the present invention will now be described with reference to the preferred embodiments thereof . fig1 is a block diagram showing the schematic structure of the first preferred embodiment of the electronic blood pressure measuring device of the present invention , and fig2 is a block diagram of an electronic blood pressure measuring device to which this invention is applied . in fig1 cuff 31 is formed as a bag or the like to be applied to the arm of a patient , which can be made of rubber of some other suitable flexible material . cuff 31 is connected to a pressure cord 32 . a pressure sensor 33 is connected to cuff 31 by way of a rubber tube or the like and converts the cuff pressure sense thereby into an electric signal . the output of pressure sensor 33 is connected to the input of blood pressure deciding means 35 as well as to pulse wave maximum amplitude extraction means 36 and pulse wave parameter extraction means 34 . outputs from pulse wave parameter extraction means 34 are supplied to blood pressure deciding means 35 , pulse wave maximum amplitude extraction means 36 and pulse wave minimum amplitude extraction means 37 . cuff pressure calculating means 38 receives the outputs from pulse wave maximum amplitude extraction means 36 and pulse wave minimum amplitude extraction means 37 and passes blood pressure values along to blood pressure deciding means 35 . fig2 - 5 describe more completely the aspects of the first preferred embodiment of this invention . in fig2 a cuff 11 is formed as a bag , which may be made of rubber or of some other suitable material , for being wound upon the arm of a patient or of some other person the blood pressure of whom is desired to be measured , and this cuff 11 is connected to an exhaust valve 13 and to a pressurization pump 14 which together make up a pressure system 12 , by way of a rubber tube 15 . a pressure sensor 16 is connected to the cuff 11 by way of the rubber tube 15 and converts the current value of the cuff pressure into an electric signal . the output end of the pressure sensor 16 is connected to an input end of an amplifier 17 and the output electric signal of the pressure sensor 16 or the cuff pressure signal is dc amplified by the amplifier 17 . the output end of the amplifier 17 is connected to an input end of an a / d converter 18 on the one hand and is connected to an input end of a band pass filter 19 on the other hand . the output end of the a / d converter 18 is fed to a cpu 20 , as is the output of the band pass filter 19 , so that the output of the amplifier 17 and the output of the band pass filter 19 are supplied to the cpu 20 after being converted into digital signals by the a / d converter 18 . the cpu 20 , which performs certain processes according to an internal program , has the functions of determining the blood pressure values such as the maximum blood pressure and the minimum blood pressure , and the determined blood pressure values are displayed on a display unit 21 . as a measurement start key which is not shown in the drawing is actuated , the cpu 20 starts the action of the pessurization pump 14 and pressurizes the cuff 11 by a command &# 34 ; a &# 34 ; and controls the amount of air exhaustion from the exhaust valve 13 by a command &# 34 ; b &# 34 ;. and the cuff pressure from the amplifier 17 and the pulse wave component from the band pass filter 19 are read out at a certain sampling timing by commands &# 34 ; c &# 34 ; and &# 34 ; d &# 34 ;. the cpu 20 has the functions of detecting the maximum value and the minimum value of the pulse wave component read out in a certain time interval which is longer than the above mentioned sampling timing time , computing the level difference between the maximum value and the minimum value , extracting cuff pressures corresponding to the maximum value and the minimum value , and computing the average value of these extracted cuff pressures . now , the overall action of the electronic blood pressure measuring device of this embodiment will be described with reference to a flow diagram of the program therefor shown in fig3 . as the action starts by the measurement start key which is not shown in the drawing being pressed , the pressure pump 14 starts its action on receiving the command &# 34 ; a &# 34 ; from the cpu 20 ( in the step st1 ), and the cuff 11 is pressurized until a cuff pressure which is sufficient for measurement builds up ( in the step st2 ). and when the cuff pressure reaches a certain cuff pressure value , the action of the cuff pressure pump 14 stops to terminate the pressurization ( in the step st3 ), and by the command &# 34 ; b &# 34 ; the exhaust valve 13 starts gradual exhaustion of air in the cuff 11 so as to start depressurization of said cuff 11 ( in the step st4 ). and various computing parameter initialization stages are conducted , such as for example clearing the counter for computing the parameters and the registers for storing the maximum values and the minimum values of the cuff pressure