JPS6272317A - Improved automated dilation period blood pressure monitor accompanying data reinforcement - Google Patents

Abstract

(57) [Summary] This bulletin contains application data before electronic filing, so abstract data is not recorded.

Description

[Detailed description of the invention]

TECHNICAL FIELD The present invention relates to automated blood pressure measurement devices, and more particularly to a self-contained program controlled monitor utilizing oscillometric sensing, characterized by data purification and enhanced systolic, diastolic and mean blood pressure measurements. Automated blood pressure monitoring is rapidly gaining acceptance and, in many cases, becoming an essential feature of human and veterinary procedures. This type of monitor is now
Emergency rooms, intensive and interdisciplinary care units, and
It has become a routine part of the patient environment in the surgical setting. The so-called oscillometric method of blood pressure measurement is one of the most popular methods in commercially available devices. This method is
It relies on measured changes in arterial counterpressure, such as those imposed by a re-inflatable cuff or cuff, which are relaxed or inflated in a controlled manner. In this case, the pressure change is continuous,
and in other cases it is incremental. In almost all cases,
A transducer monitors arterial backpressure amplitudes, and a processor converts selected parameters of these amplitudes into blood pressure data. Of particular importance to the principles of the present invention is U.S. Pat. No. 4, M. Ramsey, M.
360.029 and 4,394,034. The Ramsey patents derive from a common source, the former encompassing device claims;
On the other hand, the latter includes method claims, the division of which was made in response to a request for limitation during the procedure. However, both patents deal with the rejection of artifacts in oscillometer systems.
ion), said oscillometer system has been implemented in the commercially successful DINAMAP brand monitor, which is owned by the applicant. Critikon+ Inc., Tampa, Florida
, +) and is commercially available. According to the Ramsey patent, a re-inflatable cuff is appropriately placed on a patient's limb and pumped with air to a predetermined pressure. The sleeve pressure is then reduced to a predetermined fixed decrement and its pressure fluctuations at each level are monitored. These typically consist of a DC voltage with a small, superimposed fluctuating component (referred to herein as an "oscillatory complex") caused by arterial blood pressure oscillations. Therefore, properly filter to eliminate DC components,
and after providing amplification, the pulse peak amplitude below a given threshold level is measured and stored. As the attenuation continues, the peak amplitude is 41
It will increase to a relative maximum amount from U7 and then decrease. The lowest sleeve pressure at which the oscillations have the highest peak value represents the mean arterial pressure. Once the oscillatory complex pulse peak amplitudes are stored, the resulting sleeve pressures have a predetermined fractional relationship to the maximum stored peaks corresponding to the subject's systolic and diastolic blood pressures. The Ramsey patent strives to achieve significant results and disclosures against the rejection of artifactual data in order to obtain accurate blood pressure data. In fact, as shown in Figure 2 of the Ramsey patent,
The most substantial part of the measurement period (referred to as rT3J) is
It is devoted to the implementation of complex detection at various pressure levels, the measurement of signal peaks of genuine complexes, and the processing of those peaks according to an algorithm of artifact rejection. Nevertheless, if the occluded artery pressure decreases monotonically, this type of outcome, the signal peak data collected will sometimes result in data errors, i.e., do not match the above-mentioned typical physiological response pattern of the subject. Contains data patterns that do not. Further, in U.S. Patent Application No. 751,840 to M. Ramsay et al., entitled "Oscillometric Blood Pressure Monitor Utilizing Non-Uniform Pressure Attenuation Steps," which was filed on the same day as the present application, oscillometric blood pressure measurement is , by non-uniform sleeve pressure-dependent pressure decrement between successive oscillatory complex peak measurement intervals. The method of performing this type of oscillometric blood pressure measurement is facilitated by previously unutilized systolic, diastolic, and mean blood pressure measurement algorithms. It is an object of the present invention to provide an improved oscillometric blood pressure measurement device and method. More specifically, it is an object of the present invention to purify the oscillatory complex peak amplitude data population used for blood pressure measurements. Yet another object of the invention is an improved algorithm, method for measuring systolic, diastolic and mean arterial pressure;
and equipment. A blood pressure cuff is applied around the subject's artery and inflated above systolic levels so that the artery is sufficiently occluded for the maximum cardiac cycle. after that,
Decreasing the sleeve pressure causes incremental flow to gradually occlude the artery and measures of the successively encountered peak amplitudes are stored in a memory device. Also held are the sleeve pressures obtained for each memory complex peak. According to various features of the invention, the stored complex peak-display data set is corrected for anomalies and improved data processing is performed on the stored (and advantageously corrected) pulse peak data and The corresponding sleeve pressure information is acted upon to determine the subject's systolic, diastolic and mean arterial blood pressure. The above and other objects and features of the invention will be understood in the detailed discussion of specific, exemplary embodiments thereof presented below in conjunction with the accompanying drawings.
r, 7-) Uh. Like Ramse I II and other IMIs mentioned above,
U.S. Patent No. 4 by Meyto Latsey.
3f! 0.029'; and No. 4,349,034
and US Pat. No. 4,543,962 to Meinert U1, ZE et al.
0ll 0F AUTf)MATHI)BLOO
D PRESSUREnETFcTION)l , (
1985M', October 111) is 7°ζ for reference here.
Quote. These patents and patent applications provide a detailed description of the basic oscillometric blood pressure measurement that forms the background and starting point for this invention. just! Simply reexamining the arterial-occluding sleeve [] canopy should be placed on the subject, e.g.
- Placed over the pulmonary artery. At the beginning of the measurement cycle, the sleeve canopy should be inserted 7° through it at any point during the cardiac cycle to sufficiently occlude the brachial artery.
C expand to a pressure that inhibits blood flow. q The sleeve flap is then progressively retracted as in the damping knob. Pressure transducer, Acer inside the sleeve mouth cover 1! , and when Sowara starts issuing 4L L, (i.e.
When the left ventricle of the heart contracts, the cardiac pressure of ↓ momentarily exceeds the artery-occluded sleeve pressure), 1fl pressure oscillations occur! The peak of the signal (straight is bar 1.'I') neat or soft 1') is determined in the air. 1 All constant 14 is given by j-1, then The peak amplitude of the blood pressure complex generally becomes larger in the I11 tone, followed by the 1111 force in the contraction.
