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Description  |
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TECHNICAL FIELD
The present invention relates to a method and an apparatus for continuously
and non-invasively measuring the blood pressure of a patient and, more
particularly, the present invention relates to measuring the harmonic
frequencies and displacement components of an arterial wall, and
converting the measurements into a waveform signal emulating the signal
from an invasive arterial sensor.
BACKGROUND OF THE INVENTION
Methods and apparatuses for the detection of the blood pressure of a
patient are well-known in the art. One type of apparatus involves the use
of an invasive arterial line. In an arterial line device, a sensor is
inserted into the artery of a patient. The signal from the arterial sensor
is supplied to a patient monitor which calculates, among other parameters,
the blood pressure of a patient. The patient monitor is also capable of
sending a signal to the sensor to determine if the sensor is electrically
connected to the patient monitor. Although such apparatuses provide
continuous and accurate blood pressure data, there are many disadvantages.
First, there is a potential risk of infection. Further, the procedure is
costly and consumes valuable health care takers' time, in that it is a
surgical procedure involving the insertion of a catheter into a patient's
artery. In addition, the patient experiences discomfort.
In the area of non-invasive devices, one prior art teaches the automatic
expansion of pressure cuffs and the measurement of the blood pressure
based thereon. However, such devices can only be used intermittently.
Prolonged and frequent use can lead to patient discomfort.
U.S. Pat. No. 4,669,485 teaches using two cuffs to measure the blood
pressure of a patient. The absolute blood pressure of the patient is
initially measured. Thereafter, the second cuff is maintained at a low
pressure, continuously, to monitor continuously the relative blood
pressure of the patient. In this manner, the blood pressure of the patient
can be continuously monitored. However, such a device still involves using
blood pressure cuffs, which can be a source of discomfort to the patient
and the device is subject to patient motion and as a consequence degraded
results.
In column 4, lines 39--column 5, line 3 of U.S. Pat. No. 4,669,485,
reference is made to yet another prior art non-invasive device which
measured the arterial wall displacement and used those measurements to
determine the relative blood pressure. However, the use of only the
displacement measurement is subject to error.
Reference is also made to U.S. Pat. No. 3,318,303. In that reference, the
output of an external microphone sensor is used to determine the blood
pressure of a patient. In particular, the so-called "Korotkoff" sound may
be determined.
U.S. Pat. No. 4,203,451 discloses that a data processor can be used to
receive signals from the Carotid transducer.
U.S. Pat. No. 3,773,033 discloses the use of an arterial vibration sensor
to monitor the performance of the heart and arteries during a succession
of cardiac cycles. However, a pressure cuff also applies variable pressure
to a specified artery being monitored by the arterial vibration sensor.
Heretofore, none of the prior art devices or references has suggested a
non-invasive apparatus for continuously and accurately measuring the blood
pressure of a patient using data obtained from the arterial wall, thereby
providing for greater patient comfort. Further, none of the prior art
devices has checked for the integrity of the sensor, apart from it being
merely electrically connected to the monitor.
SUMMARY OF THE INVENTION
In the present invention, an instrument for continuously and non-invasively
measuring the blood pressure of a patient is disclosed. The instrument has
a non-invasive sensor for measuring continuously the frequencies and
displacements of an arterial wall and for generating continuously a first
signal in response thereto. The first signal is processed continuously to
produce a continuous processed first signal. The instrument further
receives a calibration signal which is indicative of the absolute blood
pressure of the patient at a particular point in time. The processed first
signal corresponding to the particular point in time is stored. Finally,
the instrument compares continuously the continuous processed first signal
to the stored processed first signal and generates continuously a signal
indicative of the continuous blood pressure of the patient.
BRIEF DESCRIPTION OF THE DRAWINGS
FIG. 1 is a block level diagram of the apparatus of the present invention.
FIG. 2(a-d) are detailed schematic diagrams of various portions of the
apparatus shown in FIG. 1.
FIG. 3(a-f) are schematic diagrams showing representative waveform signals
processed and generated by the apparatus of the present invention.
