR CARRYING OUT THE INVENTION 
     In the following, the present invention will be described with reference to the accompanying drawings. 
     The present invention is directed to measure the inner condition of a human body by utilizing the fact that the human body is an electrostatic conductor as suggested by the empirical fact that the static electricity can be physically experienced in everyday life, that electric fields are formed in accordance with potential changes caused by various biological reactions inside the human body, and that the quasi-electrostatic field has high resolution with respect to distance. First, simulation results of this measuring method are shown in  FIG. 1  to  FIG. 3 . 
     (1) Simulation Result 
       FIG. 1  to  FIG. 3  show simulation results in the case where two electrodes EDa and EDb for generating an electric field are arranged in the vicinity of the exterior of a human body, and where a quasi-electrostatic field is generated by applying a voltage to each of the electrodes ED. Noted that in the simulation, the human body is handled by assuming that it has a relative dielectric constant of 50 in a uniform manner. 
       FIG. 1  shows in section a state where no blood vessel exists in the vicinity of the quasi-electrostatic field generated by each of the electrodes ED when the voltage applied to the electrode EDa is 1 (V) and the voltage applied to the electrode EDa is −1 (V). In  FIG. 1 , it can be seen that the equipotential surface whose potential is 0 (V) is generated in the middle between the electrode EDa and the electrode EDb, and that the pattern of the electric field generated by each of the electrodes ED is equivalent to the other. 
     On the other hand,  FIG. 2  shows in section a state where a blood vessel exists in the vicinity of the quasi-electrostatic field generated by each of the electrodes ED when a voltage applied to the electrode EDa is 1 (V) and a voltage applied to the electrode EDb is −1 (V). However, it is assumed that the blood vessel performs pulsation at 1 to 2 (Hz) and a potential of 0.6 (V) (referred to as electric double layer boundary potential) is formed at an interface between the blood vessel wall and the blood in accordance with the pulsation. In  FIG. 2 , it can be seen that the equipotential surface changes to the side of the electrode EDb as compared with the simulation result in  FIG. 1  and the pattern of electric field is also correspondingly changed. This means that a positive potential (electric field) exists inside the human body in the vicinity of each of the electrodes ED, and that this change is a result of interaction between the positive potential and the quasi-electrostatic field generated by each of the electrodes ED. 
       FIG. 3  also shows in section a state at the time when the voltages applied to each of the electrodes ED in  FIG. 2  are reversed (that is, the voltage applied to the electrode EDa is set to −1 (V) and the voltage applied to the electrode EDb is set to 1 (V)). In  FIG. 3 , it can also be seen that the equipotential surface is formed closer to the electrode EDb, similarly to the simulation result shown in  FIG. 2 . This means that the equipotential surface is formed as a result of the interaction between the positive potential (electric field) existing inside the human body in the vicinity of each of the electrodes ED and the quasi-electrostatic fields generated by each of the electrodes ED, similarly to the simulation result shown in  FIG. 2 . 
     It is seen from the simulation results shown in  FIG. 1  to  FIG. 3 , that if quasi-electrostatic field detecting means to detect the above described interaction result is provided in the vicinity of the electrodes ED, the potential change caused by a biological reaction can be detected in non-contacting manner from the detection result of the quasi-electrostatic field detecting means. 
     The strength of the quasi-electrostatic field is inversely proportional to the third power of distance from the electric field sources (electrodes EDa and EDb). This means that the quasi-electrostatic field has a high resolution with respect to the distance. If quasi-electrostatic field generating means to generate a plurality of quasi-electrostatic fields (hereinafter referred to as quasi-electrostatic field scales), each of which has a different reaching distance to the inside of the human body, that is, a different depth range for detecting the effect caused by the biological reaction inside the human body (hereinafter referred to as biological reaction detecting area), is provided by utilizing the property of the quasi-electrostatic field, it becomes possible to measure in layers the inner condition of the human body. Here, before explaining the quasi-electrostatic field scale, the property of the quasi-electrostatic field is explained first. 
     (2) Property of Quasi-Electrostatic Field 
     An electric field is generated as a combined electric field of a radiated electric field which is linearly inversely proportional to the distance from the source, an induced electromagnetic field which is inversely proportional to the square of the distance from the source and a quasi-electrostatic field which is inversely proportional to the third power of the distance from the source. 
       FIG. 4  shows a result obtained by graphically illustrating the relationship of the relative strength of each of the radiated electric field, the induced electromagnetic field, the quasi-electrostatic field with respect to the distance. However, in  FIG. 4 , the relationship between the relative strength of each electric field at 1 (MHz) and the distance is shown in a logarithmic scale. 
     As can be seen from  FIG. 4 , there exists a distance (hereinafter referred to as field strength boundary point) at which the relative strengths of the radiated electric field, the induced electromagnetic field and the quasi-electrostatic field are equal to each other. In this case, at a position far away from the field strength boundary point, the radiated electric field is dominant (in the state where the strength of the radiated electric field is higher than those of the induced electromagnetic field and the quasi-electrostatic field), while at a position nearer than the field strength boundary point, the quasi-electrostatic field is dominant (in the state where the strength of the quasi-electrostatic field is higher than those of the radiated electric field and the induced electromagnetic field). 
     In deriving the field strength from a maxwell equation, the field strength boundary point can be expressed by the following formula, where r (m) is the distance and k (1/m) is the wave number. 
     
