JPH05164054A - Fluid feed pumping device - Google Patents

Abstract

PURPOSE:To reduce dispersion of driving flow rate for every pulse, dispense substantially with setting of delivery timing, and simplify driving flow rate adjusting work by suction quantity through integration of the suction flow speed, and constituting the device so as to be switched from suction to delivery when the suction quantity reaches a preset value. CONSTITUTION:A fluid feed pumping device is constituted in such a way that there are provided a flow speed detecting means 13 to detect a flow speed of blood entering a fluid receiving space from a fluid receiving port and the first control means to connect an operating fluid space to low pressure fluid sources 32n and 35 when a time during which connecting/switching means 31n and 31p connect the operating fluid space to high pressure fluid sources 32p and 35 reaches a preset time, and integral on the flow speed is carried out while the operating fluid space is connected to the low pressure fluid sources 32n and 35, and a signal to show an integral value is generated by an integral means, and when the integral value reaches a preset value, the operating oil space is connected to the high pressure fluid sources 32p and 35 by the second control means.

Description

Detailed Description of the Invention

[0001]

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to a fluid delivery pumping device for delivering a fluid under pressure to a fluid receiving port under pressure, and although not particularly limited to this, it assists the heart to deliver it from the left atrium. The present invention relates to a pumping device that pressurizes and delivers blood to the aorta while substantially maintaining its flow rate.

[0002]

2. Description of the Related Art For example, a pulsatile artificial heart pump for assisting the operation of the heart controls systolic timing, diastolic timing, ejection force, suction force, etc. to adjust the auxiliary flow rate. Have interactions and multiple parameters
The adjustment work to set the parameters as intended is complicated. However, in an artificial heart that sucks the blood of the heart and sends it to the aorta, it is not preferable to apply a suction negative pressure higher than the blood feeding ability of the heart to the heart, because a large external action is applied to the heart.

In Japanese Unexamined Patent Publication No. Sho 62-94171, two pumps are connected in parallel to each other and are inserted between the left atrium of the heart and the aorta, and one pump stores blood discharged by the heart. A pumping device is proposed in which while the other pump is being pressurized (inhalation period), the blood contained therein is pressurized and delivered to the aorta (delivery period), and this is repeated alternately. Each pump includes a working pressure chamber to which a driving pressure is applied and a sack that is inside the working pressure chamber and encloses the blood receiving space. During the inhalation period, the working pressure chamber of the pump is released to the atmospheric pressure so as not to apply an excessive negative pressure to the heart, and blood naturally enters the blood receiving space in the suck of the pump by the discharge pressure of the heart. Suck is
Depending on the pressure in the working pressure chamber, it contracts when it is higher than atmospheric pressure to contract the blood receiving space, and when the working pressure chamber is released to atmospheric pressure, the sac expands due to the pressure of blood flowing into the blood receiving space. The blood receiving space expands. To monitor the contraction / expansion movement of the sack, the position of the largest reciprocating motion of the sack is detected, and it corresponds to the time from the end of suction of one pump to the end of discharge of the other pump. So that the time becomes substantially zero, that is, when the suction of one pump ends, the discharge of the other pump ends, and at this time, the suction period and the discharge period of both pumps are switched, The positive pressure value given to both pumps is adjusted. With this, the blood is pressurized and delivered to the aorta by the pumping device without disturbing the discharge flow rate of the heart, and further, the pumping delivery flow rate (driving flow rate) changes automatically in accordance with the fluctuation of the discharge flow rate of the heart. Therefore, this pumping does not impose a particular burden on the heart, and realizes blood delivery assistance that automatically adapts to the operating state of the heart, that is, the physiological state of the living body, especially its change.

[0004]

By the way, the distance of the light reflector or the magnetized magnetic body provided in the sack is detected by an optical sensor or a hall IC mounted on the outer wall of the pump, and when the distance becomes less than a set value, the suction period is reached. When it is determined that the end of the period has been reached, the suction is switched to the discharge, but since the sack fluctuates, the distance detection accuracy is low and the suction period varies. That is, the inhalation amount of one beat varies.

A first object of the present invention is to simplify the drive flow rate adjusting work of the pumping device, and a second object thereof is to reduce the variation in the drive flow rate.