and so on ( in the step st5 ). then , the parameters are computed ( in the step st6 ). in this parameter computing process , the maximum value pmax and the minimum value pmin of the pulse wave component read out in the finely divided sampling time intervals ( windows ) are derived and the parameter value h ( i ) for each samplimg time interval is derived as the difference between the maximum value pmax and the minimum value pmin . and , in this process , the cuff pressure a ( i ) for each sampling time interval is also extracted . this computing process is a characteristic of this invention , and its details are described hereinafter . after this computing process , currently the computed parameter h ( i ) and the parameter maximum value hmax up to that time point are compared ( in the step st7 ), and if h ( i ) is greater than hmax the current parameter h ( i ) is stored as a new parameter maximum value hmax ( in the step st8 ) to determine the cuff pressure at that time point as the average blood pressure ( in the step st9 ). and then , the cuff pressure corresponding to the parameter value which corresponds for instance to one half of the parameter maximum value hmax is set as the maximum blood pressure ( in the step st10 ). and then it is determined whether the current parameter value h ( i ) is equal to or less than 70 % of the parameter maximum value hmax up to that point or not ( in the step st11 ). if the parameter is rising , this determination result will be no , and after the interval counter i is incremented by 1 ( in the step st12 ) the system flow returns to the step st6 to compute the parameter for the next time interval . thereafter , until the parameter value stops rising and starts dropping , and becomes 70 % of hmax , the processes in the steps st6 to st12 are repeated . as the parameter h ( i ) reaches 70 % of hmax and diminishes further , the determination result of the step st11 becomes yes and the cuff pressure corresponding to this time point is determined as the minimum blood pressure ( in the step st13 ). and then the blood pressure values determined as average , maximum , and minimum are displayed on the display unit 21 ( in the step st14 ), and the exhaust valve 13 starts rapid exhaustion ( in the step st15 ), to complete the measurement . now , the details of the computing process for the parameters h ( i ) and a ( i ) in the step st6 mentioned above , which may be performed by a subroutine which is invoked , will be described in the following with reference to the subroutine flow diagram shown in fig4 . as the system flow enters the subroutine for computing these parameters , first of all in the step st61 the registers for storing the maximum pressure pmax and the minimum value pmin of the pulse wave component levels and the number of sampling n in each interval are cleared . and the pulse wave component levels p ( n ) entered for each sampling time are read ( in the step st62 ). and the pulse wave component levels p ( n ) which are read are compared with the minimum value pmin of the pulse wave component level up to that point ( in the step st63 ), and if p ( n ) is smaller then the p ( n ) of the current sampling time is stored as pmin ( in the step st64 ). and the cuff pressure a ( n ) at this time point is stored as pres1 ( in the step st65 ). this pres1 is a cuff pressure corresponding to the minimum value of the pulse wave . in the step st63 , if p ( n ) is greater than pmin , the processes performed by the steps st64 and st65 are skipped . in the steps st63 to st65 , minimum value of the pulse wave level is updated . after this updating process for the minimum value , in the step st63 , p ( n ) is compared with the maximum value pmax up to that point , and if p ( n ) is greater then the p ( n ) of the current sampling is stored as pmax ( in the step st67 ). and cuff pressure a ( n ) at this time point is stored as pres2 ( in the step st68 ). this pres2 is a cuff pressure corresponding to the maximum value of the pulse wave . if p ( n ) is less than pmax in the step st66 , the processes performed in the steps st67 and 68 are skipped . in the steps st66 and st68 , the maximum value of the pulse wave level is updated . after the number of detections n is incremented by 1 ( in the step st69 ), it is determined whether this detection number n has exceeded a maximum detection number nmax of the interval or not ( in the step st70 ). if not , the system flow returns to the step st62 and after reading the data p ( n ) of the pulse wave level for te next sampling time the same steps ( i . e . the samesteps st62 through st70 ) are executed again . these processes are repeated until n is equal to nmax + 1 or one time interval is completed . when n is equal to nmax + 1 , the determination result of the step st70 becomes yes . then , the mimimum value of the pulse wave is subtracted from the maximum value pmax of the pulse wave , and the difference or the parameter h ( i ) is computed ( in the step st71 ) on