       
         
           
             
               
                 
                   r 
                   = 
                   
                     1 
                     k 
                   
                 
               
               
                 
                   ( 
                   1 
                   ) 
                 
               
             
           
         
       
     
     Then, the wave number k in formula (1) can be expressed by the following formula, where v (m/s) is the propagation velocity of the electric field in a medium and f (Hz) is the frequency. 
     
       
         
           
             
               
                 
                   k 
                   = 
                   
                     
                       2 
                        
                       π 
                        
                       
                           
                       
                        
                       f 
                     
                     v 
                   
                 
               
               
                 
                   ( 
                   2 
                   ) 
                 
               
             
           
         
       
     
     The propagation velocity v of the electric field is expressed by the following formula, where c (m/s) is the light velocity (c=3×10 8 ), and ∈ is the relative dielectric constant of the medium. 
     
       
         
           
             
               
                 
                   v 
                   = 
                   
                     c 
                     
                       ɛ 
                     
                   
                 
               
               
                 
                   ( 
                   3 
                   ) 
                 
               
             
           
         
       
     
     Thus, the field strength boundary point can be expressed by the following formula obtained by substituting formula (2) and formula (3) into formula (1) and by arranging the formula resulting from the substitution. 
     
       
         
           
             
               
                 
                   r 
                   = 
                   
                     c 
                     
                       2 
                        
                       π 
                        
                       
                           
                       
                        
                       
                         f 
                         · 
                         
                           ɛ 
                         
                       
                     
                   
                 
               
               
                 
                   ( 
                   4 
                   ) 
                 
               
             
           
         
       
     
     As can be seen from formula (4), in the case where the space of the quasi-electrostatic field whose strength is higher than those of the radiated electric field and the induced electromagnetic field is increased, the frequency is closely related, and hence in a lower frequency, the space of the quasi-electrostatic field whose strength is higher than those of the radiated electric field and the induced electromagnetic field becomes larger (that is, the distance up to the field strength boundary point shown in  FIG. 4  becomes longer as the frequency becomes lower (that is, the position is shifted to the right)). On the other hand, in a higher frequency, the space of the quasi-electrostatic field whose strength is higher than those of the radiated electric field and the induced electromagnetic field becomes smaller (that is, the distance up to the field strength boundary point shown in  FIG. 4  becomes shorter as the frequency becomes higher (that is, the position is shifted to the left)). 
     For example, when the frequency of 10 (MHz) is selected, assuming that the relative dielectric constant of a human body is 50 in a uniform manner, the quasi-electrostatic field is dominant in a position nearer than 0.675 (m) from the above described formula (4).  FIG. 5  shows a result obtained by graphically illustrating the relationship of the relative strength of each of the radiated electric field, the induced electromagnetic field, the quasi-electrostatic field with respect to the distance in the case where the frequency of 10 (MHz) is selected. 
     As can be seen from  FIG. 5 , in the case where the greatest biological reaction detection area from the electric field source (electrodes EDa and EDb) (the depth range for detecting the effect of the biological reaction inside a human body) is set for example to 0.01 (m), the strength of the quasi-electrostatic field in a position between the electric field source and the position of 0.01 (m) is larger than the strength of the induced electromagnetic field by about 18.2 (dB). Therefore, it can be considered that the quasi-electrostatic field in this case is not affected by the induced electromagnetic field and the radiated electric field. 
     Here, utilizing the above described property of the quasi-electrostatic field, there is described a method for generating a quasi-electrostatic field scale to detect the effect of the biological reaction in the region from the surface of a human body up to a position 0.01 (m) inside the surface of the human body with an interval of 0.001 (m), when the detection is performed from the surface of the human body up to the position of 0.01 (m) inside the surface, for example as shown in  FIG. 6 . 
     (3) Quasi-Electrostatic Field Scale 
     As shown in  FIG. 6 , a reference frequency of 10 (MHz) is assigned to the depth of 0.001 (m) which corresponds to a minimum biological reaction detecting area from the surface of the human body, and each time the biological reaction detecting area (that is the depth from the surface of the human body) is successively increased by every depth of 0.001 (m), a frequency corresponding to the detecting area is assigned. In this manner, the biological reaction detecting area of the quasi-electrostatic field can be controlled so as to correspond to the depth of the object to be measured by using the frequencies. 
     However, in this case, the space in which the quasi-electrostatic field is dominant becomes smaller as the frequency becomes higher, (that is, the field strength boundary point shown in  FIG. 4  is shifted to the left), so that the difference between the field strengths of the quasi-electrostatic field and the induced electromagnetic field is smaller than 18.2 (dB) in the vicinity of the end of the biological reaction detecting area corresponding to the high frequency. As a result, the field strength of the quasi-electrostatic field scale serving as an indicator for measuring the effect of the biological reaction becomes unstable, and thereby the reliability of measuring accuracy is impaired. 
     In this case, if the outputs are adjusted so that the field strength at the field strength boundary point corresponding to each frequency f (r)  higher than 10 (MHz) matches with the field strength of the biological reaction detecting area (at the depth of 0.001 (m) from the electrode) corresponding to the frequency of 10 (MHz), it is possible to secure the reliability of measuring accuracy because the quasi-electrostatic field becomes stable. 
     That is, in the case where a sinusoidal wave voltage is outputted to a pair of electrodes for electric field generation to generate a quasi-electrostatic field oscillating in accordance with the frequency of the sinusoidal wave voltage from the electrodes, assuming that a coefficient for performing the above described output adjustment (hereinafter referred to as output adjustment coefficient) is A (r) , the field strength E (r)  of the quasi-electrostatic field in a biological reaction detecting area (distance) r (m) from the pair of electrodes is expressed by the following formula. 
     