[0006]

A fluid pumping device of the present invention divides a fluid receiving space (5) and a working fluid space (6) and reciprocates in a direction of contracting / expanding the fluid receiving space (5). The first pumping action body (4), which is inserted between the fluid receiving port (7) and the fluid receiving space (5), allows the fluid to flow from the former to the latter and prevents the fluid from flowing in the opposite direction. Check valve (10), and
It has a second check valve (11) which is inserted between the fluid outlet (8) and the fluid receiving space (5) and allows the fluid to flow from the latter to the former but prevents the fluid from flowing in the reverse direction. Pump (1); Flow velocity detecting means (13, 14h, 17, 18) for detecting the flow velocity (V) of the fluid entering the fluid receiving space (5) from the fluid receiving port (7); Low pressure fluid source (32n, 35) ; High pressure fluid source (32p, 35); Working fluid space (6), Low pressure fluid source (32n, 35)
And the high-pressure fluid source (32p, 35) for selectively connecting the connection switching means (31n, 31p); the connection switching means (31n, 31p) the working fluid space (5) high-pressure fluid source (32p, 35) The first control means (18) for connecting the working fluid space (6) to the low pressure fluid source (32n, 35) by the connection switching means (31n, 31p) when the time connected to is reached to the set time (Ts) An integrating means (18) for integrating the flow velocity (V) while the working fluid space (6) is connected to the low pressure fluid source (32n, 35) and generating a signal representing an integrated value (Qm); When the integral value (Qm) reaches the set value (Qs), the connection control means (31n, 31p) connects the working fluid space (6) to the high pressure fluid source (32p, 35) by the second control means (18); Prepare The symbols in parentheses indicate the corresponding elements in the embodiments described later with reference to the drawings.

[0007]

[Operation] (A) While the working fluid space (6) is connected to the high-pressure fluid source (32p, 35) (discharging stroke), the pumping body (4)
Moves in a direction in which the working fluid space (6) is expanded and the fluid receiving space (5) is contracted, and the fluid in the fluid receiving space (5) is discharged from the fluid delivery port (8). When the discharge drive time reaches the set time (Ts), the first control means (18) connects the working fluid space (5) to the low pressure fluid source (32n, 35) by the connection switching means (31n, 31p). .. As a result, the pumping body (4) moves in a direction in which the working fluid space (6) is contracted and the fluid receiving space (5) is widened, and the fluid receiving port (7) is moved.
Fluid is sucked into the receiving space (5) through the suction (suction stroke). The flow velocity detecting means (13, 14h, 17, 18) detects the flow velocity (V) of the fluid entering the fluid receiving space (5) from the fluid receiving port (7), and the working fluid space (5) is a low pressure fluid source ( During the intake stroke connected to 32n, 35), the integration means (18) integrates this flow velocity (V) and generates a signal representing the integrated value (Qm). (B) Then, the second control means (18) causes the integrated value (Qm) to be the set value.
When it reaches (Qs), the connection switching means (31n, 31p) connects the working fluid space (6) to the high pressure fluid source (32p, 35). Below, (A)-
(B)-(A)-(B) -... is repeated, discharge drive for the set time (Ts), and suction drive until the suction amount (Qm) reaches the set value (Qs), Are repeated alternately. By setting the discharge drive time (Ts) and discharge pressure (Pps) to values that are sufficient to discharge substantially all of the suction amount for the set value (Qs) within that time, the set value (Qs) When a minute is inhaled, the suction stroke is automatically switched to the discharge stroke. This makes it substantially unnecessary for the operator to set or adjust the timing of switching from the intake stroke to the discharge stroke and to set or adjust the timing of switching from the discharge stroke to the intake stroke. In addition, the discharge amount (that is, the suction amount) in one beat (one cycle) is a set value (Qs) and is constant, and this variation is extremely small.

When the fluid supply side (living body) has a high fluid supply capacity (easy blood collection), the inhalation period (Tm) becomes short because the inhalation amount (Qm) reaches the set value (Qs) early in the inhalation stroke. , The time series average pumping flow rate automatically increases.
When the fluid supply side (living body) has a low fluid supply capacity (it is difficult to collect blood), it takes a long time (Tm) for the inhalation rate (Qm) to reach the set value (Qs), and the time-series average pumping flow rate is automatically set. Will be low. In this way, the fluid (blood) is pressurized and delivered by the pumping device without disturbing the discharge flow rate of the fluid supply side (living heart), and the discharge flow rate of the fluid supply side (living heart) is automatically changed. Since the pumping delivery flow rate (driving flow rate) changes following this, this pumping does not impose a particular burden on the fluid supply side (living heart), and the operating state of the fluid supply side (living heart) (ie A fluid (blood) delivery assistance that automatically adapts to physiological conditions), especially its changes, is realized.

Other objects and features of the present invention will become apparent from the following description of embodiments with reference to the drawings.