the one hand , and the average value of the cuff pressures pres1 and pres2 corresponding to the maximum and the mimimum values of the pulse wave is computed , and after this average value is set as the cuff pressure pres ( i ) of this time interval the system flow returns to the main routine ( in the step st72 ). the computing processes for the parameter h ( i ) and the corresponding cuff pressure a ( i ) will now be further described with reference to the wave form examples shown in fig5 . in fig5 &# 34 ; p &# 34 ; denotes a pulse wave component and &# 34 ; a &# 34 ; denotes a cuff pressure wave form . w1 , w2 , and so on are time intervals . with respect to the time interval w1 , from the cuff pressure a11 corresponding to the mimimum value of the pulse wave pmin1 and the cuff pressure a12 corresponding to the maximum value of the pulse wave pmax1 , the corresponding cuff pressure of this interval w1 is a1 =( a11 + a12 )// 2 . with respect to the time interval w2 , from the cuff pressure a21 corresponding to the minimum value of the pulse wave pmin2 and the cuff pressure a22 corresponding to the maximum value of the pulse wave pmax2 , the corresponding cuff pressure of this time interval w2 is a2 =( a21 + a22 )/ 2 . therefore , even when there are some fluctuations in the maximum and mimimum values of the pulse wave for different time intervals , the cuff pressures close to the points where the minimum and the maximum values are extracted are determined as the cuff pressure of the corresponding intervals . thus , according to this invention , since the average values of the cuff pressures corresponding to the maximum and the minimum values of the pulse wave component in each of the time intervals for obtaining the parameters are set as the cuff pressures of the corresponding time intervals , a non distorted relationship is obtained between the parameters and the cuff pressures , and an electronic blood pressure measuring device which operates with very little error and with very high precision can be obtained . fig9 is a block diagram of an electronic blood pressure measuring device which is a second preferred embodiment of the electronic blood pressure measuring device of the present invention . ( reference numerals in fig8 through 20 for this second preferred embodiment do not particularly correspond to reference numerals relating to fig1 through 7 for the first preferred embodiment ). in fig9 a cuff 1 is formed as a bag to be wound on the arm of a patient , being as before made of rubber or of some other suitable flexible material , and this cuff 1 is connected to a pressure system 2 comprising an exhaust valve 3 and a pressurization pump 4 by way of a branched rubber tube 5 . a pressure sensor 6 is connected to the cuff 1 by way of the rubber tube 5 and converts the cuff pressure sensed thereby into an electric signal . the output of the pressure sensor 6 is connected to an input end of an amplifier 7 , and the output electric signal of the pressure sensor 6 or the cuff pressure signal is dc amplified by the amplifier 7 . the output end of the amplifier 7 is connected to an input end of an a / d converter 8 on the one hand , and to an input end of a band pass filter 9 on the other hand . the output end of the a / d converter 8 is connected to a cpu 10 , and so is the output of the band pass filter 9 ; and thereby the output of the amplifier 7 and the output of the band pass filter 9 are both supplied to the cpu 10 after being converted into digital signals by the a / d converter 8 . the cpu 10 executes predetermined processes according to an internal program stored therein , and has the functions of determining the blood pressure values such as the maximum blood pressure , the minimum blood pressure , and so on , and determined blood pressure values are displayed on a display unit 11 . when a measurement start key which is not particularly shown in the drawing is actuated , the cpu 10 starts the action of the pressurization pump 4 to pressurize the cuff 1 by issuing a command &# 34 ; a &# 34 ;, and controls the air exhaust from the exhaust valve 3 by issuing a command &# 34 ; b &# 34 ;. and the cuff pressure from the amplifier 7 and the pulse wave component from the band pass filter 9 are read in at certain sampling cycles by commands &# 34 ; c &# 34 ; and &# 34 ; d &# 34 ;. according to this electronic blood pressure measuring device , after the cuff 11 is wound around the arm of the patient , and the pessurization pump 4 is actuated by operating the measurement start key until the cuff pressure reaches a certain level , the pressurization pump 4 is stopped and the air exhaust is gradually started by the exhaust valve 3 . as the cuff pressure gradually drops , the output signal of the pressure sensor 6 becomes as shown in fig3 a and the extracted pulse wave component from the output of the band pass filter 9 or the output from the amplifier 7 becomes as shown in fig3 b . the cpu 10 determines the average blood pressure , the