       
         
           
             
               
                 
                   
                     E 
                     
                       ( 
                       r 
                       ) 
                     
                   
                   = 
                   
                     
                       A 
                       
                         ( 
                         r 
                         ) 
                       
                     
                     
                       r 
                       3 
                     
                   
                 
               
               
                 
                   ( 
                   5 
                   ) 
                 
               
             
           
         
       
     
     When the biological reaction detecting area (distance) r in formula (5) is modified in accordance with the above described formula (4) relating to the field strength boundary point, the following formula can be obtained. 
     
       
         
           
             
               
                 
                   
                     E 
                     
                       ( 
                       r 
                       ) 
                     
                   
                   = 
                   
                     
                       
                         A 
                         
                           ( 
                           r 
                           ) 
                         
                       
                       · 
                       c 
                     
                     
                       
                         ( 
                         
                           2 
                            
                           π 
                            
                           
                               
                           
                            
                           
                             f 
                             · 
                             
                               ɛ 
                             
                           
                         
                         ) 
                       
                       3 
                     
                   
                 
               
               
                 
                   ( 
                   6 
                   ) 
                 
               
             
           
         
       
     
     The frequency f (r)  may be determined so that the field strength of the field strength boundary point corresponding to each frequency f (r)  higher than 10 (MHz) matches with the field strength in the biological reaction detecting area (at 0.001 (m) from the electrode) corresponding to the frequency of 10 (MHz). Thus, the following formula is established. 
     
       
         
           
             
               
                 
                   
                     
                       
                         
                           A 
                           0.001 
                         
                         = 
                           
                          
                         
                           1 
                           
                             
                               [ 
                               
                                 c 
                                 
                                   2 
                                    
                                   
                                     π 
                                     · 
                                     10 
                                   
                                   × 
                                   
                                     
                                       10 
                                       6 
                                     
                                     · 
                                     
                                       ɛ 
                                     
                                   
                                 
                               
                               ] 
                             
                             3 
                           
                         
                       
                     
                   
                   
                     
                       
                         = 
                           
                          
                         
                           1 
                           
                             
                               [ 
                               
                                 c 
                                 
                                   2 
                                    
                                   π 
                                    
                                   
                                       
                                   
                                    
                                   
                                     
                                       f 
                                       r 
                                     
                                     · 
                                     
                                       ɛ 
                                     
                                   
                                 
                               
                               ] 
                             
                             3 
                           
                         
                       
                     
                   
                 
               
               
                 
                   ( 
                   7 
                   ) 
                 
               
             
           
         
       
     
     By arranging the formula (7), the following formula is obtained. 
     
       
         
           
             
               
                 
                   
                     A 
                     r 
                   
                   = 
                   
                     
                       
                         [ 
                         
                           
                             10 
                             × 
                             
                               10 
                               6 
                             
                           
                           
                             f 
                             r 
                           
                         
                         ] 
                       
                       3 
                     
                      
                     
                       A 
                       0.001 
                     
                   
                 
               
               
                 
                   ( 
                   8 
                   ) 
                 
               
             
           
         
       
     
     Using the formula (8), it is possible to determine the output coefficient A (r)  at the time of outputting the sinusoidal wave voltage of frequency f (r)  corresponding to the biological reaction detecting area (distance) r. 
     Further, the frequency f (r)  corresponding to each biological reaction detecting area (distance) r for each depth of 0.001 (m) successively provided from the electrodes for generating the quasi-electrostatic field can be expressed by the following formula. 
     
       
         
           
             
               
                 
                   
                     
                       A 
                       0.001 
                     
                      
                     
                       1 
                       
                         0.001 
                         3 
                       
                     
                   
                   = 
                   
                     
                       A 
                       r 
                     
                      
                     
                       1 
                       
                         r 
                         3 
                       
                     
                   
                 
               
               
                 
                   ( 
                   9 
                   ) 
                 
               
             
           
         
       
     
     By modifying the output coefficient A (r)  in formula (9) in accordance with the above described formula (8), the following formula is obtained. 
     
       
         
           
             
               
                 
                   
                     
                       A 
                       0.001 
                     
                      
                     
                       1 
                       
                         0.001 
                         3 
                       
                     
                   
                   = 
                   
                     
                       
                         [ 
                         
                           
                             10 
                             × 
                             
                               10 
                               6 
                             
                           
                           
                             f 
                             r 
                           
                         
                         ] 
                       
                       3 
                     
                      
                     
                       A 
                       0.001 
                     
                      
                     
                       1 
                       
                         r 
                         3 
                       
                     
                   
                 
               
               
                 
                   ( 
                   10 
                   ) 
                 
               
             
           
         
       
     
     Then, the output coefficient A (r)  can be determined by using the following formula which is obtained by arranging formula (10). 
     