[0010]

1 and 2 show an embodiment of the present invention.
FIG. 1 shows a pump 1, a low pressure source for supplying negative pressure (low pressure) thereto, a high pressure source for supplying high pressure air, and an electromagnetic switching valve 31n for alternately applying negative pressure and high pressure air to the pump 1. , 31p, and FIG. 2 shows a control device. It should be noted that by overlapping the same alphabetical symbols of a to h of FIG. 1 and a to h of FIG. 2, an overall view of one embodiment of the present invention appears. 3 shows an enlarged cross section of the pump 1. FIG. 3 (a) shows an enlarged cross section of the fluid receiving port 7 taken along line 3a-3a (intake stroke state) of FIG. (B) shows the fluid outlet 8 cut vertically, 3b-3 in FIG.
An enlarged cross section of the b line (state of the discharge stroke) is shown. Below, pump 1
Is manufactured as an artificial heart (auxiliary heart) and its fluid receiving port 7
Is connected to the left atrium of the heart of the living body (patient), and the fluid delivery port 8
Are connected to the aorta.

The inner space of the pump 1 surrounded by the envelopes 2 and 3 is divided by a diaphragm 4 into a blood (fluid) receiving space 5 and an air (working fluid) receiving space 6. Due to the negative pressure applied to the diaphragm 4 via the air-receiving space 6, the blood that has arrived at the fluid receiving port 7 has the first check valve 10 (see FIG. 3).
A) is pushed to be sucked into the blood receiving space 5. When high-pressure air is switched and supplied to the air-receiving space 6, a positive pressure is applied to the diaphragm 4 via the air-receiving space 6, and the blood in the blood receiving space 5 receives the second check valve 11 (b in FIG. 3). ) To go through the fluid outlet 8 to the aorta.

The air receiving space 6 is connected to the output ports of the electromagnetic on-off valves 31n and 31p through an air port 9. A negative pressure accumulator 32n is connected to the input port of the electromagnetic on-off valve 31n for supplying the negative pressure, and the electromagnetic on-off valve 31n is driven by a valve member when the electric coil is energized to output the output port. The port (9) is connected to the input port (accumulator 32n), but when not energized, the compression coil spring drives the valve member back to output the output port.
The connection between the port (9) and the input port (accumulator 32n) is cut off. A positive pressure accumulator 32p is connected to the input port of the positive pressure supplying electromagnetic on-off valve 31n. When the electric coil of the electromagnetic on-off valve 31p is energized, the valve member is driven to output the output port. The port (9) is connected to the input port (accumulator 32p), but when not energized, the compression coil spring drives the valve member back to drive the output port (9) and the input port (9). The gap between the accumulator 32p) is cut off.

The accumulator 32n has an electromagnetic opening / closing valve 34.
n output ports are connected. An intake port (negative pressure supply port) of an air pump 35 driven by an electric motor 36 is connected to an input port of the electromagnetic opening / closing valve 34n. When the electric coil of the electromagnetic opening / closing valve 34n is energized, the valve member is driven to connect the output port to the input port, and the intake pressure of the air pump 35 is applied to the accumulator 32n. When the electric coil is not energized, the compression coil spring drives the valve member back to drive the pump 35 and the accumulator.
32n is cut off. In order to prevent the negative pressure (absolute value) of the intake port of the pump 35 from becoming excessive by closing the electromagnetic opening / closing valve 34n, an over-negative pressure protection valve 37 is provided at the intake port of the pump 35 to prevent overload. It is connected. Pump 35
When the negative pressure (absolute value) of the intake port of the above exceeds a set value higher than the required range, the over-negative pressure protection valve 37n opens and the atmosphere
It is sucked into the intake port of the pump 35 through n.

The accumulator 32p has an electromagnetic opening / closing valve 34.
The p output port is connected. A discharge port (high pressure supply port) of an air pump 35 driven by an electric motor 36 is connected to an input port of the electromagnetic opening / closing valve 34p. When the electric coil of the electromagnetic on-off valve 34p is energized, the valve member is driven to connect the output port to the input port, and the discharge pressure of the air pump 35 is applied to the accumulator 32p. When the electric coil is de-energized, the compression coil spring drives the valve member back to disconnect the pump 35 from the accumulator 32p. An overpressure protection valve 37p is connected to the discharge port of the pump 35 to prevent the pump 35 from being overloaded when the positive pressure at the discharge port of the pump 35 becomes excessive by closing the electromagnetic opening / closing valve 34p. When the positive pressure at the discharge port of the pump 35 exceeds a set value higher than the required range, the overpressure protection valve 37p opens, and the high pressure air at the discharge port of the pump 35 goes out to the atmosphere through the valve 37p.