Kattei! If you continue, it will become significantly smaller. The peak amplitude of the oscillation complex and the corresponding occlusion-sleeve pressure value are maintained in the memory of the two pins. 1 - The Ramsey patent and patent application described above were used to process the recorded iQ blood 1 m 21 mp [nox peak value] and the test subject's ゛ V-equilibrium artery). ! This is an example of the incidental pressure value for obtaining -. These patents and Benefit 1 applications describe detailed methods for oscillatory knee pressure peak measurements, methods for testing for complex and rejected bad data related to measurement-disturbing artifacts (e.g. motion) during measurement cycles. etc. are also provided. Oscillometric blood pressure measurement, as featured by the Ramsey disclosure cited above, uses a read-only memory (1?OM or PROM) under stored program control as well as oscillometric pressure, oscillatory complex peak amplitude, and other measurements. This is done via a microprocessor operative in conjunction with a program that includes variable content random access memory ff (RAM) for storing processing operand variables. The microprocessor receives and receives gauze pressure readings produced by a pressure transducer, such as for processing by a peak detector, an amplifier, and an analog-to-digital converter, and generates the required total output l# control signal. for example, to open and close one or more sleeve vent valves q υ . Several variations of the oscillometric method, discussed in more detail in the Ramsey patent and patent publications cited above, may also be implemented. Thus, for example, a sleeve may be directly inflated by an air pump under microprocessor control and deflated in predetermined separate steps. Alternatively, the sleeve cap is primarily or exclusively inflated by the pressurized contents of the air reservoir, and/or deflation is via a selected one or more of the plurality of vent valves in a sleeve cap pressure-dependent step. It is also good to proceed variably. Are these latter alternatives of operation? (Achieves the desirable effect of compressing the time required for joint measurements.) Furthermore, at any predominant sleeve IF force,
Other methods exist for measuring oscillatory peak amplitude. According to the previously utilized embodiment, multiple (e.g. two) complex peaks are measured at each sleeve pressure step during sleeve contraction and their average was used as the peak value. Since the peaks should be approximately equal, any significant discrepancy (eg, >20%) will signal that an artifactual error has occurred and that the data will be rejected. In the fast (stat) mode, after a number interval has been detected to qualify a companion complex (nearly or equal peak value) and measurement confidence has developed:
Only one pulse is required during subsequent sleeve deflation intervals, thereby speeding up the combined measurement period. In this regard, reference is made to the aforementioned application, filed July 9, 1984. As mentioned above, when testing blood pressure complexes for peak amplitude at any occlusion pressure level, there can sometimes be the development of inappropriate data. There are sources of variation for this type of anomaly. Perhaps the most common is spurious movement by the subject, which generates inappropriate pressure impulses in the sleeve that can be sensed by the pressure cadence Q-ducer and then inaccurately reflected in the blood pressure measurement. be. Other causes include fluctuating power supplies with interfering electrical noise or internal cardiac or respiratory changes in the subject. When a false complex peak amplitude value occurs, it is discarded by the complex measurement device and the discard-signal value (e.g. +
1) is held in place in storage. A second type of spurious data exists when the pattern of stored pulse peak values deviates from a physiologically memorized sequence of values that increases toward a peak and then tapers off. Attention will now be directed to data processing under stored program control for cleaning the data collected by the blood pressure measuring device. A more specific, illustrative, and effective algorithm is the actual systolic
To measure diastolic, and mean arterial blood pressure! ji will be discussed. This type of data processing can be performed on any computing device, preferably a digital microprocessor, such as those commercially available from a number of vendors. The program instructions and sequences set forth below are for illustrative purposes only. Instructions of this type can be implemented in virtually any different programming language and sequence that will be readily apparent to those skilled in the art. In the signal processing described below, processing variables have the following meanings. CP (1) The cuff pressure obtained during the fifth deflation step, as measured by a transducer pneumatically coupled to the arterial occlusion cuff. CP(1) is an indexed array. That is, there are multiple values for CP(1) characterizing each ± contraction step. ΦA(1) i Peak amplitude of oscillometric vibration occurring at the first step (i.e., complex peak amplitude). If multiple complexes are measured during each prevailing contraction pressure, ΦA(1) is the average of two (or more) peak amplitudes during the i-th step. φA(1) is an indexed array. ΦA (MAX) Peak value MAX regarding the array of averaged amplitude blood pressure complex amplitudes Peak complex ΦA (MAX)
The time interval when the occurs. ■、Dual cup pressure measurement - ζ vs. 1 tatami 4 ribs - Natsume variance
Intermediate processing variable representing a predetermined fractional part of Lingu Function 1 LVL ΦA (MAX). sys Test subject's measured systolic pressure ■, Fox systolic pressure iJo variance'' Inuka Kujinto 1 11DLVL and LDLVL Intermediate processing variables each representing a different fractional part of ΦA (WAX). Old All, old A1. The diastolic pressure 41'I variables interpolated in the first and third parts are shown in Table 4: Intermediate processing variables. 1) IIi, Zhang! ! 1
1 pressure. ] V, 'l' IJ] Processing variable of pulse pressure Variable Expressed function quantity IMll The pulse pressure pulse for the contraction interval following the interval where the pressure oscillation amplitude was maximum
peak. 1 tithe 1. Referring to the final equation (intermediate processing variables used. MAll subject's arterial blood pressure. A waveform diagram is shown with associated data for overcoming bad data components. According to the discussion in 1999, the sleeve flap artery occlusion pressure over the measurement period, as measured by the sleeve flap associated transducer, is characterized by waveform 10. Sleeve] 1 cover 11- force is less than the subject's systolic pressure l-
Easily increases up to the maximum value of L7 and then expands in the order of steps! It is contracted to a point of less than 1JIl+force. The order of the sleeve closure shrinkage is reduced by 41 to the time interval (B digit 1.2... (the highest toe column + 8 in the data table section of FIG. 1). At each step i, the internal pressure is represented by the data array CI'(1), CP(2), , , , , .