       
         
           
             
               
                 
                   
                     
                       f 
                       r 
                     
                      
                     
                       
                         0.01 
                         r 
                       
                       · 
                       10 
                     
                     × 
                     
                       10 
                       6 
                     
                   
                   = 
                   
                     
                       10 
                       × 
                       
                         10 
                         3 
                       
                     
                     r 
                   
                 
               
               
                 
                   ( 
                   11 
                   ) 
                 
               
             
           
         
       
     
       FIG. 7  shows a result obtained by graphically illustrating the quasi-electrostatic field scale generated on the basis of each of the above described conditions determined in this manner. However, in  FIG. 7  for reasons of clarity, the biological reaction detecting areas (distances) for each depth of 0.001 (m) are not shown, but the quasi-electrostatic fields corresponding to only predetermined biological reaction detecting areas (at 0.001 (m), 0.002 (m), 0.004 (m), 0.006 (m), 0.008 (m), 0.01 (m)) are shown. In addition, the vertical axis (field strength) in  FIG. 7(A) , and the vertical axis (field strength) and the horizontal axis (distance) in  FIG. 7  (B) are shown in a logarithmic scale. As can be seen from  FIG. 7 , when the field strength of a quasi-electrostatic field is fixed for example to the value at the field strength boundary point as a predetermined reference value, the biological reaction detecting area (distance) of the quasi-electrostatic field can be accurately controlled by means of the frequency, so as to correspond to the depth of the object to be measured. 
     Noted that the case ( FIG. 6 ) where the quasi-electrostatic field is generated for each depth of 0.001 (m) from the electrodes for electric field generation is described, but in practice, the size of each depth in which the quasi-electrostatic field is generated is selected in consideration of the distance of the effect of the biological reaction to be detected from the surface of the human body. In this case, after formula (8) and formula (11) are derived on the basis of the selection result, the output adjustment factor and the frequency for generating the quasi-electrostatic field scale having reliability are determined, respectively. 
     In this manner, the quasi-electrostatic field generating means is capable of generating the quasi-electrostatic field scale having reliability as an indicator for measuring the effect of the biological reaction. 
     In addition, if the quasi-electrostatic field detecting means is made to detect the result of interaction with the potential change due to the biological reaction within the biological reaction detecting area (distance) corresponding to each frequency of the quasi-electrostatic field scale, the potential change due to the biological reaction inside the human body can be measured in layers. 
     (4) Configuration of Measuring Apparatus 
       FIG. 8  shows a measuring apparatus  1  according to the present embodiment, having quasi-electrostatic field generating means and quasi-electrostatic field detecting means, as described above. That is, in the measuring apparatus  1 , the quasi-electrostatic field generating means comprises: an output source  2  (hereinafter referred to as alternating voltage output source) outputting a plurality of sinusoidal wave voltages (hereinafter referred to as alternating voltages) respectively corresponding to a plurality of frequencies; a pair of electrodes for electric field generation  4   a  and  4   b  which are connected to the alternating voltage output source  2 , and which are arranged at a predetermined position on the surface of a human body via a thin insulating sheet  3  whose dielectric constant is selected so as to be close to that of the air; and an output adjusting section  5  controlling the output of the alternating voltage output source  2 . 
     Each of the sinusoidal wave voltages of alternating voltage in the alternating voltage output source  2  is selected to correspond to each of the frequencies determined in accordance with the above described formula (8). Further, the output adjusting section  5  is arranged to output each of the sinusoidal wave voltages of alternating voltage for every unit time, successively from the sinusoidal wave voltage with lower frequency. At this time, each sinusoidal wave voltage is correspondingly adjusted in accordance with the output adjusting coefficient determined by the above described formula (11) and thereafter outputted to the electrodes for electric field generation  4   a  and  4   b.    
     As a result, from the electrodes for electric field generation  4   a  and  4   b , the quasi-electrostatic field scales having reliability are successively generated in the time division manner from a quasi-electrostatic field scale having a smaller biological reaction detecting area (distance). In this case, the quasi-electrostatic field with a frequency corresponding to the biological reaction detecting area including a blood vessel VE is changed by the effect of the potential change (electric double layer boundary potential) caused by the biological reaction of the blood vessel VE. At the same time, the quasi-electrostatic fields of each frequency corresponding to the biological reaction detecting areas including various cells (not shown) inside the human body are changed by the effect of the potential charge caused by the biological reactions (for example, neurone stimulation in a nerve cell, and electron transport system in predetermined cells) in the various cell levels in the inside of the human body, respectively. 
     On the other hand, in the measuring apparatus  1 , quasi-electrostatic field detecting means is constituted by a quasi-electrostatic field detecting section  15  which detects a change of the quasi-electrostatic field of the frequency corresponding to each biological reaction detecting area successively generated by the electrodes for electric field generation  4   a  and  4   b , as a signal S 1  (hereinafter referred to as field strength change signal) via electrodes for electric field detection  11   a ,  11   b , and amplifiers  12   a ,  12   b . Also, analog digital converters (ADCs)  13   a ,  13   b  convert the field strength change signal S 1  to detection data D 1  (hereinafter referred to as field strength change data), and send the detection data to a measuring section  20 . 
