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1Motorola Sensor Device Data
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Prepared by: C.S. Chua and Siew Mun HinSensor Application EngineeringSingapore, A/P
INTRODUCTION
This application note describes a Digital Blood PressureMeter concept which uses an integrated pressure sensor,analog signal–conditioning circuitry, microcontrollerhardware/software and a liquid crystal display. The sensingsystem reads the cuff pressure (CP) and extracts the pulsesfor analysis and determination of systolic and diastolicpressure. This design uses a 50 kPa integrated pressuresensor (Motorola P/N: MPX5050GP) yielding a pressurerange of 0 mmHg to 300 mmHg.
CONCEPT OF OSCILLOMETRIC METHOD
This method is employed by the majority of automatednon–invasive devices. A limb and its vasculature arecompressed by an encircling, inflatable compression cuff. Theblood pressure reading for systolic and diastolic bloodpressure values are read at the parameter identification point.
The simplified measurement principle of the oscillometricmethod is a measurement of the amplitude of pressurechange in the cuff as the cuff is inflated from above the systolicpressure. The amplitude suddenly grows larger as the pulsebreaks through the occlusion. This is very close to systolicpressure. As the cuff pressure is further reduced, the pulsationincrease in amplitude, reaches a maximum and thendiminishes rapidly. The index of diastolic pressure is takenwhere this rapid transition begins. Therefore, the systolic
blood pressure (SBP) and diastolic blood pressure (DBP) areobtained by identifying the region where there is a rapidincrease then decrease in the amplitude of the pulsesrespectively. Mean arterial pressure (MAP) is located at thepoint of maximum oscillation.
HARDWARE DESCRIPTION AND OPERATION
The cuff pressure is sensed by Motorola’s integratedpressure X–ducer . The output of the sensor is split into twopaths for two different purposes. One is used as the cuffpressure while the other is further processed by a circuit.Since MPX5050GP is signal–conditioned by its internalop–amp, the cuff pressure can be directly interfaced with ananalog–to–digital (A/D) converter for digitization. The otherpath will filter and amplify the raw CP signal to extract anamplified version of the CP oscillations, which are caused bythe expansion of the subject’s arm each time pressure in thearm increases during cardiac systole.
The output of the sensor consists of two signals; theoscillation signal ( ≈ 1 Hz) riding on the CP signal ( ≤ 0.04 Hz).Hence, a 2–pole high pass filter is designed to block the CPsignal before the amplification of the oscillation signal. If theCP signal is not properly attenuated, the baseline of theoscillation will not be constant and the amplitude of eachoscillation will not have the same reference for comparison.Figure 1 shows the oscillation signal amplifier together withthe filter.
Figure 1. Oscillation Signal Amplifier
C2
+5V
R2
–
+
+DC offset
U1a
3
21
150k
LM324N0.33u
Vi
R3 1M 11
4
Vo
R1
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C1
33u
Order this documentby AN1571/D
��� ���SEMICONDUCTOR APPLICATION NOTE
Motorola, Inc. 1997
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2 Motorola Sensor Device Data
The filter consists of two RC networks which determine twocut–off frequencies. These two poles are carefully chosen toensure that the oscillation signal is not distorted or lost. The
two cut–off frequencies can be approximated by the followingequations. Figure 2 describes the frequency response of thefilter. This plot does not include the gain of the amplifier.
10
0
–10
–20
–30
–40
–50
–60
–70
–8010 10010.10.01
Frequency (Hz)
Figure 2. Filter Frequency Response
Oscillation Signal (1 Hz)
CP Signal (0.04 Hz)
Atte
nuat
ion
(dB)
fP1 =1
2�R1C1
fP2 =1
2�R3C2
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3Motorola Sensor Device Data
The oscillation signal varies from person to person. Ingeneral, it varies from less than 1 mmHg to 3 mmHg. From thetransfer function of MPX5050GP, this will translate to a voltageoutput of 12 mV to 36 mV signal. Since the filter gives anattenuation of 10 dB to the 1 Hz signal, the oscillation signalbecomes 3.8 mV to 11.4 mV respectively. Experiments
indicate that, the amplification factor of the amplifier is chosento be 150 so that the amplified oscillation signal is within theoutput limit of the amplifier (5 mV to 3.5 V). Figure 3(a) showsthe output from the pressure sensor and Figure 3(b) shows theextracted oscillation signal at the output of the amplifier.