maximum blood pressure , and the minimum blood pressure from the detected cuff pressure and the amplitude value of the pulse wave ( peak value ) according to a flow which will be described hereinafter . now , this action will be described with reference to the flow chart of fig4 . first of all , when the measurement start key is pressed and the action is started , the pressurization pump 4 starts its action by the command &# 34 ; a &# 34 ; ( in the step st1 ), and the cuff 1 is pressurized until a determinate pressure sufficient for measurement is built up ( in the step st2 ). and , when the cuff pressure reaches a certain predetermined cuff pressure , the action of the pressurization pump 4 is stopped and at the same time as stopping the pressurization ( in the step st3 ) the exhaust valve 3 begins gradual air exhaustion by the command &# 34 ; b &# 34 ; to begin depressurization ( in the step st4 ). and by the command &# 34 ; c &# 34 ;, for every t1 ( for instance 100 ms as an example ) the output of the amplifier 7 or the cuff pressure is a / d converted and is stored ( in the step st5 ). likewise , by a command , for each t2 ( for instance 10 ms in the same example ) the output of the band pass filter 9 or the pulse wave component is a / d converted by the a / d converter 8 and is taken in by the cpu and is stored ( in the step st6 ). the discrete data of the pulse wave which has been a / d converted is differentiated for each point ( in the step st7 ). this differentiation is conducted according to the following equation : ## equ1 ## where n = 1 , 2 , 3 and so on , k is a normalization constant ( k = 110 in the illustrative example ), and f ( n ) is an original data with n selected as 5 in the example . fig1 shows the wave forms of the pulse wave before and after the differentiation . fig1 a is a differentiated wave form , and fig1 b is the pulse wave wave form . then the maximum value of the differentiated pulse wave is extracted . specifically , following the differentiation process in the step st7 , it is determined whether the maximum value of the differentiated pulse wave has been detected or not ( in the step st8 ), and this detection of the maximum value of the differentiated pulse wave is repeated until such a value is detected ( in the step st9 ). this process consists of comparing the current differentiated value and the maximum value up to the point and renewing or updating the maximum value if the current value is greater than the previous maximum value , and if the value is not updated for more than a certain time interval ( for instance three seconds ) the value is considered as the maximum value of the differentiated pulse wave . therefore , when the certain time interval has elapsed without the differentiated value being updated , the determination result for the detection of the maximum value of the differentiated pulse wave in the step st10 is no , and the process flow returns to the step st5 and the process of detecting the maximum value of the differentiated pulse wave is repeated on a real time basis . when the maximum value of the differentiated pulse wave is detected , the determination result of the step st10 becomes yes , and the maximum value of the differentiated pulse wave is stored ( in the step st11 ). and the process flow returns to the step st5 , but since the determination result for the detection of the maximum value of the differentiated pulse wave in the step st8 now becomes yes , the process flow moves on to the step st12 and conducts a pulse wave division process . this pulse wave division process consists of setting α percent ( α is equal to 10 to 20 ) of the maximum value of the differentiated pulse wave extracted in the step st9 as a threshold level , finding an intersecting point between this level and the rising curve of the differentiated pulse wave , and setting the point on the pulse wave wave form corresponding to this intersecting point as a division point . the line th shown in fig1 is the threshold level , and d1 , d2 , d3 and so on are division points . and the maximum value of the pulse wave is detected for each of the intervals defined by this division of the pulse wave ( in the step st13 ), and these maximum values of the pulse wave are set as the pulse wave peaks . and the maximum value of these pulse wave peaks are obtained for various division intervals . the detection of the maximum peak value of the pulse wave consists of comparing the current pulse wave peak value to the preceding pulse wave peak values , and if the current pulse wave peak value is greater than the previous ones the greater pulse wave is stored as updating data , and if no updating takes place for more than a certain time interval the pulse wave peak value is stored as the maximum peak value of the pulse wave ( in the step st17 ). the cuff pressure corresponding to this maximum peak value of the pulse wave is stored as an average blood pressure cm . when the maximum peak value of the pulse wave is stored , the determination result on the detection of the maximum peak value of the pulse wave in the step st14 becomes yes , and then it is determined whether or not the pulse wave peak value is equal to or less than β percent ( β is equal to 40 to 60 %) of the maximum peak value ( in the step st18 ). if it is not equal to or less than β %, the process flow returns to the step st5 and the processes including the cuff pressure a / d conversion , storage ( in the step st5 ), pulse wave a / d conversion , storage ( in the step st6 ), the pulse wave peak detection ( in the step st14 ) and so on are repeated . when the pulse wave peak becomes equal to or less than β % of the maximum peak , the determination result of the step st18 becomes yes , meaning that the pulse wave peak value which is necessary for measurement has already been measured in this state , and a command &# 34 ; b &# 34 ; is outputted from the cpu 10 to the exhaust valve 3 . as a result , the exhaust valve 3 starts rapid air exhaustion ( in the step st19 ). thus , the real time processes such as differentiation of the pulse wave , detection of pulse wave peaks , and so on in the depressurization process of the cuff pressure are completed . thereafter , certain processes are executed on the pulse wave peak values obtained in this real time process , and subsequent thereto the process of determining the maximum blood pressure and the minimum blood pressure is to be started . now , the process of determining blood pressures will be described in the following . after rapid air exhaustion , a row of areas ( a ( n )) defined by the envelope lines and the straight lines are computed with respect to the group of data of the extracted pulse wave peaks ( pp ( n )) on the higher cuff pressure side of the pulse wave maximum peak ( pmax ) ( in the step st20 ). a concrete example of the computations of the areas a ( n ) will be described in the following with reference to fig2 . in fig2 , n on the x axis denotes pulse wave serial numbers , while the y axis represents corresponding pulse wave peaks . the area a ( n ) represented by the pulse wave number n is obtained by subtracting an area defined by points ( n - 2 , 0 ), ( n + 2 , pp ( n + 2 )), ( n - 1 , pp ( n - 1 )), ( n , pp ( n )), ( n + 1 , pp ( n + 1 ), ( n + 2 , pp ( n + 2 )), ( n + 2 , 0 ) from a trapezoidal area defined by points ( n - 2 , 0 ), ( n - 2 , pp ( n - 2 )), ( n + 2 , pp ( n - 2 ), and ( n + 2 , 0 ). the trapezoidal area defined by points ( n - 2 , 0 ), ( n - 2 , pp ( n - 2 )), ( n + 2 , pp ( n - 2 ), and ( n + 2 , 0 ) is found as 1 / 2 . 4h ( pp ( n + 2 )+ pp ( n - 2 )) if the interval h is between a point ( i , 0 ) and a point ( i + 1 , 0 ) where i is from n - 2 to n + 1 ). meanwhile the trapezoidal area q ( i ) defined by the points ( i , 0 ), ( i , ppi )), ( i + 1 , pp ( i + 1 ), and ( i + 1 , 0 ) ( where i is from n - 2 to n + 1 ) is q ( i )= 1 / 2h ( pp ( i )+ pp ( i + 1 )). therefore , the area a ( n ) can be expressed by : ## equ2 ## however , if any one of the points ( n - 1 , pp ( n - 1 )), ( n , pp ( n )), and ( n + 1 , pp ( n + 1 )) is above a line connecting the points ( n + 2 , pp ( n + 2 )) and ( n - 2 , pp ( n - 2 )), since it means that the envelope line is within the range of the average blood pressure away from the area corresponding to the maximum blood pressure , a ( n ) is set as zero . these areas a ( n ) are computed for each of the pulse wave numbers by incrementing the pulse wave number n for the pulse wave peaks shown in fig8 b by 1 . and a row or series of areas ( a ( n )) are computed as shown in fig8 c . subsequently , a maximum area is detected from the area series ( a ( n )) ( in the step st21 ), and setting the cuff pressure value corresponding to the group of the pulse wave series which gives the maximum area value as ci ( refer to fig1 ) the maximum blood pressure value cs is determined from the following equation according to the average blood pressure value cm which has already been extracted and stored ( refer to fig1 ) ( in the step st22 ): the maximum blood pressure determined from this equation has been experimentally confirmed to be proper and practical . next , a series of areas a ( n ) surrounded by the envelope line and the straight lines are computed in the same way as in the step st20 with respect to a series of data of the extracted pulse wave peaks pp ( n ) on the lower cuff pressure side of the pulse wave maximum peak ( pmax ) ( in the step st23 ). subsequently , the maximum area is derived from the series of areas a ( n ), ( refer to the right hand side of fig8 c ) ( in the step st24 ), the minimum blood pressure value is determined from the cuff pressure value cd ( refer to fig8 a ) corresponding to the maximum value of the areas ( in the step st25 ). and , the maximum blood pressure and the minimum blood pressure are displayed on the display unit 11 ( in the step st26 ), and the measurement is completed . now , the specific processes in the subroutines invoked from