     In this case, the measuring section  20  performs measurement so as to extract a potential change larger than a predetermined set level out of potential changes caused by the biological reaction for each biological reaction detecting area corresponding to each frequency, by applying FFT processing to the field strength change data D 1  supplied from the ADCs  13 , and sends the measurement result as data D 2  (hereinafter referred to as tomographic biological reaction data) to a living body tomogram preparing section  30 . 
     The set level is arranged to be set by the user, and is set for example to the potential change of ±5 (mV) or more. Therefore, a change in the nerve action potential caused by neurone stimulation, a change in the electric double layer boundary potential by the pulsation of a blood vessel, and the like are made as the object to be extracted, and in this case, the tomographic biological reaction data D 2  are made to be data in which the potential changes due to minute biological reactions, for example an electron transport system in the predetermined cells and the like, are eliminated. 
     The living body tomogram preparing section  30 , generates data of living body tomogram (hereinafter referred to as living body tomogram data) D 3  by performing a living body tomogram preparing processing using for example an algebraic method on the basis of the tomographic biological reaction data D 2 , and outputs the living body tomogram data to a display device (not shown). As a result, the state of biological reactions caused by a blood vessel, a nerve and the like under the electrodes for electric field generation  4   a  and  4   b , corresponding to the tomographic biological reaction data D 2 , are displayed. 
     In this manner, the measuring apparatus  1  is capable of simultaneously noninvasively measuring different biological reactions for each layer inside the human body, and of providing the measurement result as information. 
     In addition to the above described configuration, the measuring apparatus  1  comprises a conductive shielding section SL 1  surrounding the electrodes for electric field generation  4   a  and  4   b  in a state electrically separated from the electrodes  4   a  and  4   b , and conductive shielding sections SL 2 , SL 3  surrounding the electrodes for electric field detection  11   a ,  11   b  in a state electrically separated from the electrodes  11   a ,  11   b.    
     As a result, in the measuring apparatus  1 , it is possible to avoid as much as possible the state where the external noise other than the field strength change in the quasi-electrostatic field scale (quasi-electrostatic field with a substantially fixed field strength for each distance corresponding to each of the plurality of frequencies) is detected. Thereby, it is possible to accurately measure the potential change of the biological reaction of very trace amount. 
     Further, in the measuring apparatus  1  according to the present embodiment, as shown in  FIG. 9 , the electrodes for electric field detection  11   a ,  11   b  corresponding to the adjoining electrodes for electric field generation  4   a ,  4   b  are linearly arranged so as to be formed as a unit of electrode group ME (hereinafter referred to as unit measuring electrode), and a set of the electrode groups (hereinafter referred to as surface measuring electrode) FME is formed by arranging the unit measuring electrodes in k rows on the same surface. 
     In addition, in the measuring apparatus  1 , for example as shown in  FIG. 10 , a plurality of surface measuring electrodes FMEi are provided in mutually adjoining state via the insulating sheet  3 . 
     In this case, the electrodes for electric field generation  4   a ,  4   b  (i×k sets of electrodes  4   a ,  4   b ) of each unit measuring electrode ME 1  to MEk in each surface measuring electrode FMEi are connected to the common alternating voltage output source  2 , respectively, while the electrodes for electric field detection  11   a ,  11   b  (i×k sets of electrodes  11   a ,  11   b ) are connected to commonly corresponding amplifiers  12   a ,  12   b  ( FIG. 8 ), respectively. 
     As a result, in the measuring apparatus  1 , it is possible to measure different biological reactions for each layer-inside the human body over a wider range in real time, whereby for example, a bloodstream and a nerve flow can be dynamically measured so as to be simultaneously followed. 
     (5) Measurement Processing Procedure 
     Here, the measurement processing in the control section  40  comprising the output adjusting section  5  and the measuring section  20 , is performed in accordance with a measurement processing procedure RT 1  shown in  FIG. 11 . 
     That is, when the main power supply of the measuring apparatus  1  is switched on, the control section  40  starts the measurement processing procedure RT 1 , and selects in step SP 1  the surface measuring electrode FME 1  ( FIG. 10 ) as the electrode to which a quasi-electrostatic field scale is generated. After selecting the unit measuring electrode ME 1  ( FIG. 9 ) in step SP 2 , the control section  40  selects in step SP 3  a sinusoidal wave voltage with a minimum frequency f1 ( FIG. 6 ) as a frequency to be outputted to the electrodes for electric field generation  4   a  and  4   b  of the unit measuring electrode ME 1  ( FIG. 9 ). In step SP 4 , the control section  40  outputs the selected sinusoidal wave voltage to the electrodes for electric field generation  4   a  and  4   b.    
     In this case, the quasi-electrostatic fields ( FIG. 6 ) of the biological reaction detecting area up to 0.001 (m) from each of the electrodes for electric field generation  4   a  and  4   b  are generated, so that when a blood vessel and the like is present in each layer inside the human body under the electrodes for electric field generation  4   a  and  4   b , the quasi-electrostatic field interacts with the electric field corresponding to the potential change due to the biological reaction of the blood vessel and the like. 
     Then, in step SP 5 , the control section  40  temporarily stores in an internal memory the field strength change data D 1  ( FIG. 8 ) supplied via the corresponding electrodes for electric field detection  11   a  and  11   b  as a detection result of the change in the strength of the quasi-electrostatic field in the biological reaction detecting area. In step SP 6 , the control section  40  judges whether a predetermined period of time has elapsed from the start of the output operation in step SP 4 , and when an affirmative result is obtained here, stops outputting the sinusoidal wave voltage in step SP 7 . 
     Subsequently, the control section  40  applies in step SP 8  a frequency analyzing processing to the field strength change data D 1  temporarily stored in step SP 5  and thereby performs measurement so as to extract the potential change due to the biological reaction in the biological reaction detecting area up to 0.001 (m), which potential change is larger than a set level and temporarily stores the measurement result in the internal memory. Then, in step SP 9 , the control section  40  judges whether sinusoidal wave voltages of all frequencies fn have been outputted to the electrodes for electric field generation  4   a  and  4   b.    