DETAILED DESCRIPTION OF THE DRAWINGS
Referring to FIG. 1, there is shown a block diagram of an apparatus 10 of
the present invention. The apparatus 10 comprises a sensor assembly 12
which measures continuously, with time, the external displacement and the
harmonic frequencies of the displacement caused by the lateral expansion
of an arterial wall of a patient. The pattern of expansions and
contractions is reflective of the changes in the pressure wave at this
site in the arterial system. In one embodiment, the sensor assembly 12 has
a piezoelectric sensing material, such as Kynar film 14. The Kynar film 14
generates a signal which is directly coupled to a sensing amplifier 16,
located within the sensor assembly 12. The sensing amplifier 16 transforms
the impedance of the signal from a high value, on the order of several
megohms of the sensing film 14, to a low value which can be transmitted
over a cable 18 (typically on the order of 10 feet). The sensor assembly
12 is positioned at any site of a patient where the artery is close to the
surface of the skin, such as over the radial artery.
The sensing film 14 can be excited by an excitation signal supplied from
the control microprocessor 54 through the control microprocessor bus 52,
through an amplifier 15 and through the cable 18 to a diode 13. The
excitation signal causes the film 14 to mechanically transduce, i.e. flex.
The excitation signal is applied momentarily (on the order of one
microsecond), and is thereafter removed Because the sensing film 14 will
have been flexed by the excitation signal, upon removal of the excitation
signal, the sensing film 14 will resonate and move in the opposite
direction. This movement in the opposite direction causes the production
of a response electrical signal which is supplied along the cable 18. The
detection of this response signal indicates that the sensing film 14 is
not only electrically connected and is adapted to transduce, but is also
in fact electromechanically ready to transduce the arterial wall
movements.
The sensor assembly 12 is then positioned to detect arterial wall motion.
The signal detected by the sensor assembly 12, caused by the motion of the
arterial wall, is then supplied to an input amplifier 20 which removes any
DC component from the signal (FIG. 3a ). The input amplifier 20 comprises
an AC voltage amplifier and high pass filter 22 which receives the signal
from the cable 18 and supplies an output thereof to a programmable gain DC
voltage amplifier 24. The purpose of the programmable gain DC voltage
amplifier 24 is to compensate for variations in the sensitivity of
different sensors and physical variations among different patients. The
output of the programmable gain DC voltage amplifier 24 is then supplied
to a fixed gain DC amplifier and low pass filter 26. The DC amplifier and
low pass filter 26 provides an output which is supplied to an
analog-to-digital converter 28. The output of the input amplifier 20 is
set to optimize the signal of the analog-to-digital converter 28.
The analog-to-digital converter 28 is a bipolar 10-bit A-to-D converter
which receives a reference voltage 30 of 2.5 volts. The analog-to-digital
converter 28 digitizes the input analog signal at the rate of
approximately 250 hertz or one conversion each four milliseconds.
The output of the bipolar analog-to-digital converter 28 is then supplied
to a first-in-first-out (FIFO) buffer 32. The data is stored in the FIFO
buffer 32 until a predetermined number of samples are collected. In one
embodiment, the apparatus 10 of the present invention waits until there
are 16 samples in the FIFO buffer 32 before the data from the FIFO buffer
32 are read out and are supplied to the DSP microprocessor bus 36 and are
then further processed.
Further, the eight most significant bits (MSB) of the ten bits from the
analog-to-digital converter 28 of each sensor sample are stored in an
8-bit latch 34. The output of the 8-bit latch 34 is supplied to the
control microprocessor bus 52 and can be supplied to an external or
internal display screen 74. By outputting the relative signal strength of
the sensor assembly 12 and displaying it on the display 74, the apparatus
10 permits the operator to move the sensor assembly 12 to optimally place
the sensor assembly 12 on the patient.
After the FIFO buffer 32 is filled with the predetermined number of
digitized sensor samples, the digital signal processor (DSP) 38 is
interrupted. The contents of the FIFO buffer 32 is then transferred to the
DSP microprocessor bus 36 and into the DSP working memory 42. In one
embodiment, the DSP working memory 42 comprises 16K by 16 bits of random
access memory (RAM) 46 and two multiplexed memory address counters 44. One
memory address counter addresses RAM 46 when writing data to the RAM 46.
The other memory address counter addresses RAM 46 when reading data from
RAM 46. Each counter can be set to automatically increment or decrement
after a read or write operation is completed. This increases processing
throughput, since the DSP microprocessor 38 does not have to address each
operation. The memory address counters 44 supply 14 address lines to
address the 16K by 16 RAM memory 46. The DSP microprocessor 38 is under
the control of a program which is stored in a program memory 40. The DSP
microprocessor 38 is a TMS-32010 made by Texas Instruments. The program
memory 40 comprises 4K by 16 bits of PROM.