0゛'-data table 1 two columns + 2), the L IJ is found. Each step (time interval) includes 1 ζ combs per minute, at least 2 heart beats. 1 sea urchin - 4 ru. Therefore, after the start of this type of pulse, at least two So-rI + Over Ll Caninzolenox pulses 21i and L-22i are measured during each interval. A legend is applied to the four pulses during vl, transformation steps [; and 9] to avoid the /fj disturbance and loss of clarity in FIG. No pulses are measured during the first and second pressure steps (time intervals), since the sleeve cover pressures [F': 11(]) = 201 Torr and C1'(2) - 194 Torr] are During this period, it is determined that during the entire heart phase 11-1, the blood flow flowing through the subject's arteries is not required. Subsequent intervals 3.4. , , two oscillometric complex pulses 21i and 22i are generated and measured, with an average peak amplitude of 231 (the processor variable array values are initially Φ
A(1) is stored in °C. Shoulder fig-
The vibration amplitude array (ΦA(1)) is shown in the second column 14 of the data table of FIG. 1 for each time interval. The data sequence of the pressure amplitude ΦA(1) does not contain any +1 value signifying a disturbing measurement. Furthermore, the data pattern in the second column of the data table regarding the vibration amplitude shows a continuously increasing number of values towards the peak value. It shows a pattern, followed by decreasing values, but none of these values are accompanied by adjacent equal ΦA(1) values.To the extent that any ΦA(1)-1 value is stored,
Alternatively, to the extent that a gradual increase/decrease pattern is not obtained, the data processing according to the present invention applies appropriate modified ΦA(1) values (third data table column 15 in FIG. 1) for vibration amplitude entries that require modification. Calculate. To put it in perspective, if any φA(1)=1 values exist, they are replaced by the average value of the vibration amplitude during two adjacent memory elements. Zunawara, φA(1)-(ΦA(
1-1) ((ToA(shi1))/2...Bu10 Correspondingly, if two adjacent vibration amplitudes have two equal hani whose vibration amplitudes are prohibited +l-, then consecutive equal pairs The first one is replaced by the average value of the amplitudes of the twenty-one psix peaks measured at the next lower and the next higher occlusion sleeve pressure.For example, Equation 1, and more specifically, See Comparable Correlation in Function Block 30 of FIG. the average vibration amplitude (second data table column 14 in FIG. 1), and the modification φ shown in data table column 15 of No.
A(1)(!) is emitted 4F. For this purpose, start block 10 (Fig. 2)
Step 15 reads the next value ΦA(1) (proceeding to the right along data table column 14 in FIG. 1), and test 18 determines whether the value stored in ΦA(1) is the error signal value. Determine whether it is equal to 1+1. If this is the case, it does not control the progression to the equality test 27 (indicating that the measured value was inferentially unrelated to artifacts, etc.). However, the content of ΦA(T) is +
1 ("yes" branch of test 18), the function block 23 executes 21, i.e. the memory cell ΦA corresponding to the sleeve pressure CP(1)
The content mentioned above of +1 in (1) is changed to the next lower (ΦA
(1-1) and the next higher non-plus one (ΦA(1
+1)) Replaced by the average value of the vibration amplitude measured at the contraction step and step. Continue steps 18 and 23
thus removes the measured pressure peak amplitude memory contents (column 2 of the data table in Figure 1) which are all +1 values,
These are replaced by the average values of the measurements made during the immediately next contraction step (the content of the modification ΦA(1) is shown in column 15). Test 27 then tests the current operand φA(1) for equality prohibited with the previous value φA(I-1). If ΦA(1) and ΦA(1-
If the contents of 1) are different (from test 27 to the 1-no-1 branch), the process flows to test 32 and each N of ΦA(1)
Determine whether the element has been processed. If they are not, control returns to block 15 to read and process the next ΦA(1) element of the array in the third column 15 of the data table of FIG. Once all elements have been processed, control exits the data cleansing routine of FIG. 2 to data processing point 33 for the microprocessor to continue with the next (unrelated) task. If a data error occurs (the "yes" output of test 27 signals that the data value ΦA(1) has been made equal to the previous bond), control passes to step 30, which is the estimated arl reelement ΦA(II) = (a value that should be different from ΦA(1) but was not), ΦA(T-1) = (ΦA(1) + ΦA(T-2))/2
...Replace with the average value of two immediately adjacent elements 乎ζ 9 as per 2. Therefore, the data cleaning routine shown in FIG. 2 and described above replaces all erroneous readings indicating φA(I)-1 values with interpolated estimates and
ΦA(1) Remove all adjacent equal values of the array data. The modified set of ΦA(1) is shown in the third column 15 of the FIG. 1 data table. Thus, for example, during the sleeve flap pressure step (time interval) "4" the vibration amplitude value is modified from the error-signal +1 value to a peak amplitude of 14, and the sleeve flap pressure 187 during the immediately adjacent time intervals 3 and 5. Represents the average value of measurements 4 and 25 at Tor and 153 Tor. Similarly, the first of two equal measured vibration amplitude pulses (pressure step 6) of value 63 during periods 6 and 7, corresponding to occlusion sleeve pressures of 140 Torr and 126 Torr, has an adjacent measured amplitude The value 44 represents the average value of 63 and 25 units.
will be corrected. Accordingly, the modified array ΦA(]) as indicated by the third column 15 of FIG. It consists of values that can be utilized to measure each of the systolic, diastolic, and mean arterial blood pressures. The data purification described above provides more accurate measurements than in the traditional case,
It also allows blood pressure to be measured more quickly, eliminating the need for repeated dilation steps when unacceptable artifacts or noise-contaminated data are detected. Attention is now drawn to a unique method, according to which the first
The stored sleeve cover pressure CP(1) and corrected blood pressure peak value ΦA(T
) The information is utilized in accordance with other features of the invention to measure the subject's systolic, diastolic, and mean arterial blood pressure. The pulse complex waveform processing that characterizes systolic blood pressure measurement is illustrated in FIG. 3, and a flowchart related to the underlying data processing is shown in a small size in FIG. Overview ``4'', systolic force is 31,
will be determined. (・I) Maximum plane II vibration - amplitude of lamplenox (ΦA
(MAX)) (Kosai 1 is the time interval MAX.
Find fbl peak (amplitude equal to a given fractional part of ΦA (MAX) to 1

[・Find Hell (LVL). we,
For high-speed (rapid expansion, L/or 1-pulse) operation the name is (e.g. 0.45) and for normal processing it is 0.
．． A value of 5 was obtained; ((:) starting at the MAX interval and higher sleeves) - 1 towards the left of Figures 1 and 3). adjacent vibration amplitudes, (A(L) < 4)A(MAX)
”0.5<Φ(L −+ 1) ) ・・
・Corrected vibration amplitude (into (1
) test for the tail (column 3, 15 in the data table of Figure 1);
(d) Interval 1. Calculate the interpolated sleeve cover pressure (between CP(L) and C11(l)l) to estimate the amount of linear variance in the vibration amplitude and sleeve cover pressure between and L-+1. This itself, which is a trapezoidal interpolation of +61 knowledge, is shown graphically in FIG.
SYS). h of systolic pressure measurement marked
' ? To explain the theory in detail, if the maximum vibration amplitude peak occurs 4 = the sleeve cover ji quantity force interval 1 =
, , MAX is essentially any well-known horn method (in Figure 4 corresponding to the spacing MAX in Figure 3) 11-1,000 yards-1.
Measured with Sugenop 4(1). Thus, for example, one sock sequence to the summary of -F is, by way of example, to find the interval) IAX: MAX==φA(1) to Φ.