the step st20 to the step st25 in the main flow will be described in the following . explanation of computation of the series of areas on the high cuff pressure side ( in the step st20 ). upon entering the step st20 in the main flow , the pulse wave number n is set to 2 ( in the step st51 ), as shown in the flow chart of fig1 , and 1 is added to n ( in the step st52 ), and it is determined whether or not nmax = n or not ( in the step st53 ). here , nmax is an integer which causes pmax to be equal to pp ( nmax ) ( the cuff pressure corresponding to this nmax is the average blood pressure cm ), and as long as the determination result is no in the step st53 , the computation of the areas on the high cuff pressure side is to be executed . in other words , if the determination result of the step st53 is no , it is determined whether the following inequalities hold or not ( in the step st54 , the step st55 , the step st56 ): ## equ3 ## if any one of these inequalities holds , it means that either pp ( n ), pp ( n - 1 ), or pp ( n + 1 ) is located above the straight line previously identified , and therefore the area a ( n ) is determined as zero ( in the step st57 ). if none of the inequalities holds , then the equation : ## equ4 ## is executed ( in the step st58 ), and after the process flow has returned to the step st52 n is incremented by one and the computation of the areas is repeated . in the step st53 , if nmax is equal to n , the computation of a ( n ) on the higher cuff pressure side is complete and the system flow returns to the main flow . explanation of computation of the maximum area on the high cuff pressure side ( in the step st21 ). upon entering the step st21 in the main flow , as shown in the flow chart of fig1 , the maximum value of the area amax is set to zero ( in the step st61 ). and n is set to 2 ( in the step st62 ) and after unity is added to n ( in the step st63 ) it is determined whether or not nmax is equal to n or not ( in the step st64 ). and until this determination result becomes yes , the maximum value of the area amax is compared with the sequentially read out area values a ( n ) ( in the step st65 ), and if the read out area value a ( n ) is smaller than the maximum value the system flow returns as it is to the step st63 , but if the area value a ( n ) is greater than the maximum value this area value a ( n ) is used for updating the maximum area value amax ( in the step st66 ). and the value of n at this particular point is stored as nmax as being corresponding to the maximum area value amax ( in the step st67 ) and after the system flow has returned to the step st63 n is incremented by unity to repeat the update process of the maximum area value amax thereafter . in the step st64 , if nmax is equal to n , the derivation of the maximum area on the high cuff pressure side is complete , and the system flow returns to the main flow . upon entering the step st22 in the main flow , as shown in the flow chart of fig1 , the cuff pressure cm at the time point when the maximum value pmax of the pulse wave peak was obtained is substituted into press1 ( in the step st71 ). subsequently , the cuff pressure ci at the time point when the pulse wave peak pp ( namax ) maximizes the area is substituted into press2 ( in the step st72 ). and by carrying out the computation ( 2 ( press2 )+( press1 )/ 3 , the maximum blood pressure cs is determined ( in the step st73 ) before the system flow returns to the main flow . explanation of computation of the low cuff pressure side area ( in the step st23 ). upon entering the step st23 in the main flow , as shown in the flow chart of fig1 , first n is set to nmax - 2 ( in the step st81 ), and after adding unity to n ( in the step st82 ) it is determined whether or not n is equal to nend - 2 or not ( in the step st83 ). here , nend is the serial number of the pulse wave which was extracted last of all . as long as the determination result of the step st82 is no , throughout the step st84 to the step st86 , it is determined whether or not the same inequalities ( 1 ), ( 2 ), and ( 3 ) hold or not , in the same way as in the computation of the series of areas on the higher cuff pressure side described in connection with fig1 , and if either one of the inequalities holds a ( n ) is set to zero ( in the step st87 ), but on the other hand if none of the inequalities holds then the area a ( n ) is computed by equation ( 4 ) ( in the step st88 ) before the system flow returns to the step st82 . thereafter , n is incremented by one in the step st82 , and the computation for the areas is repeated until n becomes equal to nend . in the step st83 , if n equals nend - 2 , the computation of the areas a ( n ) on the lower cuff pressure side is completed , and the system flow returns to the main flow . explanation of computation of the maximum area on the lower cuff pressure side ( in the step st24 ). upon entering the step st24 in the main system flow , as shown in the flow chart of fig1 , first