While the pump 1 is being driven, the accumulator 3
The negative pressure of 2n is detected by the pressure sensor 33n. When the detected pressure is higher than the target pressure (Pns) (low in absolute value), the electromagnetic opening / closing valve 34n is opened, and when low (high in absolute value), it is closed. The target pressure (Pns) is maintained substantially at all times. The negative pressure of the accumulator 32p is detected by the pressure sensor 33p,
When the detected pressure is higher than the target pressure (Pps), the solenoid on-off valve 34p is closed, and when the detected pressure is lower than the target pressure (Pps), the electromagnetic on-off valve 34p is opened, and the target pressure (Pps) is always kept substantially.
Maintained at.

Therefore, the solenoid opening / closing valve 31 for supplying positive pressure
Solenoid on / off valve 31 for negative pressure supply by deenergizing (off) p
When n is energized (turned on), a negative pressure of the target pressure (Pns) is supplied to the air-receiving space 6 of the pump 1, and the diaphragm 4 moves in a direction to expand the blood receiving space 5 (suction stroke). De-energize the solenoid on-off valve 31n for supplying negative pressure (OFF)
When the electromagnetic on-off valve 31p for supplying positive pressure is energized (turned on), the positive pressure of the target pressure (Pps) is supplied to the air-receiving space 6 of the pump 1 so that the diaphragm 4 contracts the blood receiving space 5. Move (discharging stroke).

The suction pipe connected to the fluid receiving port 7 has a flow velocity sensor 1 of an electromagnetic flow meter for detecting the flow velocity of blood flowing therein.
3 (a in FIGS. 1 and 3) is attached. This flow velocity sensor has a signal processing circuit 1 of the control device 12 via a signal line.
4h (FIG. 2). Signal processing circuit 14h
Generates a flow velocity signal representing the flow velocity of blood flowing through the suction tube to which the flow velocity sensor 13 is attached. This flow velocity signal is given to the A / D converter 17 via the input / output port 16, the A / D converter 17 converts the flow velocity signal into digital data, and this digital data is converted. It is read by a microprocessor (hereinafter referred to as CPU) 18.

The electric coils of the solenoid on-off valves 31n, 31p, 34n and 34p are connected to solenoid drivers 14f, 14g, 14c and 14b of the control unit 12, respectively, and these drivers 14f, 14g and 14p are connected.
c and 14b turn on (energize) / turn off (non-energize) the electric coil according to an instruction from the CPU 18. That is, each electromagnetic on-off valve is opened / closed.

Electric motor 3 for driving the air pump 35
6 is connected to the motor driver 14a, and the driver 14a operates in response to an instruction from the CPU 18 to generate an electric motor 36.
Turn on / off. That is, the pump 35 is driven / stopped. The pressure sensors 33n and 33p generate electric signals corresponding to the internal pressures of the accumulators 32n and 32p, and give them to the signal processing circuits 14d and 14e. The signal processing circuits 14d and 14e convert the electric signal indicating the internal pressure into an analog signal indicating a level change having a linear relationship with the pressure and apply the analog signal to the A / D converter 17 through the input / output port 16. A / D converter 17
Converts these analog signals into digital data, and the CPU 18 reads these digital data.

An operation / display board 22 having a power switch, a key for inputting data, a two-dimensional display, an indicator lamp and a buzzer is connected to the control unit 12, and the CPU 18 of the control unit 12 is connected to the control unit 12. The system controller 1
9, RAM 20 and ROM 21 are connected.

The control operation of the CPU 18 is shown in FIGS. Referring to FIG. 4, when the device is powered on and a predetermined voltage is applied to itself (step 1), the CPU 18
Clears internal registers, counters, timers, etc., outputs standby signals (electromagnetic open / close valve off, motor off) to the output ports (step 2), and then operates / displays the board. The "user set value" column, the "measured value" column, and the "alarm" column of the display screen 22d shown in FIG. 9 are displayed on the two-dimensional display 22 and the "user set value" column is displayed. The information input items (inhalation amount, discharge time) and the numerical values (Qs, Ts) set therein are displayed (step 3). As for the numerical value, the reference value is initially displayed. When there is a numerical value change input, the CPU 18 reads it, and when the input numerical value is within a predetermined range, changes the display to the input value and updates the contents of the register (step 3). If the input numerical value is out of the predetermined range, the display is not changed and the register contents are not updated. When the system setting key of the operation / display board 22 is pressed, the system setting item and the numerical value set therein are displayed by additionally displaying the "system setting value" column of the display screen 22d shown in FIG. Display (step 3). As for the numerical value, the reference value is initially displayed. CPU18
Reads the numerical value change input when it is input, and when the input numerical value is within a predetermined range, changes the display to the input value and updates the contents of the register as well (step 3).
If the input numerical value is out of the predetermined range, the display is not changed and the register contents are not updated. When the system setting key of the operation / display board 22 is pressed while the "system setting value" column is displayed, the display of the "system setting value" column is erased. When there is no input of a numerical value or the like, it waits until the start key is pressed (steps 3, 4, 3).