・・・・・・・・・・・・・・・・・・Formula 4% formula% IFΦA(K)<φA? IAX GOTO70...
・・・・・・・・・Formula 7ΦA gate ＾X-ΦA(K) ・・・
・・・・・・・・・・・・・・・・・・・・・・・・ Take 8
Gate AX-K・・・・・・・・・・・・・・・・・・
・・・・・・・・・・・・・・・8970 NEXT
K・・・・・・・・・・・・・・・・・・・・・
・・・・・・・・・・・・ Bu H1 section simply stated, generation 4
and 5 L, l peaks (direct is tF in the first interval,
Then, along with (11'+(11A(1)), the variable ΦAMAX
Record 1! The first assumption is made that the beat value of the 4-beam rotation is rotatable. Regarding the assumed N time interval measurements, ゛C
The loop between 386 and 10 is ΦA(1) from 2 to N
All elements of the array are tested successively and the value ΦA(K
)−(K is the loop index) is the previously assumed ΦAMAX(i
Update ΦAMAX only when it exceeds fi. When processing exits the loop following instruction 70 of Equation 10, variable MAX contains the value I such that ΦA (MAX) is the largest value in the array. The next successive step 42 is LVL = ΦA (gate AX)" 0.5...
. . . As shown in Equation 11, a variable LVI is set equal to a predetermined fractional part of the peak amplitude ΦA (MAX). The subsequent operation 45 obtains a first time interval (L) prior MAX, for which the ζ vibration amplitude peak is less than LVL and is always less than 1/2 of the peak value ΦA (MAX);
Thereby we obtain two consecutive values (L, L+1) with peak amplitudes that couple the values to LVL. Algorithms for performing this type of search are well known to those skilled in the art, for example FORJ-I TO AX...
・・・・・・・・・・・・・・・a12IP(ΦA(hA
x-J)〈0GOT0140...Formula 13
% formula % 140 L -MAX l・・・・・・・・・・・・
・・・・・・・・・・・・Formula 15 Formula 1215 is MA
Do or FOR-NE progressing from X-1 to l-1
It consists of 111 net XT loops, and the first sub-LV
1. Exists when a value is obtained. Appropriate interval identification (MA
X −, 1) is stored in the device I. Finally, the systolic pressure is determined by the linear variation in the cuff pressure between (,?1C11(1,) and CP(L+1)) and The corresponding vibration amplitudes 4]A(L) and (ll
1' is evaluated to estimate the linear variation between (L+1) and (L+1). In this way, according to trapezoidal interpolation, which is known per se, the systolic pressure sys can be determined by (step 47 in FIG. 4). To illustrate the data usage in Figure 1, the peak amplitude (70)
50% of is 35, so pulses in time intervals 5 and 6
Complex measurements are selected for calculation of systolic pressure. The software interpolation implementation of Equation 16 assumes 3 significant figures: SYS = 153+ ((140-153)
35-25) / (44-25) )...Formula 17-
146)-ru ・・・・・・・・・・・・・・・
.........Equation 1B. The pulse complex waveform processing that characterizes diastolic blood pressure measurements is shown in FIG. 6, and the flowchart underlying the diastolic data processing algorithm is shown in FIG. To put it in perspective, diastolic pressure is measured by: +8) Complex amplitude (ΦA (MAX))
(This occurs in the time interval MAX); tb+ Find the amplitude level (L[ILVL) equal to the first predetermined fractional part of the peak value ΦA (MAX). We are satisfied with 0.69 for normal processing and rapid (
A value of 0,75 was obtained for the "fast") process; (C) starting at the MAX interval and moving towards lower sleeve flap pressure (i.e. to the right in Figures 1 and 6); and two adjacent vibration amplitudes, φA(UD
) <φA(MAX)” 0.6LEΦA (Ull
-1) Test the modified IF vibration amplitude (ΦA(+)) buffer 15 (Fig. 1) to obtain that represented by 19; (dl vibration amplitude between intervals UD-1 and 1II1 and sleeve opening Cover pressure (processing variable 1 in Figure 7) IAl
Estimate the amount of linear dispersion in l) (cp(on-1)
Calculate the interpolated sleeve pressure between and CP (UD): f8+ the second factor lower than the first factor (e.g. 0.55), i.e. if ΦA(L0) < ΦA(MAX)” 0.55 <ΦA
(tri −1) ... the stored ΦA(I) oscillation amplitude at the pressure starting at the lowest CP measured for the adjacent pair combining the peak amplitude ΦA(MAX) multiplied by Equation 20 test; CP(L) corresponding to ffl MAX times, 0.55 factor;
0) and CP (LD-1). This lower interpolated sleeve pressure is related to the variable symbol DIAL; and +g+ subjects diastolic pressure (DIA) to the mean value of -F and lower interpolated values DIAU and old AL, i.e. old^=(DIAII +( DIAL)/2...
・l1...Old...Measure as Equation 21. The above procedure is illustrated in the blood pressure complex display flowcharts of FIGS. 6 and 7. The peak φ^(MAX) is first determined by processing Equation 4-10. Upper and lower peak amplitude fractional part 1) I
AII and 1) IAL are then determined (steps 64 and 65 in FIG. 7 correspond to the labeled horizontal dash lines in FIG. 6). Step 69 then determines the first time interval (CD) following MAX at the point where the peak amplitude ΦA (UD) is lower than the value stored in DTAU (Equation 12 substituting IEAX-J for rMAX+J through processing similar to 15), then,
Step 72 performs a trapezoidal interpolation similar to FIG. 5 to determine the sleeve flap pressure ([1IAll) corresponding to the tlDLVL complex amplitude value. When a peak complex value occurs, time interval 11 is the interval MAX.
It is observed that it is consistent with . For the illustrated data, it is less than 0.69XΦA (MAX) (7) MAX
Two consecutive (first pulse complex continues for the next time period 1)
This is because it occurred during 1MMAX+1. Functional steps 73 and 74 of FIG. 7 are performed in a manner directly analogous to operations 69 and 72, i.e., the peak complex amplitude is
When Llll and νL, which are equal to 0.55 times, are combined, the sleeve cover pressure DIAL can be calculated by interpolating the interval.
decide. This latter search performs ΦA(
+) and then towards higher CPs. Ultimately, the subject's diastolic pressure (DIA) is DT
is calculated as the average value of the contents stored in AU and [)IAI (step 82). To illustrate by way of a numerical example, we will again make use of the data section of FIG. DIAU=83+((93-83) X(4B-4
0))/(40-53)=77・・・・・・・・・・・・
・・・・・・Formula 22%Formula%) ・・・・・・・・・・・・・・・Formula 23DIA
=(71+67)/2 =69 ・・・・・・・・・
・・・・・・・・・Equation 24゜1 [4 shallow (This is the sidecar shift waveform processing for Equation 24゜1 [4 shallow (this).