The program stored in the program memory 40 controls the DSP processor 38
to process the data from the FIFO buffer 32 to convert the sensor data
into data values of a signal representative of the output blood pressure A
copy of the program is attached herewith as Exhibit A. The function of the
program stored in the program memory 40 will be described hereinafter.
After the DSP microprocessor 38 has completed the processing of the sensor
signal data from the FIFO buffer 32 and into a waveform signal data, the
waveform signal data are passed to and stored in the monitor data FIFO
buffer 50.
From the monitor data FIFO buffer 50, the computed points of the waveform
signal may be directed to display on the display screen 74. The handshake
register 48 links the DSP microprocessor 38 with the control
microprocessor 54, by means of the DSP bus 36 and the control bus 52. Both
data and control commands can be passed between the two processors by this
register 48. Since the monitor data FIFO buffer 50 is loaded with and
relieved of data at the same rate as the original sensor data FIFO buffer
32, the computed points which comprise the waveform are displayed at the
rate of one data point for each four milliseconds.
The control microprocessor 52 also operates under a program which is stored
in the program memory 60. A copy of that program is attached herewith as
Exhibit B. The control microprocessor 52 is a 80C31 made by Intel
Corporation.
The apparatus 10 of the present invention can also supply the waveform
signal data from the DSP microprocessor 38 to an external patient monitor
68. When the apparatus 10 functions in this manner, it is acting as an
arterial sensor emulator, i.e. to the patient monitor 68, the signal
supplied thereto is no different than the signal generated by an arterial
sensor. The data is supplied to an eight-bit multiplying digital-to-analog
converter 64 which emulates a normal dome pressure transducer, which is
conventionally used to convert invasive arterial line fluid pressure
sensor to electrical signals for input to the patient monitor 68. The
monitor 68 outputs its normal excitation voltage and, in turn, receives an
input signal of the expected sensitivity expressed as microvolts output
per volt of excitation per millimeter of mercury of pressure from the
analog simulator 64.
The analog simulator 64 consists of an 8-bit multiplying digital-to-analog
converter 66, which converts digital values received from the monitor data
FIFO buffer 50 sent along the control bus 52, into an analog signal,
required by the external patient monitor 68. The programmable
amplifier/low pass filter 65 varies the output level of the analog signal
in accordance with the input sensitivity of the particular patient monitor
68 being used. Thus, some of the commonly used patient monitors 68 require
the following input sensitivities:
Hewlett-Packard: 5 uv input/volt of excitation/ mm Hg.
Marquette: 20 uv input/volt of excitation/ mm Hg.
In the operation of the apparatus 10 of the present invention, the
apparatus 10 is initially placed in a calibration mode. In this
calibration mode, the operator identifies the patient monitor 68 with
which the apparatus 10 is connected through the analog simulator 64. The
selection of the particular patient monitor 68 sets the programmable
amplifier 65 to the correct output voltages.
Thereafter, the apparatus 10 sends to the patient monitor 68 a signal that
the patient monitor 68 expects during the venting of the arterial line
dome that is normally connected to the arterial line port. When the
operator confirms the completion of the above steps, the apparatus 10 then
shifts into the next mode of operation, the acquire mode.
In the acquire mode, the apparatus 10 provides a check that the sensor
assembly 12 is connected to the apparatus 10. As previously discussed,
this includes supplying the excitation signal and the detection of the
response signal. The detection of the response signal from the sensing
film 14 indicates that the sensor assembly 12 is electrically connected
and the sensing film 14 is electromechanically operational. The apparatus
10 acquires and displays the raw pulse vibration signal that the sensor
assembly 12 detects for the purpose of positioning the sensor assembly 12
optimally. Upon command by the operator, the apparatus 10 acquires and
stores the previous four-second segment of the pulse vibration signal for
correlation with the starting blood pressure values.
The DSP microprocessor 38 then processes the signal corresponding to the
four-second segment from the FIFO buffer 32. The DSP microprocessor 38
determines the characteristic components of the input signal in accordance
with the following steps:
1. The input signal comprising approximately four (4) seconds of data at a
sample frequency of 4 milliseconds is stored in the working memory 42
(FIG. 3a).
2. The input signal is fast fourier transformed at approximately 0.25 Hz.
interval from approximately 0-250 Hz., thereby generating 1024 frequency
values, with each frequency value having an amplitude value (FIG. 3d).
3. The frequency that corresponds to the maximum amplitude value is
determined.
4. All the amplitudes of the spectrum data are normalized to the frequency
found in step 3, with that amplitude as 100.
5. The normalized fast fourier transformed signal is stored in the working
memory 42.