     When a negative result is obtained here, this means that the extraction of the potential change due to the biological reaction in all biological reaction detecting areas under the unit measuring electrode ME 1  ( FIG. 9 ) has not yet completed. At this time, the control section  40  returns to step SP 3 , and changes the selection of frequency to be outputted from frequency f1 to the subsequent frequency f2, and then repeats the above described processing. 
     In this manner, when obtaining an affirmative result in step SP 9  as a result of repeating the above described processing for sinusoidal wave voltages of all frequencies f1 to fn for the electrodes for electric field generation  4   a  and  4   b  of the unit measuring electrode ME 1  ( FIG. 9 ), the control section  40  judges in step SP 10  whether extraction results of the potential change due to the biological reaction in all unit measuring electrodes ME 1  to MEk have been obtained. 
     When a negative result is obtained here, this means that the extraction of the potential change due to the biological reaction in all biological reaction detecting areas under a surface measuring electrode FME 1  ( FIG. 10 ) has not yet completed. At this time, the control section  40  returns to step SP 2 , and changes the selection of electrodes to which sinusoidal wave voltages are generated, from the unit measuring electrode ME 1  to the subsequent unit measuring electrode ME 2 , and then repeats the above described processing. 
     In this manner, when obtaining an affirmative result in step SP 10  as a result of repeating the above described processing for all electrodes of unit measuring electrode ME 1  to MEk of the surface measuring electrode FME 1  ( FIG. 10 ), the control section  40  judges in step SP 11  whether extraction results of the potential change due to the biological reaction in all surface measuring electrodes FME 1  to FMEi have been obtained. 
     When a negative result is obtained here, this means that the extraction of the potential change due to the biological reaction in all biological reaction detecting areas under all the surface measuring electrodes FME 1  to FMEi ( FIG. 10 ) has not yet completed. At this time, the control section  40  returns to step SP 1 , and changes the selection of electrodes to which sinusoidal wave voltages are generated, from the surface measuring electrode FME 1  to the subsequent surface measuring electrode FME 2 , and then returns to step SP 1  and repeats the above described processing. 
     In this manner, when obtaining an affirmative result in step SP 11  as a result of repeating the above described processing operation for all the surface measuring electrodes FME 1  to FMEi ( FIG. 10 ), the control section  40  generates in step SP 12  tomographic biological reaction data D 2  on the basis of potential changes due to the biological reaction in all biological reaction detecting areas under all the surface measuring electrodes FME 1  to FMEi temporarily stored in step SP 8 , and sends the generated data to the living body tomogram preparing section  30 . After this sending operation, the control section  40  returns to step SP 13  and terminates this measurement processing procedure RT 1 . 
     In this manner, the control section  40  is arranged to perform the measuring processing. 
     (6) Operation and Effect of Present Embodiment 
     In the above described configuration, the measuring apparatus  1  outputs a plurality of sinusoidal wave voltages, each of which has a predetermined frequency, successively from a voltage with lower frequency for every unit time, from the alternating voltage output source  2  to the electrodes for electric field generation  4   a  and  4   b , and thereby generates quasi-electrostatic fields oscillating correspondingly to the frequencies in the time division manner in the state where the field strength of the quasi-electrostatic fields is more dominant than that of the induced electromagnetic field. 
     Then, the measuring apparatus  1  detects the result of interaction between the quasi-electrostatic fields which are generated by the electrodes for electric field generation  4   a  and  4   b  and applied to the human body, and the electric field corresponding to the potential change caused by the biological reaction inside the human body, and performs measurement so as to extract the potential change from the interaction result. 
     Therefore, in this measuring apparatus  1 , it is possible simultaneously detect different biological reactions as potential changes due to the different biological reactions, such as an electric double layer boundary potential of a blood vessel, a nerve action potential and the like, so that much information inside the human body can be simultaneously obtained. 
     In this case, in the measuring apparatus  1 , the outputs of the sinusoidal wave voltage to the electrodes for electric field generation  4   a  and  4   b , each of which outputs corresponds to each of the frequencies, are adjusted so that the strength of each quasi-electrostatic field generated at each distance corresponding to each frequency becomes a predetermined reference field strength. 
     Therefore, in the measuring apparatus  1 , the strength of the quasi-electrostatic field used as an indicator for measuring the effects of the biological reaction can be uniformly generated in the state where the strength of the quasi-electrostatic field is higher than that of the induced electromagnetic field, and hence, it is possible to generate the stable quasi-electrostatic field having reliability in measuring accuracy. 
     Further, in this case, the measuring apparatus  1  is configured so that a pair of electrodes for generation and a pair of electrodes for detection are formed as a unit electrode, and that the plurality of unit electrodes are formed on a surface. Therefore, in the measuring apparatus  1 , the biological reactions which are different for each layer inside the human body, can be measured over a wide range and in real time, as a result of which for example, a bloodstream, a nerve flow and the like can be dynamically measured so as to be followed. 
     In the above described configuration, the quasi-electrostatic field of higher strength is generated as compared with the radiated electric field and the induced electromagnetic field, and the result of interaction between the quasi-electrostatic field thus generated and applied to the human body, and the electric field caused by the biological reaction inside the human body is detected, so that the measurement is performed so as to extract the potential change from the interaction result. Thereby, different biological reactions can be simultaneously detected and thus much information inside the human body can be simultaneously obtained, as a result of which the inner condition of an object to be measured can be more accurately grasped. 
     (7) Other Embodiments 