4) 11-Chart・
It is shown in So A-1. First of all, without further summary, the arterial pressure is determined by the following equation:
Find (bj into (MAX river), i.e. 6 hours M
The complex peak amplitude that occurs in the first interval following AX (the first sleeve to the left of the interval MAX that was lower than (MAX + 1)) is lower than 1 cover pressure (obtains the first vibration amplitude of ◇) Test the sleeve Il cover pressure value in the correction register 15 (Fig. 1) with respect to the interval MNI.Keep the above relation, ΦA group Nl) ≦Φ(gate AX+1) ≤Φ8(gate NI+1
)......is the one that satisfies the generation 25: icl Next, the vibration amplitude (-ΦA (MAX-+-1
)] 1 over l-+force MAP and interpolate between the intervals MN+ and MNI+1; )+(2”MAP
l,))/2.9...+(as expressed by 26, ・1'equal artery ll mass) is the sleeve cover pressure C
P(MAX river) and 1 yen, 0) weighted to 11, is measured. The denominator (2.9 in 26 is [high speed; Mo 1, for example, regarding the motion 1 at 2.85) (is young 1' (+(may be. Step 1:
Rhythm 1 is not illustrated in FIGS. 8 and 9. The subroutine 101 (Figure 9) is (for example, equation 410
Compare I) with the peak interval MAX by executing G). Processing variable A? IP is interval MAX (step 105)
The peak of the complex following t (set equal to t,
And the interval MNI is the time MAX in Fig. 8), and the force may be directly applied to the force.
(MAX +-])) (h 1st occurrence: 1 sample (for example, λ, compared to Equation 12-15, j: I processing, L), then measured (step 106)
. Then interpolation is done and points? I^ yen, (8th
FIG. Determine the mean arterial pressure of the subject beforehand. Again, a numerical example is shown from the data in Figure 1: PL- to the gate.
140÷((128-140)X(62-44))/(
63-44) -129・・・・・・・・・・・・
...Formula 27 MAt' - (104+2°+29
) /2.9 = 124 ・・・・・・・・・・・・
Equation 28 Therefore, the above discussion shows that measured data can be enhanced by replacing data lost due to measurement artifacts or deviations from the proper data pattern with approximate values. Specific data processing algorithms were presented and discussed for the calculation of a subject's measured systolic, diastolic, and mean arterial blood pressure. Arrangements 1-1 are merely illustrative of the principles of the invention. Numerous variations and adaptations thereof will be readily apparent to those skilled in the art without departing from the spirit and scope of the invention. For example, the pressure measurement mode is described above as a gradual deflation from an initial inflation above the subject's systolic pressure. Measurements of the present invention can be performed on stepwise inflation from an initial sub-diastolic orifice pressure, or on successive face-to-face individual flap inflations or deflations.

[Brief explanation of drawings]

FIG. 1 is a timing diagram illustrating data generation and modification in an exemplary measurement jll for LASIL meter pressure measurement in accordance with the principles of the present invention; FIG. A flowchart showing data purification related to measurement, FIG. 3 is a small graph diagram showing vibration amplitude processing related to systolic blood pressure measurement according to the present invention, and FIG. 4 is a flowchart showing the systolic pressure surface 1! A program flowchart related to measurement, FIG. 5 shows the processing mode 1 of FIGS.
and ffl lft (also in Figures 6-9)
FIG. 6 is a graph showing blood pressure interpolation according to the present invention.
+ constant waveform diagram, Figure 7 is a program flowchart 1 for reducing diastolic blood pressure measurement not featured in Figure 6, and Figure 8 is a program flowchart 1 for reducing diastolic blood pressure measurement according to the present invention. Twenty-one pres. 1λ1, 9th peak amplitude processing
The figure is a program flowchart for measuring mean arterial pressure as featured in FIG.

Claims (1)

Claims: (1) an inflatable sleeve flap, means for inflating and deflating the sleeve flap, and pressure transducer means coupled to the sleeve flap for detecting the pressure available at the sleeve flap; means responsive to the pressure detected by the transducer means for generating a signal representing a blood pressure pulse sensed by the sleeve flap and the transducer means coupled thereto; and a sleeve flap detected at different sleeve flap pressures. A complex peak storage means for storing a value characterizing the sleeve pressure vibration peak amplitude of the sleeve pressure pulse, and a sleeve cover for storing the sleeve pressure vibration obtained when the sleeve pressure vibration signal rises. a combination of pressure storage means and data purification means for correcting data uncertainties in response to values characterizing the sleeve flap pressure complex peak amplitude stored in said complex peak storage means; A digital processor-controlled automated blood pressure measuring device operative in conjunction with a stored program comprising: (2) a preselected character is stored in said complex peak storage means for detecting an unsuccessful sleeve pressure oscillation peak measurement, and further said data correction means is responsive to the detection of said preselected character. and means for examining the stored contents of the complex peak storage means and replacing the preselected character with one of a plurality of stored sleeve-mouth pressure complex peak values, At least one of the plurality of stored sleeve flap pressure complex peak values is obtained at a higher pressure than the sleeve flap pressure associated with the preselected character, and at least one other is obtained at a pressure higher than the sleeve flap pressure associated with the preselected character. , obtained at a lower pressure than the sleeve flap pressure associated with the preselected character. (3) The examination and replacement means includes means for replacing the preselected character with an average value of a plurality of sleeve flap pressure complex peak values stored in the complex peak storage means, and at least one of the complex peak values associated with said preselected character was obtained at a pressure higher than the sleeve flap pressure associated with said preselected character; 3. The device of claim 2, wherein the device is obtained at a pressure lower than the sleeve pressure associated with the character. (4) means for said data purification means to search said sleeve cover pressure complex storage means for each occurrence of two equal peak amplitude values rising with successive sleeve cover contraction pressures, and in response to said search means; and means for replacing said two stored equal values with divisors of two other values stored in said complex peak storage means. equipment. (5) The data purification means searches the sleeve flap pressure complex peak storage means for each occurrence of two equal peak amplitude values that rise with successive sleeve flap contraction pressures, and searches the sleeve flap pressure complex peak storage means to obtain two stored equal values. 2. Apparatus according to claim 1, further comprising means for replacing the complex peak amplitude with the average value of the stored complex peak amplitudes of the earlier and later values of the next measurement. (6) an inflatable sleeve cover, means for inflating and deflating said sleeve cover, pressure transducer means coupled to said sleeve cover for detecting the pressure available in said sleeve cover; means responsive to pressure detected by said transducer means for generating a signal representative of blood pressure pulses sensed by said transducer means coupled to said transducer means; and peak amplitudes of said sleeve flap pressure pulses detected at different sleeve flap pressures. complex peak storage means for storing values characterizing the
comprising a sleeve cover pressure storage means for storing the sleeve cover pressure obtained when the sleeve cover pressure pulse peak signal rises, and a systolic pressure determining means,