When the start key is pressed, the CPU 18
Energizes the electric motor 36 to drive the air pump 35 and energize (valve open) the electromagnetic on-off valves 34n and 34p (step 5a). Then, the pressure detected by the pressure sensor 33n is read and waits until it becomes equal to or lower than the system set value Pns (the absolute value of the detected pressure is equal to or higher than the absolute value of Pns) (step 5b).
When the pressure detected by the pressure sensor 33n becomes Pns or less, that is, the pressure of the accumulator 32n becomes Pns or less (at the same time, the pressure of the accumulator 32p rises), CP
U18 executes a "pressure adjustment" process (step 6) and a "display update" process (step 7).

In the "pressure adjusting" process (step 6), the detection pressures of the pressure sensors 33n and 33p are read, and when the detection pressure Pn of the pressure sensor 33n is equal to or lower than Pns, the electromagnetic opening / closing valve 34n is closed (OFF) and Pn is set to Pn. When it exceeds Pns, the solenoid on-off valve 34n is opened (ON), when the detection pressure Pp of the pressure sensor 33p is Pps or more, the solenoid on-off valve 34p is closed (OFF), and when Pp is less than Pps, the solenoid on-off valve 34p is opened ( turn on.

In the "display update" process (step 7), the latest set values, measured values and alarm information, if any, are updated and displayed on the display screen 22d of the display board 22.

Then, the CPU 18 drives the pump as follows.

(1) Control of First Half Cycle (Discharge Stroke) The CPU 18 has the content of the register CHF for indicating whether the stroke to be performed next is the discharge stroke or the suction stroke is "0" (discharge stroke instruction). It is checked (step 8). Immediately before starting the first half cycle, the register CHF
Is "0" in "initialization" (step 2). Since the content of the register CHF is "0", the CPU1
8, the electromagnetic on-off valve 31n is closed (step 9), the electromagnetic on-off valve 31p is opened (step 10), and the discharge time set value Ts is written in the discharge time measurement register PIR (step 11). , Allow interrupt 1 (step 1
2). When the interrupt 1 is permitted, the CPU 18 proceeds to “interrupt 1” (step 50) shown in FIG. 7 every time one clock pulse is generated, and updates the content of the register PIR to a value smaller by one there. As a result, when the interrupt 1 is permitted, the content of the register PIR decreases in inverse proportion to the passage of time. The CPU 18 waits until the content of the register PIR becomes 0 (step 13). While waiting, the input of the operation / display board 22 is monitored (step 16), and if there is an input, the process according to the input is performed (step 17).
If there is a setting value change input here, it is read, and if it is within a predetermined range, the display on the display screen 22d is updated and the register value is also updated. If there is a stop input, stop processing is performed and the process returns to step 3. When there is no stop input and the content of the register PIR becomes 0, the CPU 18 makes an interrupt 1
Is prohibited, and register CHF is set to "1" (inhalation stroke is specified)
And write back to step 6.

(2) Control of Second Half Cycle (Suction Process) Next, the CPU 18 performs the above-mentioned "pressure adjustment" process (step 6).
Then, the "display update" process (step 7) is executed. C
The PU 18 checks whether or not the content of the register CHF for indicating whether the next stroke to be performed is the discharge stroke or the suction stroke is "0" (discharge stroke instruction) (step 8). Here, the content of the register CHF is "1" (inhalation stroke instruction)
Therefore, the CPU 18 opens the electromagnetic opening / closing valve 31n (step 18) and closes the electromagnetic opening / closing valve 31p (step 1).
9), a register Vm for storing the suction flow velocity peak value
a, Clear the register Qma for storing the inhaled amount integrated value and the register Tma for inhaling time measurement (step 2
0 to 22), register the flow velocity sampling period Ct in the register NI
Write to R (step 23) and permit interrupt 2 (step 24).