After the DSP microprocessor 38 has completed the processing of the sensor
signal from the FIFO buffer 32 the apparatus 10 shifts to the BP input
mode.
In the BP input mode, the apparatus 10 requests the operator to input the
patient's absolute blood pressure values as measured by an independent
blood pressure apparatus. The absolute blood pressure values may be
manually determined by a health care worker and entered into the apparatus
10 via the panel buttons 78. Alternatively, the absolute blood pressure
values may be supplied from a conventional, well known, automatic blood
pressure monitor 90, such as a pressure cuff measuring instrument 90. The
data from the blood pressure monitor 90 is supplied to the apparatus 10
along an RS-232 input line 92, to the LCD controller 70, just like the
inputs from the panel buttons 78. Since the apparatus 10 of the present
invention 10 requires correlation with absolute blood pressure value only
during the initial stage, the automatic blood pressure monitor 90, even if
it were of pressure cuff design, would not pose the disadvantages of
continual use.
The absolute blood pressure values correspond to the correlated, stored
four-second segment sensed by the sensor assembly 12. When the operator
confirms the conclusion of the input blood pressure value, the DSP
microprocessor 38 performs the following steps:
a. The four-seconds of data stored in memory 42 (from step 1, above) are
integrated (FIG. 3b).
b. A first scale factor is calculated. The first scale factor is chosen
such that the maximum absolute amplitude of the waveform signal found in
step a times the first scale factor would equal the pulse pressure (pulse
pressure=systolic - diastolic) (FIG. 3c).
c. An offset (equal to the diastolic) is added to the waveform of step b
(FIG. 3c).
d. The processed waveform signal from step c is stored in the memory 42.
In sum, during the input mode, the DSP microprocessor 38 calculates the
first scale factor and the offset. The waveform generated by the apparatus
10 (from step c), after passing through the analog simulator 64, would be
as if the waveform signal were generated by an invasive arterial sensor.
Thus, the apparatus 10 emulates an invasive arterial sensor. The apparatus
10 then enters into the monitor mode.
In the monitoring mode, the apparatus 10 continuously receives the signal
from the output of the sensor assembly 12 and continuously processes that
signal via the input amplifier 20, digital-to-analog converter 28 and the
sensor data FIFO buffer 32. The DSP microprocessor 38 continuously
processes the digitized signal in the following manner.
6. The digitized signal from the FIFO buffer 32 is processed in accordance
with steps 1-5 above.
7. The normalized frequency spectrum of the current signal from step 6 is
subtracted from the normalized frequency spectrum of the initial signal,
as stored in working memory 42 (FIG. 3e or 3f).
8. A comparison is made between the maximum frequency of the normalized
frequency of the current signal and of the initial signal.
9. The change in the amount of the maximum frequency is noted and is
supplied to the following look up table, and the corresponding second
scale factor is determined:
______________________________________
Change of Maximum Frequency
Second Scale Factor
______________________________________
50% 85%
67% 90%
83% 95%
100% 100%
133% 105%
167% 110%
200% 115%
______________________________________
10. A comparison is made between the frequency of the maximum amplitude of
the current signal to the initial signal For each shift in frequency (+or
-) of 1 Hz., the offset (determined from step c) is adjusted
correspondingly to yield a change of 5 mm Hg. Thus, if the frequency of
the maximum amplitude of the current signal is increased 1 Hz. from the
frequency of the maximum amplitude of the initial signal, the offset for
the initial signal is increased by an amount equal to 5 mm Hg.
11. The data points from the FIFO buffer 32 are integrated.
12. The data points from step 11 are multiplied by the first scale factor
and by the second scale factor, and the new offset (from step 10) is added
to the resultant waveform signal.
The points that represent the waveform signal (step 12) are supplied to the
monitor data FIFO buffer 50 and then to the analog simulator 64 or LCD
controller 70 for display on the external patient monitor 68 or internal
LCD display 74. The steps of 6-12 are repeated for each new four-second
segment of data.
In another embodiment of the present invention, the health care worker can
supply operating limits to the apparatus 10 by way of the input panel
buttons 78. When the current signal, processed by the DSP microprocessor
38, is outside of the operating limits, an alarm can be sounded to alert
the health care worker. Alternatively, the LCD controller 70 can initiate
a control signal to the automatic blood pressure monitor 90 to re-initiate
the apparatus 10.
From the foregoing, it can be seen that a highly accurate and efficient
blood pressure measuring apparatus and method has been disclosed.
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