Figure 3. CP signal at the output of the pressure sensor
Oscillation signal is extracted here
3
2.5
2
1.5
1
0.5
00 5 10 15 20 25 30 35 40
Time (seconds)
Vi (
volts
)
3
2.5
2
1.5
1
0.5
0
Vo
(vol
ts)
10 15 20 25 30 35
Time (seconds)
MAP
DBPSBP
3.5
Figure 3b. Extracted oscillation signal at the output of amplifier
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4 Motorola Sensor Device Data
Referring to the schematic, Figure 4, the MPX5050GPpressure sensor is connected to PORT D bit 5 and the outputof the amplifier is connected to PORT D bit 6 of themicrocontroller. This port is an input to the on–chip 8–bitanalog–to–digital (A/D) converter. The pressure sensorprovides a signal output to the microprocessor ofapproximately 0.2 Vdc at 0 mmHg to 4.7 Vdc at 375 mmHg ofapplied pressure whereas the amplifier provides a signal from0.005 V to 3.5 V. In order to maximize the resolution, separatevoltage references should be provided for the A/D instead ofusing the 5 V supply. In this example, the input range of the A/Dconverter is set at approximately 0 Vdc to 3.8 Vdc. Thiscompresses the range of the A/D converter around 0 mmHgto 300 mmHg to maximize the resolution; 0 to 255 counts is therange of the A/D converter. VRH and VRL are the referencevoltage inputs to the A/D converter. The resolution is definedby the following:
Count = [(VXdcr – VRL)/(VRH – VRL)] x 255
The count at 0 mmHg = [(0.2 – 0)/(3.8 – 0)] x 255 ≈ 14The count at 300 mmHg = [(3.8 – 0)/(3.8 – 0)] x 255 ≈ 255Therefore the resolution = 255 – 14 = 241 counts. This
translates to a system that will resolve to 1.24 mmHg.The voltage divider consisting of R5 and R6 is connected to
the +5 volts powering the system. The output of the pressuresensor is ratiometric to the voltage applied to it. The pressuresensor and the voltage divider are connected to a commonsupply; this yields a system that is ratiometric. By nature of this
ratiometric system, variations in the voltage of the powersupplied to the system will have no effect on the systemaccuracy.
The liquid crystal display (LCD) is directly driven from I/Oports A, B, and C on the microcontroller. The operation of aLCD requires that the data and backplane (BP) pins must bedriven by an alternating signal. This function is provided by asoftware routine that toggles the data and backplane atapproximately a 30 Hz rate.
Other than the LCD, there are two more I/O devices that areconnected to the pulse length converter (PLM) of themicrocontroller; a buzzer and a light emitting diode (LED). Thebuzzer, which connected to the PLMA, can produce twodifferent frequencies; 122 Hz and 1.953 kHz tones. Forinstance when the microcontroller encounters certain errordue to improper inflation of cuff, a low frequency tone is alarm.In those instance when the measurement is successful, a highfrequency pulsation tone will be heard. Hence, differentmusical tone can be produced to differential each condition. Inaddition, the LED is used to indicate the presence of a heartbeat during the measurement.
The microcontroller section of the system requires certainsupport hardware to allow it to function. The MC34064P–5provides an undervoltage sense function which is used toreset the microprocessor at system power–up. The 4 MHzcrystal provides the external portion of the oscillator functionfor clocking the microcontroller and provides a stable base fortime based functions, for instance calculation of pulse rate.