means for said systolic pressure determining means to locate a maximum complex peak amplitude stored in said complex peak storage means; and means for generating a threshold level of a predetermined fraction of said maximum peak amplitude value; In response to the threshold level determined by the calculation means, a plurality of sleeve flaps generated at a pressure higher than the sleeve flap pressure obtained when the maximum pulse peak signal rose is determined from the sleeve flap pressure storage means. A digital processor-controlled automated blood pressure measuring device operative in conjunction with a stored program, having means for selecting a pressure peak pulse amplitude and means for determining a systolic pressure from the selected plurality of signals. . (7) A patent in which the systolic pressure determination means further comprises interpolation means for determining a systolic pressure from the plurality of selected signals and the corresponding sleeve cover pressure stored in the sleeve cover pressure storage means. An apparatus according to claim 6. (8) The apparatus according to claim 7, wherein said interpolation means further comprises means for calculating an intermediate pressure among a plurality of pressure values retrieved from said sleeve cover pressure storage means. (9) an inflatable sleeve cover, means for inflating and deflating said sleeve cover, pressure transducer means coupled to said sleeve cover for detecting the pressure available in said sleeve cover; means responsive to pressure detected by said transducer means for generating a signal representative of blood pressure pulses sensed by said transducer means coupled to said transducer means; and peak amplitudes of said sleeve flap pressure pulses detected at different sleeve flap pressures. complex peak storage means for storing values characterizing the
comprising a sleeve cover pressure storage means for storing the sleeve cover pressure obtained when the sleeve cover pressure pulse peak signal rises, and a systolic pressure determining means,
said systolic pressure determining means includes means for locating a maximum sleeve flap pressure pulse complex peak amplitude stored in said sleeve flap pressure complex peak storage means and a threshold for a predetermined fraction of said maximum peak amplitude value; means for generating a level and said complex peak storage means, one of which is greater than said predetermined peak component;
means for locating two items, one of which is smaller than this peak component, and the two located sleeve flap pressure pulse peak amplitude values stored in the complex peak storage means and the sleeve flap. and means for determining systolic pressure by interpolating between corresponding sleeve pressures stored in pressure storage means. (10) an inflatable sleeve cover, means for inflating and deflating said sleeve cover, pressure transducer means coupled to said sleeve cover for detecting the pressure available in said sleeve cover; means responsive to pressure detected by said transducer means for generating a signal representative of blood pressure pulses sensed by said transducer means coupled to said transducer means; and peak amplitudes of said sleeve flap pressure pulses detected at different sleeve flap pressures. a complex peak storage means for storing a value characterizing the sleeve cover pressure; a sleeve cover pressure memory means for storing a sleeve cover pressure obtained when the sleeve cover pressure pulse peak signal rises; and a sleeve cover pressure memory means for storing a value characterizing the sleeve cover pressure pulse peak signal. data purification means for correcting data uncertainties and systolic pressure determination means responsive to a value characterizing a sleeve flap pressure complex peak amplitude stored in the storage means; The maximum sleeve cover pressure complex peak storage means stores the maximum sleeve cover pressure complex peak storage unit.
means for locating a peak amplitude; and means for generating a threshold level of a predetermined fraction of said maximum peak amplitude value; and in response to said threshold level determined by said calculating means, from said sleeve flap pressure storage means. , means for selecting a plurality of sleeve flap pressure peak pulse amplitudes generated at a pressure higher than the sleeve flap pressure obtained when the maximum pulse peak signal rises, and calculating systolic pressure from the plurality of selected signals. A digital processor-controlled automated blood pressure measuring device operative in conjunction with a stored program, comprising: means for determining. (11) a preselected character is stored in said complex peak storage means for detecting a measurement of an unsuccessful sleeve pressure oscillation peak, and further said data correction means is responsive to the detection of said preselected character. and examines the memory contents of the complex peak storage means, and stores the preselected character in a plurality of stored complex peaks.
means for substituting one of the peak values, wherein at least one of the plurality of stored sleeve flap pressure complex peak values is a pressure higher than the sleeve flap pressure associated with the preselected character. and at least one other
11. The apparatus of claim 10, wherein the device is obtained at a lower pressure than the sleeve pressure associated with the preselected character. (12) means for the data purification means to search the sleeve cover pressure complex storage means for each occurrence of two equal peak amplitude values rising with successive sleeve cover contraction pressures, and in response to the search means; means for replacing one of said two stored equal values with a divisor of two other values stored in said complex peak storage means. The device according to item 10. (13) means for the data purification means to search the sleeve cover pressure complex storage means for each occurrence of two equal peak amplitude values rising with successive sleeve cover contraction pressures, and in response to the search means; means for replacing one of said two stored equal values with the arithmetic mean of two other values stored in said complex peak storage means. 1
The device described in item 0. (14) a pressurized sleeve canopy and a means for reducing the sleeve flap pressure to a predetermined sleeve pressure decrement level to predominately and temporally vary the peak of the arterial pressure oscillation complex and its envelope; a) detecting an oscillatory complex at each of said decrement levels; b) determining the amplitude ΦA(MAX) of the largest of said peaks; c) determining the amplitude ΦA(MAX) of the largest of said peaks; producing an amplitude reference LVL that is a predetermined component; fixing the decrement levels L and L+1; e) producing a systolic pressure as the sleeve flap pressure interpolated between said pressure levels L and L+1, ΦA(L);