     It is to be noted that in the above described embodiment, there is described the case where the quasi-electrostatic field generating means to generate the quasi-electrostatic field of higher field strength as compared with the radiated electric field and the induced electromagnetic field is constituted by the alternating voltage output source  2 , the electrodes for electric field generation  4   a  and  4   b , and the output adjusting section  5 , as shown in  FIG. 8 , but the present invention is not limited to the case, and the quasi-electrostatic field generating means may be realized by other various constitutions. 
     Further, as the generating method of the quasi-electrostatic field generating means for generating the quasi-electrostatic field of higher field strength as compared with the radiated electric field and the induced electromagnetic field, the output adjusting section  5  as output adjusting means is arranged to make the alternating voltage output source  2  output to the electrodes for electric field generation  4   a  and  4   b , sinusoidal wave voltages successively from a voltage with lower frequency in time division manner, thereby generating the quasi-electrostatic fields which makes it possible to obtain the higher field strength as compared with and the induced electromagnetic field, at each distance corresponding to each of the plurality of frequencies in time division manner. However, the present invention is not limited to the case, and the output adjusting section  5  may output to the electrodes for electric field generation  4   a  and  4   b  the result of combination of each of the sinusoidal wave voltages, so as to generate the quasi-electrostatic fields which make it possible to obtain the higher field strength as compared with the induced electromagnetic field at each distance corresponding to each of the plurality of frequencies, not in time division manner but simultaneously. In this case, the quasi-electrostatic fields which are the result of combination of the plurality of frequency components are generated simultaneously so that the detected result includes the plurality of frequency components. Thus, it is possible to obtain the same effect as in the above described embodiment by decomposing the detected result for each frequency by the FFT processing. 
     Further, as the generating method of the quasi-electrostatic field generating means for generating the quasi-electrostatic field of higher field strength as compared with the radiated electric field and the induced electromagnetic field, only a predetermined sinusoidal voltage of the alternating voltage output source  2  may be outputted, whereby the quasi-electrostatic field is selectively generated at a predetermined position inside the human body. 
     Further, in the above described embodiment, there is described the case where a human body is taken as an object to be measured so that the biological reaction inside the human body is measured. However, the present invention is not limited to the case, and the present invention may be arranged to measure for example the biological reaction inside animals, plants and the like by taking these as objects to be measured, to measure water flows in certain points of ground by taking these as an object to be measured, to measure the biological reaction of survivors present inside collapsed matters collapsed by the disaster and the like by taking these as objects to be measured, to measure a predetermined dynamic response of predetermined fine electronic devices by taking these as objects to be measured, and to measure a predetermined dynamic reaction present in predetermined objects to be conveyed by taking these as objects to be measured, and the like. In addition to these, the present invention may also measure various dynamic reactions inside various objects to be measured. 
     Further, in the above described embodiment, there is described the case where the electrodes for electric field detection  11   a ,  11   b  and amplifiers  12   a ,  12   b  are arranged as the quasi-electrostatic field detecting means to detect the result of interaction between the quasi-electrostatic field applied to an object to be measured and the electric field corresponding to the potential change caused by the dynamic reaction inside the object to be measured. However, the present invention is not limited to the case. As shown in  FIG. 12  in which the portions corresponding to those in  FIG. 8  are denoted by the same reference characters respectively, the interaction result may be detected by an impedance change detecting section  105  which detects an impedance change based on measured values obtained by an ammeter  103  connected between one of the electrodes for electric field generation  4   b  and the alternating voltage output source  2 , and by a voltmeter  104  connected between the outputs of the alternating voltage output source  2 , via the ADC  106 . 
     Further, in this case, the interaction result may also be detected by other various kinds of quasi-electrostatic-field detecting means, such as for example, an induction electrode type field strength meter to detect a voltage induced as the induced voltage, an induction electrode modulation amplification type field strength meter in which a DC signal obtained by an induction electrode is converted to AC by using a chopper circuit, an oscillating capacity and the like, an electro-optical effect type field strength meter detecting a change in optical propagation characteristics caused in a material having the electro-optical effect by applying an electric field to the material, an electrometer, a shunt resistance type field strength meter, a current-collecting type field strength meter, and the like. 
     Further, in the above described embodiment, there is described the case where the measuring section  20  performing FFT processing is applied as the extracting means to extract from the interaction result the potential change caused by the dynamic reaction inside the object to be measured. However, the present invention is not limited to the case, and a measuring section performing frequency analysis processing other than FFT may also be applied. 
     Further, in the above described embodiment, there is described the case where a unit measuring electrode ME ( FIG. 9 ) is formed by linearly arranging the electrodes for electric field detection  11   a ,  11   b  corresponding to the electrodes for electric field generation  4   a ,  4   b , and a set of surface measuring electrode FME is formed by arranging the plurality of unit measuring electrodes ME in k rows on the same surface. However, the present invention is not limited to the case, and various unit measuring electrodes ME and surface measuring electrodes FME of which shapes and arrangement states are different from those shown in  FIG. 9  and  FIG. 10 , may also be formed. What is essential is to form a pair of adjoining electrodes for electric field generation  4   a ,  4   b  and a pair of electrodes for electric field detection  11   a ,  11   b  adjoining and corresponding to the electrodes  4   a ,  4   b  as one unit (a unit measuring electrode ME), and to arrange the plurality of units on the same surface. 