of all , the maximum value of the areas amax is set to zero ( in the step st91 ). and n is set to nmax - 2 ( in the step st92 ), and after n is further incremented by one ( in the step st93 ) it is determined whether or not n is equal to nend - 2 or not ( in the step st94 ). until this determination result becomes yes , the area values a ( n ) and the maximum value of the areas amax are compared and the maximum value of the areas amax is updated ( in the step st95 , and the step st96 ) on the one hand , and the n at which an updating took place is stored as namax ( in the step st97 ) before the system flow returns to the step st93 on the other hand . thereafter , the update process of the maximum area value amax is repeated . if n is equal to nend - 2 in the step st94 , the derivation of the maximum area on the lower cuff pressure side is completed , and the system flow returns to the main flow . upon entering the step st25 in the main flow , the cuff pressure cd at which the pulse wave peak pp ( namax ) which causes the minimum value of the areas is determined as the minimum blood pressure ( in the step st101 ). after this determination , this system flow returns to the main flow . thus , the various blood pressures can be measured from the cuff pressure and the pulse wave . it has been confirmed that the maximum , minimum , and the average blood pressures obtained according to the above described algorithm agree with the blood pressure measurements obtained by the use of korotkoff sound . although in the above described embodiment a band pass filter was used to extract the pulse wave , according to this invention it is possible to use a digital filter instead , and it is also possible to feed the cuff pressure signal containing a pulse wave signal into a cpu and to separate the cuff pressure signal and the pulse wave component by a software process which is different from a digital filter . further , although in the above described second preferred embodiment extraction of the pulse wave peak values was conducted by pulse wave division after deriving the differentiated values of the pulse wave , the extraction of the pulse wave peak values is not to be considered as limited thereby , according to this invention . thus , according to the electronic blood pressure measuring device of this second preferred embodiment of the present invention , as opposed to conventional electronic blood pressure measuring devices , since a blood pressure measurement is conducted by making use of information on cuff pressure and the amplitude of the pulse wave which is an oscillation within the cuff pressure , and the frequency range of this pulse wave is as low as from 1 hz to 10 hz , by providing a filter of such a band , almost all the external noises and oscillation noises can be eliminated , so that the amplitude information of the pulse wave can be used for processing by arithmetic means without involving any distortion , and accurate blood pressure measurement is possible even in the environment filled with noise . in particular , since the determination of the blood pressure is based upon the computation of the areas surrounded by the envelope line of the pulse wave amplitude which does not contain noise components , and the line connecting both ends of a predetermined number of data to use these partial areas as parameters , the differences in the areas become very conspicuous , and therefore accurate measurement of blood pressure becomes possible . although the present invention has been shown and described in terms of certain preferred embodiments thereof , and with reference to the appended drawings , it should not be considered as being particularly limited thereby . the details of any particular embodiment , or of the drawings , could be varied without , in many cases , departing from the ambit of the present invention . accordingly , the scope of the present invention is to be considered as being delimited , not by any particular perhaps entirely fortuitous details of the disclosed preferred embodiments , or of the drawings , but solely by the legitimate and properly interpreted scope of the accompanying claims , which follow .
an electronic blood pressure meter including a cuff , a pressure system for pressurizing and evacuating the cuff , a pressure sensor for detecting the pressure within the cuff , a pulse wave parameter extraction circuit and a blood pressure determining circuit . the pulse wave parameter extraction circuit extracts the maximum level difference in the pulse wave component of the cuff pressure over a certain time intervals and also provides pulse wave maximum and minimum values corresponding to the maximum and minimum values of the pulse wave components over each of the time intervals chosen . the electronic blood pressure meter may also include circuitry for finding maximum and minimum values on each of the higher and lower cuff pressure sides of the cuff and deriving blood pressure measuring readings therefrom .