estimating a predetermined function divisor for the amplitude between and ΦA(L+1). (16) an inflatable sleeve cover, means for inflating and deflating said sleeve cover, pressure transducer means coupled to said sleeve cover for detecting the pressure available in said sleeve cover; means for generating a signal representative of the blood pressure sensed by the sleeve sheath and the transducer means coupled thereto in response to the pressure applied thereto; and the peak amplitude of the sleeve flap pressure pulses detected at different sleeve flap pressures. complex peak memory means for storing a value to be applied to the sleeve cover, sleeve cover pressure memory means for storing the sleeve cover pressure obtained when the sleeve cover pressure pulse peak signal rises, and mean arterial pressure determining means. and the mean arterial pressure determining means includes means for locating a maximum sleeve pressure complex peak amplitude stored in the complex peak storage means; means for locating a subsequent peak value stored in said complex peak storage means; calculation means for calculating two different levels, each being a different component of said subsequent peak value; a plurality of peak pulse amplitudes generated at a sleeve flap pressure higher than that obtained when said maximum complex peak signal was raised from said complex peak storage means in response to a value determined by said calculation means; and means for determining mean arterial pressure from the plurality of selected signals, wherein the sleeve cover pressure stored in the sleeve cover pressure storage means corresponds to the selected pulse signal, and A digital processor controlled automated blood pressure measurement device operating in conjunction with a stored program, wherein the sleeve flap pressure recorded in the sleeve flap pressure storage means corresponds to the subsequent complex peak signal. (17) The apparatus according to claim 16, wherein said determining means comprises interpolation means. (18) The determining means determines the sleeve cover pressure stored in the sleeve cover pressure storage means associated with the subsequent complex peak signal and the sleeve cover pressure memory associated with the plurality of selected complex peak values. 17. The apparatus of claim 16, further comprising means for calculating a weighted average with a divisor of the sleeve flap pressures stored in the means. (19) an inflatable sleeve cover, means for inflating and deflating said sleeve cover, pressure transducer means coupled to said sleeve cover for detecting the pressure available in said sleeve cover; means for generating a signal representative of the blood pressure sensed by the sleeve sheath and the transducer means coupled thereto in response to the pressure applied thereto; and the peak amplitude of the sleeve flap pressure pulses detected at different sleeve flap pressures. a complex peak storage means for storing a value to be applied to the sleeve cover, a sleeve cover pressure memory means for storing a sleeve cover pressure obtained when the sleeve cover pressure pulse peak signal rises, and the complex peak memory means. data purification means for correcting uncertainties in the data and operating with respect to complex peak amplitudes characterizing the values stored in the data; and means for determining mean arterial pressure; - means for locating a maximum sleeve pressure complex peak amplitude stored in a peak storage means, and a means for locating a maximum sleeve pressure complex peak amplitude stored in the complex peak storage means following the rise of said maximum complex peak amplitude; means for locating a subsequent peak value; calculation means for calculating two different levels, each being a different component of said subsequent peak value; and in response to the value determined by said calculation means, said means for selecting from a complex peak storage means a plurality of peak pulse amplitudes generated at a higher sleeve pressure than that obtained when said maximum complex peak signal rises; and said plurality of selected signals; means for determining a mean arterial pressure from said sleeve cover pressure storage means, wherein said sleeve cover pressure stored in said sleeve cover pressure storage means corresponds to said selected pulse signal;
and wherein the sleeve flap pressure recorded in the sleeve flap pressure storage means corresponds to the subsequent complex peak signal. (20) A preselected character is stored in said complex peak storage means for detecting an unsuccessful pulse flow peak measurement, and said data correction means, in response to detection of said preselected character, Examining the memory contents of the complex peak storage means, the preselected character is selected from a plurality of stored complexes, at least one of which was obtained at a sleeve flap pressure higher than the sleeve flap pressure associated with this character. - The device according to claim 19, comprising means for substituting a divisor of the peak value. (21) a preselected character is stored in said complex peak storage means for detecting an unsuccessful pulse flow peak measurement, and said data correction means, in response to the detection of said preselected character, Examining the memory contents of the complex peak storage means, the preselected character is obtained by averaging the next highest sleeve flap pressure and the next lowest sleeve flap pressure, at least one of which is associated with this character. 20. The apparatus of claim 19, further comprising means for substituting a submultiple of the stored complex peak values. (22) means for the data purification means to search the sleeve cover pressure complex storage means for each occurrence of two equal peak amplitude values rising with successive sleeve cover contraction pressures, and in response to the search means; means for replacing one of said two stored equal values with a divisor of two other values stored in said complex peak storage means. The device according to item 19. (23) means for the data purification means to search the sleeve cover pressure complex storage means for each occurrence of two equal peak amplitude values rising with successive sleeve cover contraction pressures, and in response to the search means; means for replacing one of said two stored equal values with a divisor of the next highest value or next lowest value stored in said complex peak storage means. Apparatus according to claim 19. (24) a pressurized sleeve canopy and a means for reducing the sleeve flap pressure to a predetermined sleeve pressure decrement level to reduce arterial pressure to a predominant and temporal peak of the oscillatory complex and its envelope; a) detecting an amplitude complex at each of said decrement levels; b) determining the amplitude ΦA(MAX) of the largest of said peaks and associated c) recording the stored prevailing sleeve pressure decrement levels; d) identifying and retaining each of the sleeve flap pressure decrement levels having a peak amplitude equal to or less than the level obtained by the identification step; e) interpolating the peak amplitude associated with the interpolated peak amplitude as a predetermined weighted average of the sleeve flap pressure corresponding to the interpolated peak amplitude and the recorded and maintained sleeve flap pressure decrement level; A method comprising: generating arterial pressure. (25) a) an inflatable sleeve flap; b) means for inflating and deflating the sleeve flap; and c) pressure transducer means coupled to the sleeve flap for detecting the pressure available in the sleeve flap. and d) means responsive to the pressure detected by the transducer for generating a signal representative of the blood pressure complex sensed by the transducer and the transducer coupled thereto; and e) at different vent pressures. f) sleeve cover pressure storage means for storing a value characterizing the peak amplitude of said signal representing a complex of said signals; f) sleeve cover pressure memory means for storing a sleeve cover pressure; and g) said peak amplitude signal is generated. h) diastolic pressure measuring means; and h) diastolic pressure measuring means.
) means for locating the maximum peak pulse amplitude recorded in the sleeve cover pressure amplitude complex peak storage means; (iii) from a plurality of peak amplitudes of said complex peak storage means generated at a lower sleeve flap pressure than that obtained when said maximum peak amplitude occurred; (iv) means responsive to a value measured by said calculation means for selecting; and (iv) said sleeve port corresponding to a diastolic pressure from said selected plurality of peak amplitudes and said selected plurality of signals. measuring means for measuring the sleeve cover pressure stored in the sleeve cover pressure storage means; the plurality of signal selection means select the four pulse peak signals stored in the sleeve cover pressure storage means; means for selecting, two of said four values being greater than the two levels measured by said calculating means, while the other two of said four values are being determined by said calculating means; A digital program operating in conjunction with a stored program consisting of less than two selected levels.