     Further, in the above described embodiment, there is described the case where the potential change of a blood vessel or a nerve is measured as the potential change due to the biological reaction in the human body. However, the present invention is not limited to the case, and the potential change due to a certain cell itself may be measured. 
     Specifically, as shown in  FIG. 13 , a pair of unit measuring electrodes ME 1 , ME 2 , each consisting of electrodes for electric field generation  4   a ,  4   b  and electrodes for electric field detection  11   a ,  11   b , each of which electrodes has a size approximately equal to a cell level, are provided so as to make quasi-electrostatic electric fields applied inwardly from the directions different from each other, and the reaching distance (biological reaction detecting areas) of each quasi-electrostatic field applied from both of the unit measuring electrodes ME 1 , ME 2  is successively increased by the output adjusting section  5 . At this time, as described above, an intersection point P of the reaching distances r1, r2 of the quasi-electrostatic fields is detected by the impedance change detecting section  105  on the basis of the change in impedances measured by the electrodes for electric field detection  11   a ,  11   b  via the ammeter  103  and the voltmeter  104 . At this time, the reaching distances (biological reaction detecting areas) of each of the quasi-electrostatic fields applied from both of the unit measuring electrodes ME 1 , ME 2  are fixed, and the potential change due to the biological reaction in the cell at the intersection point is measured by reversely estimating the impedance change before the intersection point is detected, from the impedance change when the intersection point is detected. In this manner, since the potential change of the biological reaction of a specific cell level can be measured, it is possible not only to avoid that as in the conventional patch clamp method, a micropipet is made to be in contact with a cell membrane and the control of the micropipet is performed under an optical microscope, but also to perform noninvasive and non-contacting measurement. 
     Further, in the above described embodiment, there is described the case where the quasi-electrostatic fields are generated from the electrodes for electric field generation  4   a  and  4   b . However, in addition to that, according to the present invention, directivity limiting means to limit the directivity of the quasi-electrostatic fields for example in a linear state may also be provided for the electrodes for electric field generation  4   a ,  4   b . Thereby, it is possible to perform a detecting operation specialized for the result of interaction with the dynamic reaction inside the object to be measured without detecting the result of interaction with external noises, as a result of which the measuring accuracy can be further enhanced. 
     Further, in the above described embodiment, there is described the case where the quasi-electrostatic field is taken as the object to be measured in order to measure the potential change due to the biological reaction inside the human body. However, the present invention is not limited to the case, and a quasi-electrostatic field for treatment may also be generated as the object to be measured simultaneously with the measurement. In this case, it is possible not only to perform the treatment in non-contacting manner but also to measure the effect of the treatment in real time, and to thereby effect simplification at the time of surgery and study. 
     Further, in the above described embodiment, there is described the case where the change of the electric double layer boundary potential caused by the pulsation of a blood vessel is arranged to be measured. However, according to the present invention, in addition to that, it is also possible to measure the pulsation itself by taking a time-base area into account. 
     Further, in the above described embodiment, there is described the case where the living body tomogram preparing section  30  which generates living body tomogram data D 3  on the basis of a measurement result (tomographic biological reaction data D 2 ) and outputs the tomogram data to the display section (not shown), is arranged to be provided. However, the present invention is not limited to the case, and a discriminating section to discriminate an acute lesion and other diseases on the basis of the measurement result may also be provided. By this manner, a simple diagnosis can be performed simultaneously with the measurement. 
     Further, in the above described embodiment, there is described the case where the living body tomogram preparing section  30  which generates living body tomogram data D 3  on the basis of a measurement result (tomographic biological reaction data D 2 ), and outputs the tomogram data to the display section (not shown), is arranged to be provided. However, instead of this, according to the present invention, an authentication information generating section which generates authentication information used in performing a predetermined authentication processing and outputs the authentication information to an external apparatus, may also be provided. Thereby, it is possible to use the biological reaction formed in a pattern specific to a human body as the authentication information so that the confidentiality of information in the external apparatus can be further secured. 
     Further, in the above described embodiment, there is described the case where the result of the interaction between the quasi-electrostatic field generated by the quasi-electrostatic field generating means and applied to a human body and the electric field corresponding to the potential change caused by the biological reaction inside the human body is arranged to be detected, and where the potential change is extracted on the basis of the detection result. However, the present invention is not limited to the case, and for example, as in an example that a shark, a ray and the like detect electric fields (quasi-electrostatic fields) generated in living bodies by means of an organ referred to as ampulla of Lorenzini which is present in their head, to thereby identify a living body as a bait for themselves among the living bodies, it may also be arranged that the potential change caused by the biological reaction inside the living body is directly detected by the above described quasi-electrostatic field detecting means, and the potential change caused by a predetermined biological reaction is extracted from the levels of the detected potential change, by referring for example to a table in which the levels of the potential change and the kinds of the biological reaction are made in advance to correspond to each other. 
     INDUSTRIAL APPLICABILITY 
     The present invention is applicable in the case of noninvasively measuring inner conditions of an object to be measured, such as a living body, a predetermined electronic device and ground.