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5Motorola Sensor Device Data
Figure 4. Blood Pressure Meter Schematic Drawing
PC
0P
C1
PC
2/E
CLK
PC
3P
C4
PC
5P
C6
PC
7
PD
0/A
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+5V
+5V
+5V
+5V
+5V
+5V
+5V
Pre
ssur
e S
enso
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3
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9V Battery
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1
1
2
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ator
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78L0
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zer
0.33
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C2
3
1
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24k
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1M
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R1 C1
1k33u
150kR2
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R8
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100u
C8
C6
330u
R10
10M
X1
4MH
z
C3
C4
22p
22p
PD
1/A
N1
PD
2/A
N2
PD
3/A
N3
PD
4/A
N4
PD
5/A
N5
PD
6/A
N6
PD
7/A
N7
PLM
BP
LMA
SC
LKT
DO
TC
MP
2T
CM
P1
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D
OS
C2
MC
68H
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B16
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N
OS
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SE
T/IR
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1T
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P2
RD
VR
HV
RL
PA
0P
A1
PA
2P
A3
PA
4P
A5
PA
6P
A7
PB
0P
B1
PB
2P
B3
PB
4P
B5
PB
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R6R5
4.7k + 36R 15kR9
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3406
4
Res
etIn
put
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D
LCD
5657
1
32
17 10 2 1 52 51 20 21 49 48 47 46 45 44 43 42 14 13 12 11 9 5 4 33233343536373839242526272829303178502322191816
16 23 22 21 20 19 18 17 12 27 26 25 24 15 14 13
CB
AG
1DD
PE
F
2
DP
LL
3
DP
4
DP
1
G1
F1
A1
B1
C1
D1
E1
DP
2
G2
F2
A2
B2
C2
D2
E2
37 36 35 34 7 6 5 28 40 1 8 32 31 30 29 11 10 9
G4
F4
A4
B4
C4
D4
E4 L
BP
BP
DP
3
G3
F3
A3
B3
C3
D3
E3
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6 Motorola Sensor Device Data
SOFTWARE DESCRIPTIONUpon system power–up, the user needs to manually pump
the cuff pressure to approximately 160 mmHg or 30 mmHgabove the previous SBP. During the pumping of the inflationbulb, the microcontroller ignores the signal at the output of the
amplifier. When the subroutine TAKE senses a decrease inCP for a continuous duration of more than 0.75 seconds, themicrocontroller will then assume that the user is no longerpumping the bulb and starts to analyze the oscillation signal.Figure 5 shows zoom–in view of a pulse.
–7.1–7.3–7.5–7.7–7.9–8.1–8.3–8.5
Time (second)
Figure 5. Zoom–in view of a pulse
Vo (v
olt)
450 ms
Premature pulse
1.75
First of all, the threshold level of a valid pulse is set to be 1.75V to eliminate noise or spike. As soon as the amplitude of apulse is identified, the microcontroller will ignore the signal for450 ms to prevent any false identification due to the presenceof premature pulse ”overshoot” due to oscillation. Hence, thisalgorithm can only detect pulse rate which is less than 133beats per minute. Next, the amplitudes of all the pulsesdetected are stored in the RAM for further analysis. If themicrocontroller senses a non–typical oscillation envelope
shape, an error message (“Err”) is output to the LCD. The userwill have to exhaust all the pressure in the cuff beforere–pumping the CP to the next higher value. The algorithmensures that the user exhausts all the air present in the cuffbefore allowing any re–pumping. Otherwise, the venous bloodtrapped in the distal arm may affect the next measurement.Therefore, the user has to reduce the pressure in the cuff assoon as possible in order for the arm to recover. Figure 6 is aflowchart for the program that controls the system.
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7Motorola Sensor Device Data
Figure 6. Main program flowchart
MAIN PROGRAM
InitializationClear I/O ports
Display ”CAL” andoutput a musical tone
Clear all the variables
Take in the amplitude of all theoscillation signal when the
user has stop pumping
Calculate the SBP and DBPand also the pulse rate
Repump?
Is there any errorin the calculation or the
amplitude envelopedetected?
Output a highfrequency
musical tone
Exhaust cuffbefore repump
Exhaust cuffbefore repump
Display pulse rate.Display ”SYS” follow by SBP.Display ”dlA” follow by DBP.
Display ”Err”
Output a lowfrequency
alarm
N
N
N N
Y
Y
Y Y
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8 Motorola Sensor Device Data
SELECTION OF MICROCONTROLLERAlthough the microcontroller used in this project is
MC68HC05B16, a smaller ROM version microcontroller canalso be used. The table below shows the requirement ofmicrocontroller for this blood pressure meter design in thisproject.
Table 1. Selection of microcontroller
ÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁ
On–chip ROM space 2 kilobytesÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁ
On–chip RAM space 150 bytesÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁ2–channel A/D converter (min.)ÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁ16–bit free running counter timerÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁ
LCD driverÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁ
On–chip EEPROM space 32 bytes
ÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁÁ
Power saving Stop and Wait modes
CONCLUSION
This circuit design concept may be used to evaluateMotorola pressure sensors used in the digital blood pressuremeter. This basic circuit may be easily modified to providesuitable output signal level. The software may also be easilymodified to provide better analysis of the SBP and DBP of aperson.
REFERENCES
Lucas, Bill (1991). “An Evaluation System for Direct Interfaceof the MPX5100 Pressure Sensor with a Microprocessor,”Motorola Application Note AN1305.
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