Processor controlled automated blood pressure measurement device. (26) The measuring means measures the four complexes.
means for measuring peak amplitude and diastolic pressure stored in said sleeve flap pressure storage means and operating for four sleeve flap pressures corresponding to said four stored complex peak values; 26. The apparatus of claim 25. (27) a) an inflatable sleeve cover; b) means for inflating and deflating said sleeve cover; and c) pressure transducer means coupled to said sleeve cover for detecting the pressure available in said sleeve cover. and d) means responsive to the pressure signaled by the transducer for generating a signal representative of the blood pressure complex sensed by the sleeve flap and the transducer coupled thereto; and e) at different sleeve flap pressures. f) complex peak storage means for storing a value characterizing the peak amplitude of said signal representative of the complex of said signal; and f) a sleeve cover pressure memory for storing a sleeve cover pressure obtained when said pulse peak signal occurs. g) diastolic pressure measuring means, said diastolic pressure measuring means (i) for locating the maximum peak amplitude stored in said sleeve cap pressure complex peak storage means; (ii) calculating means for calculating two different levels, each of which is a different fraction of said maximum peak amplitude value; (iii) in said complex peak storage means;
means for arranging two pairs of entries, each pair having one entry larger and one smaller than that corresponding to one of said two fractional values of said maximum peak amplitude; (iv) interpolation means operative with respect to said arranged peak pairs and corresponding sleeve flap pressures stored in said sleeve flap pressure storage means for measuring upper and lower endo-peak pressures; and (v) measuring diastolic pressures. and means responsive to said intra-peak pressure for said digital processor controlled automated blood pressure measuring device operative in conjunction with a stored program. (28) a) an inflatable sleeve flap; b) means for inflating and deflating said sleeve flap; and c) pressure transducer means coupled to said sleeve flap for detecting the pressure available in said sleeve flap. and d) means responsive to the pressure sensed by the transducer for generating a signal representative of the blood pressure complex sensed by the transducer and the transducer coupled thereto; and e) at different cuff pressures. complex peak storage means for storing a value characterizing the peak amplitude of said signal representing a complex; f) sleeve cover pressure storage means for storing a sleeve cover pressure obtained when said pulse peak signal occurs; and g) data purification means responsive to the values stored by said complex peak amplitude characterization means, i.e. pressure complex peak storage means for correcting inaccurate data; and h) diastolic pressure measurement means. The diastolic pressure measuring means comprises: (i) means for positioning the maximum peak amplitude stored in the complex peak storage means; and (ii) each having a different value of the peak amplitude. (iii) said maximum sleeve flap pressure pulse peak signal generated at a lower sleeve flap pressure than that obtained when said maximum sleeve flap pressure pulse peak signal was generated; means responsive to the value measured by said calculation means for selecting from a plurality of peak amplitudes of a complex peak storage means; (iv) diastolic pressure from said selected plurality of amplitudes and said and measuring means for measuring sleeve cover pressure stored in said sleeve cover pressure storage means corresponding to a plurality of selected signals, operating in conjunction with a stored program. Digital processor controlled automated blood pressure measurement device. (29) a preselected character is stored in said complex peak storage means to signal an unsuccessful capping pressure flow peak measurement, in which case said data modification means stores the contents of said complex peak storage means; and means responsive to detecting said preselected character for testing said character and for replacing said character with a plurality of stored complex peak value measurements; At least one of the complex peak values of is obtained at a higher gauze pressure than that associated with the preselected character, and at least one is obtained at a gauze pressure that is lower than that associated with the preselected character. 29. A device according to claim 28, which is obtained at pressure. (30) a preselected character is stored in said complex peak storage means to signal an unsuccessful pulse flow peak measurement, in which case said data modification means modify the contents of said complex peak storage means; means responsive to detecting the preselected character for testing and replacing the character with a plurality of stored complex peak value measurements; 29. At least one of the complex peak values is obtained by averaging the next highest and next lowest sleeve pressures than those associated with the preselected character. equipment. (31) the data purification means includes means for searching the complex storage means for occurrences of two equal peak amplitude values occurring in subsequent sleeve flap inflation pressures; 29. means responsive to said search means for substituting the next highest measured value for the next lowest value stored in said complex peak storage means. Device. (32) a) an inflatable sleeve flap; b) means for inflating and deflating the sleeve flap; and c) pressure transducer means coupled to the sleeve flap for detecting the pressure available in the sleeve flap. and d) means responsive to the pressure detected by the transducer for generating a signal representative of the blood pressure complex sensed by the transducer and the transducer coupled thereto, and e) the blood pressure complex at different cuff pressures. f) complex peak storage means for storing a value characterizing the peak amplitude of said signal representing said pulse peak signal; f) sleeve cover pressure storage means for storing a sleeve cover pressure obtained when said pulse peak signal occurs; g) data purification means responsive to complex peak amplitudes characterizing the values stored in said sleeve pressure complex peak storage means for correcting inaccurate data; and h) diastolic pressure measurement means. and (i) means for locating the maximum peak pulse amplitude stored in the complex peak storage means; and (ii) each of the peaks (iii) said complex generated at a lower sleeve pressure than that obtained when said maximum peak signal occurs; - means responsive to the value measured by said calculation means for selecting from a plurality of peak amplitudes of a peak storage means; and (iv) diastolic pressure from said selected plurality of signals and said selection. (i) measuring means for measuring the sleeve flap pressure stored in the sleeve flap pressure storage means corresponding to a plurality of signals obtained by: (i) subsequent sleeve flap inflation; 2 produced under pressure
(ii) means for searching said complex storage means for occurrences of equal peak amplitude values; and (ii) means for searching said complex storage means for occurrences of equal peak amplitude values; and means responsive to said search means for substitution with a measured value of another value.
Processor controlled automated blood pressure measurement device. (33) An automated oscillometric blood pressure unit that utilizes an arterial occluding sleeve and means for controllably inflating said sleeve to at least a mean arterial pressure, comprising: a) measuring sleeve sleeve pressure oscillation peak amplitudes; , a step associated with the sleeve cap pressure level at a predetermined increment between the sleeve cap contraction and the mean arterial pressure, and b) starting with a specified maximum amplitude close to the mean arterial pressure and moving toward the sleeve cap contraction pressure. c) identifying a first pair of adjacent amplitudes having a predetermined, first fractional relationship to the identified maximum amplitude that is close to mean arterial pressure; d) adjacencies of said amplitudes starting at a specified minimum amplitude and progressing toward a maximum sleeve pressure and having a second predetermined fractional relationship to said specified maximum amplitude; e) interpolating said second pair of adjacent amplitudes; and f) diastolic pressure as the pressure corresponding to a predetermined, weighted average value of each of said interpolated values. and identifying a diastolic pressure.