When the interrupt 2 is enabled, the CPU 18 causes "interrupt 2" shown in FIG. 8 every time one clock pulse is generated.
The process proceeds to (step 60), where the content of the register NIR is updated to a value smaller by 1 (step 61), and the register Tma is updated.
The content of is updated to a value larger by 1 (step 62). As a result, when the interrupt 2 is enabled, the content of the register NIR decreases in inverse proportion to the elapse of time, and the content of the register Tma increases in direct proportion to the elapse of time. The CPU 18 waits until the content of the register NIR becomes 0 (step 2).
5). While waiting, the input of the operation / display board 22 is monitored (step 26), and if there is an input, the process according to the input is performed (step 27). If there is a setting value change input here, it is read, the display on the display screen 22d is updated, and the register value is also updated. If there is a stop input, stop processing is performed and the process returns to step 3.

When there is no stop input and the content of the register NIR becomes 0 (one sampling period Ct elapses), CP
U18 again stores the sampling cycle Ct in the register NIR.
Is written (step 28), the detected flow velocity V of the flow velocity sensor 13 is read (step 29), and the value obtained by adding the measured value V of this time to the content Qma at that time is updated and stored in the integration register Qma (step 30). The CPU 18 then compares the detected flow velocity V with the value of the peak value register Vma (step 3
1) If the former is larger than the latter, the former, that is, the detected flow velocity V
Is updated and stored in the peak value register Vma (32).

Next, the CPU 18 checks whether the value Qma of the integral value register Qma, that is, the inhalation amount has reached the set value Qs (step 33). If not reached, inhalation time Tma
It is checked whether (the value of the register Tma) is abnormally long (step 34), and if it is abnormally long, an "abnormality alarm" (step 35) is executed. In the "abnormality alarm", "absorption abnormality" is displayed in the alarm field of the display screen 22d, and the buzzer of the operation / display board 22 is activated for a predetermined time. When the inhalation time Tma is not an abnormally long time, or when an abnormal time is issued and an "abnormality alarm" is executed, the next sampling 1 cycle Ct
Returns to the check (step 25).

In this manner, the reading of the intake flow velocity V and its integration (integration) are repeated in the Ct cycle, and the integrated value Qma becomes the set value Qs.
When the blood inhalation amount Qma reaches the set value Qs, the interrupt 2 is prohibited (step 36) and the register CH
"0" is updated and written in F (step 37), and the respective values of the registers Vma, Tma and Qma (suction flow rate peak value, suction time and suction amount) are measured value registers Vm, Tm and Qm.
(Steps 38-40).

Then, the suction time Tm of the measurement value register Tm
Is within the setting range Tmi to Tmx (step 41), and if it is within the setting range Tmi to Tmx, the process proceeds to the notification data generation (step 46). Setting range Tmi ~ T
When mx is deviated to the long side, the value of register Pns (negative pressure reference value for pressure control) is decreased by 1 in order to increase the negative pressure (increase its absolute value) and shorten the suction time Tm. However, when the updated value is equal to or lower than the lower limit value Pnmi, the lower limit value Pnmi is written in the register Pns (42 to 45) to avoid application of a strong negative pressure lower than Pnmi. ). And generation of notification data (step 4)
Proceed to 6). When the set range Tmi to Tmx is out of the long side, the value of the register Pns is updated by 1 in order to weaken the negative pressure (lower its absolute value) and lengthen the suction time Tm. When the updated value exceeds the upper limit value Pnmx, the register Pn should be set so that the negative pressure is not weakened below Pnmx.
Write the upper limit value Pnmx to s (47 to 49). Then, the process proceeds to the generation of notification data (step 46). By this negative pressure adjustment, the suction period Tm is automatically adjusted within the set range Tmi to Tmx, provided that the negative pressure does not fall outside the set range.

In the alarm data generation (step 46), the suction pressure Pn, the suction time Tm, and the suction flow velocity peak value Vm are
Setting range Pnmi to Pnmx, Tmi to Tmx and Vmi respectively
It is checked whether or not it is within ~ Vmx, "suitable" when it is within the setting range, "insufficient" when it is outside the setting range to the low side (negative pressure Pn has a small absolute value), and When the set range is out of the high range (the negative pressure Pn has a large absolute value), it is judged as "excessive" and each parameter is determined.
Output data is generated by allocating this judgment data to the data. This output data is "display update" (step 7).
Then, the judgment item 23 in the measurement value column of the display screen 22d (FIG. 9)
Display in 3. Further, the CPU 18 determines whether or not an alarm should be issued from the correlation of the output data assigned to each of the suction pressure Pn, the suction time Tm, and the suction flow velocity peak value Vm in the notification data generation (step 46), When there is a correlation to alarm, alarm data is generated. This alarm data is "display updated" (step 7) and is displayed in the display area 234 of the alarm column of the display screen 22d. For example, when the suction pressure Pn, the suction time Tm and the suction flow velocity peak value Vm are all "appropriate", no alarm data is generated, but they are "excessive", "excessive" and "insufficient", respectively. Sometimes
"Inhalation failure: suction stenosis / regurgitation. Inhalation system blockage / delivery valve check of regurgitation required" is displayed in the alarm column and the operation / display board 22 is displayed.
When the buzzer is activated for a predetermined time and it is "insufficient", "insufficient" or "excessive", "Excessive suction: pump damage / reverse flow. Break / check for suction valve reverse flow" is displayed in the alarm column. The buzzer of the operation / display board 22 is energized for a predetermined time.

When the processing of the notification data generation (step 46) is completed, the CPU 18 returns to the "pressure adjustment" (step 6).

(3) Control after Third Half Cycle The CPU 18 controls the third half cycle in the same manner as the control of the first half cycle described in (1) above, and the fourth half cycle described above.
The control is performed in the same manner as the control of the second half cycle of (2), and similarly, the odd half cycles are controlled in the same manner as the control of the first half cycle of (1) above, and the even half cycles are Above
The control is performed in the same manner as the control in the second half cycle of (2).

When the stop key of the operation / display board 22 is operated, the CPU 18 sends it to step 16 or 26.
Then, the interrupts 1 and 2 are prohibited, the electromagnetic on-off valves 31n and 31p are turned off (valve closed), the motor 36 is stopped, the electromagnetic on-off valves 34n and 34p are turned off, and the register C
HF, PIR, Vma, Qma, Tma and NIR are cleared and the process returns to step 3.

In this embodiment, the discharge pressure Pps is set to be larger than the arterial pressure of the living body with a margin, and the operator determines the discharge time Ts and the discharge amount Ps of the suction stroke at this discharge pressure Pps. Set it to a time long enough to discharge substantially all. As a result, when a set amount of blood is inhaled in the inhalation stroke, the inhalation stroke is automatically switched to the ejection stroke, and the inhalation time Tm automatically becomes a value corresponding to the inhalation volume set value Qs and the blood-sending ability of the living body. .. As long as the suction negative pressure Pn falls within the set range Pnmi to Pnmx, the suction negative pressure is automatically adjusted so that the suction time Tm falls within the set range Tmi to Tmx. The flow rate (aspiration and blood supply amount per unit time) can be adjusted by the set value Qs. In addition, the blood flow rate of the pump 1 becomes a value corresponding to the inhalation amount set value Qs and the blood sending capacity of the living body. Therefore, when the operator sees how much the heart is recovering, the operator is
It is possible to judge the degree of recovery of the heart by changing the Qs little by little using the operation / display board 22 and observing how the blood flow rate of the pump 1 changes accordingly. When the blood supply capacity of the heart is low, when Qs is large, Tm is correspondingly long and when it is small, Tm is short. However, when the blood supply capacity of the heart is high, the change amount of Tm with respect to the change of Qs is small.

During the suction stroke, if a backflow occurs at the fluid outlet 8 due to an abnormal operation of the check valve 11, the flow velocity V detected by the sensor 13 is low and the rising speed of the integrated value Qma is slow. An abnormal alarm is issued, or when the alarm data is generated (step 46), the suction pressure Pn,
The inhalation time Tm and the inhalation flow velocity peak value Vm are judged to be "excessive", "excessive" and "insufficient", respectively, and "inhalation failure: suction stenosis / backflow. Inhalation system blockage / delivery valve backflow check". Is displayed in the alarm column of the display screen 22d, and if a check valve 10 malfunctions and backflow occurs in the fluid receiving port 7,
Since blood reciprocates in the receiving port 7, the flow velocity V detected by the sensor 13 in the suction stroke is high, and the rising speed of the integrated value Qma is high.
In the notification data generation (step 46), the suction pressure Pn, the suction time Tm, and the suction flow velocity peak value Vm are determined to be "insufficient", "insufficient" and "excessive", respectively, and "excessive suction: pump damage". "Reverse flow. Breakage / check of intake valve reverse flow" is displayed in the alarm column. Although the reverse flow abnormality is also detected as described above, the fluid in the discharge stroke due to the operation abnormality of the check valve 10 is read by reading the flow velocity V even in the discharge stroke (the content of the register CHF is "0"). The backflow at the receiving port 7 can be uniquely monitored.

By the way, in the above-mentioned embodiment, the negative pressure and the high pressure air are switched and supplied to the pump 1 by using the two solenoid on-off valves 31n and 31p. Alternatively, the air port 9 of the pump 1 may be alternately connected to the negative pressure accumulator 32n and the positive pressure accumulator 32p. Furthermore, although the embodiment described above is an artificial heart, the pumping device of the present invention is
Not limited to this, a delivery flow rate substantially equivalent to the delivery flow rate is pressurized and delivered without disturbing the delivery flow rate on the fluid supply side, and in addition, the same as the application for adjusting the drive flow rate of the pumping device. Applicable.

[0040]

As described above, according to the pumping device of the present invention, the suction flow rate V is integrated to calculate the suction amount Qm, and when the suction amount Qm reaches the set value Qs, the suction mode is switched to the discharge mode. The variation in the drive flow rate is small, and the setting of the ejection timing is substantially unnecessary. Moreover, the inhalation time Tm automatically becomes a value corresponding to the inhaled amount set value Qs and the blood-sending ability of the living body, and the operator sets the blood-flowing amount of the pump (suction, blood-sending amount per unit time) It can be adjusted by Qs, and the drive flow rate adjustment work becomes simple. In addition, the set value Q
s can be changed to determine the degree of recovery of the heart.
It is possible to easily monitor narrowing and clogging of the suction line, abnormal operation of the check valve, etc.

[Brief description of drawings]

FIG. 1 is a diagram showing an embodiment of the present invention, and is a block diagram showing a pump, positive and negative pressure sources, and electromagnetic on-off valves connected to them.

FIG. 2 is a view showing an embodiment of the present invention, and is a block diagram showing an electric device for controlling the pressure source and the electromagnetic on-off valve shown in FIG.

3A is an enlarged cross-sectional view taken along line 3a-3a of pump 1 shown in FIG. 1, and FIG. 3B is a view 3b-3b of pump 1 shown in FIG.
It is a line expansion sectional view.

4 is a flowchart showing a part of the control operation of the CPU 18 shown in FIG.

5 is a flowchart showing a part of the control operation of the CPU 18 shown in FIG.

6 is a flowchart showing a part of the control operation of the CPU 18 shown in FIG.

7 is a flowchart showing a part of the control operation of the CPU 18 shown in FIG.

8 is a flowchart showing a part of the control operation of the CPU 18 shown in FIG.

9 is a plan view showing a display screen of a two-dimensional display of the operation / display board 22 shown in FIG.

[Explanation of symbols]

1: Pump 2, 3: Enclosure 4: Diaphragm 5: Fluid receiving space 6: Working fluid receiving space 7: Fluid receiving port 8: Fluid sending port 9: Air-
Ports 10 and 11: Check valve 12: Control device 13: Flow rate sensor 14a: Motor driver 14b, 14c, 14f, 14g: Solenoid driver 14d, 14e, 14h: Signal processing circuit 16: Input / output port 17 : A / D converter 18: Microprocessor 19: System controller 20: RAM 21: ROM 22: Operation /
Display board 31n, 31p: Electromagnetic on-off valve 32n, 32p: Accumulator 33n, 33p: Pressure sensor 34n, 34p: Electromagnetic on-off valve 35: Air pump 36: Electric motor 37n, 37p: Overpressure protection valve

Claims (2)

[Claims] 1. A fluid receiving space and a working fluid space are divided,
A pumping member that can reciprocate in the direction of contracting / expanding the fluid receiving space, and is inserted between the fluid receiving port and the fluid receiving space to allow the fluid to flow from the former to the latter and prevent the fluid to flow in the opposite direction. And a second check valve that is interposed between the fluid outlet and the fluid receiving space and that allows the fluid to flow from the latter to the former but prevents the fluid from flowing in the reverse direction. pump;
Flow velocity detecting means for detecting the flow velocity of the fluid entering the fluid receiving space from the fluid receiving port; a low pressure fluid source; a high pressure fluid source; a connection switching for selectively connecting the working fluid space to the low pressure fluid source and the high pressure fluid source. First control means for connecting the working fluid space to the low pressure fluid source by the connection switching means when a time period during which the connection switching means connects the working fluid space to the high pressure fluid source reaches a set time. Integrating means for integrating the flow velocity while the working fluid space is connected to a low-pressure fluid source to generate a signal representing the integrated value; and, when the integrated value reaches a set value, the working fluid space by the connection switching means. Fluid feed pumping device comprising: second control means for connecting the to the high pressure fluid source. 2. A pressure adjusting means for adjusting the pressure of a low-pressure fluid source, and a time during which the working fluid space is connected to the low-pressure fluid source is measured, and when the time is longer than a set range, the time is shortened. 3. The fluid feed pumping device according to claim 1, further comprising third control means for controlling the pressure of the low-pressure fluid source via the pressure adjusting means in a direction that lengthens the time when the pressure is shorter than a set range.