JPH07163663A - Simulated respirator for artificial respiratory apparatus - Google Patents

Abstract

PURPOSE:To reproduce correct simulated respiration only by inputting various types of actual respiration (normal respiration, breathing, sigh, and cough) by a human being. CONSTITUTION:A device is provided with bellows 22 for sucking/discharging air quantity as simulated respiration, a crank mechanism 23 and a bellows expansion/contraction motor 24 for actuating the bellows 22 to expand/contract, a respiration pattern inputting tube 26 for inputting actual respiration such as normal respiration, breathing, sigh, and cough, a flow gauge 27 for converting the inputted respiration into flow rate waveform signals, and a computation control part 35 for calculating a simulated respiration pattern corresponding to the inputted respiration by time integration of respiration waveform signals, calculating a desired angle of the bellows expansion/contraction motor 24 to suck/discharge the air quantity corresponding to the simulate respiration pattern, and controlling the bellows expansion/contraction motor 24 in such a way that its actual rotation angle coincides with the desired rotation angle.

Description

Detailed Description of the Invention

[0001]

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to a simulated breathing apparatus for a ventilator, and more particularly, it requires a human to input various actual breaths (normal breath, deep breath, sigh, cough, etc.) for accurate simulated breathing. The present invention relates to a simulated breathing apparatus for a ventilator suitable for reproduction.

[0002]

2. Description of the Related Art Conventionally, as described in, for example, Japanese Patent Application No. 5-121999 filed by the present applicant, respiratory vibration (pressurization / negative pressure) generated by a respiratory vibration generator is alternately applied to a vibration circuit. The artificial respirator has been developed to force the patient's lungs to breathe at a breathing rate according to the frequency of the vibration circuit.
The ventilator cannot breathe spontaneously (apnea)
When inhaling the patient, the oxygen supplied from the oxygen source is sent to the lungs of the patient based on the respiratory oscillation, and when exhaling, the air discharged from the lungs of the patient is released to the atmosphere based on the respiratory oscillation. I am sending it out. On the other hand, in order to avoid burdening the lungs of a patient who is normally apnea and occasionally spontaneously breathes, the opening pressure of the spontaneous breathing valve equipped in the expiratory circuit of the ventilator is set to the outlet pressure of the endotracheal tube. It is controlled to be constant.

[0003]

By the way, in the above-described ventilator, in particular, in order to prevent the burden on the lungs even for a patient who normally breathes spontaneously and sometimes spontaneously, the ventilator does not work. It is necessary to control the opening of the spontaneous-breathing valve to an optimum opening so that the outlet pressure of the endotracheal tube of the human being becomes constant. For that purpose, various human breathing patterns (normal breathing, deep breathing, coughing, etc.) are required. ), It is necessary to determine the control amount of the opening degree of the spontaneous breathing valve. Therefore, in the past, for example, by periodically oscillating a waveform (as an example, a sine wave or the like) like human breathing, and connecting a device that generates the waveform to an endotracheal tube of a ventilator,
An experiment was also conducted to control the spontaneous breathing valve opening so that the endotracheal tube outlet pressure was constant, but since the breathing pattern is different and complicated for each human,
There is a problem that it is difficult to reproduce various breathing patterns of an actual human with the device that generates the cyclically varying waveform as described above.

[0004]

The object of the present invention is to improve the disadvantages of the above-mentioned conventional examples, and in particular, it is possible for humans to input various actual breaths (normal breath, deep breath, sigh, cough, etc.) It is an object of the present invention to provide a simulated breathing apparatus for an artificial respirator, which is capable of accurately reproducing simulated breathing having the same waveform.

[0005]

According to a first aspect of the present invention, there is provided a duct that is detachably connected to a breathing system of an artificial respirator, and a predetermined air amount for simulated breathing is provided by expanding and contracting. In a simulated breathing apparatus for a ventilator, which includes a bellows which is inhaled or discharged through a pipe, a bellows expansion / contraction mechanism for expanding / contracting the bellows, and a control means for controlling the operation of the bellows expansion / contraction mechanism, a normal breath and a deep breath , Respiratory input means for inputting various actual respiratory information such as sigh and cough, and respiratory / waveform conversion for converting the actual respiratory information input via the respiratory input means into an electrical respiratory waveform signal Means, and the control means forms a simulated breathing pattern having the same waveform as the waveform of the input breath based on the respiratory waveform signal output from the respiratory / waveform conversion means. A forming function, a target operation amount calculating function for calculating a target operation amount of the bellows expansion / contraction mechanism so that an air amount corresponding to the formed simulated breathing pattern is inhaled / discharged from the conduit of the bellows, and the bellows A configuration is provided in which a motion amount coincidence control function for controlling the operation of the bellows expansion / contraction mechanism is provided so that the actual operation amount of the expansion / contraction mechanism matches the target operation amount. This aims to achieve the above-mentioned object.

According to the present invention of claim 2, the control means further comprises a storage control function of storing data relating to a target operation amount of the bellows expansion / contraction mechanism in a predetermined storage means.
Is adopted.

According to a third aspect of the present invention, the bellows expansion / contraction mechanism is configured as a crank mechanism for expanding / contracting the bellows and a motor for operating the crank mechanism.
The target operation amount calculation function of the arithmetic control unit is executed by calculating a target rotation angle of the motor such that an air amount corresponding to the simulated breathing pattern is inhaled / exhausted from the conduit of the bellows, The operation amount matching control function of the arithmetic control unit is executed by controlling the operation of the motor so that the actual rotation angle of the motor matches the target rotation angle.

According to the present invention of claim 4, the breathing / waveform converting means is configured as a flow meter.

[0009]

According to the present invention of claim 1, various actual respiratory information such as normal breathing, deep breathing, sighing and coughing inputted through the breathing input means is converted into a respiratory waveform signal, and based on the respiratory waveform signal. A simulated breathing pattern having the same waveform as the input respiratory waveform is formed, and the target operation amount of the bellows expansion / contraction mechanism is calculated so that the air volume corresponding to the simulated breathing pattern is inhaled / exhausted from the bellows conduit, and the bellows expansion / contraction is calculated. In order to control the operation of the bellows expansion and contraction mechanism so that the actual movement amount of the mechanism matches the target movement amount, simulated breaths having the same waveform as various actual breaths input via the breathing input means are provided in the bellows conduit. Can be output from. Accordingly, by connecting the conduit of the bellows of the simulated breathing apparatus and the breathing system of the ventilator, the ventilator can be tested under the same conditions as the actual spontaneous breathing of the patient.

According to the present invention of claim 2, the control means comprises:
Further, since it has a function of storing data relating to the target operation amount of the bellows expansion / contraction mechanism in a predetermined storage means, it is possible to reproduce the same simulated breathing any number of times.

According to the third aspect of the present invention, the bellows expansion / contraction mechanism is configured as a crank mechanism for expanding / contracting the bellows and a motor for operating the crank mechanism, and an air amount corresponding to the simulated breathing pattern is sucked from the conduit of the bellows. / The target rotation angle of the motor is calculated so that it is discharged, and the operation of the motor is controlled so that the actual rotation angle of the motor matches the target rotation angle. Therefore, simulated breathing with complicated and delicate waveforms is also reproduced. It becomes possible.

According to the present invention of claim 4, since the respiration / waveform conversion means is configured as a flow meter, normal respiration, deep respiration, sigh, cough, etc. input via the respiration input means are converted into a flow rate waveform. As a result, a simulated breathing pattern corresponding to the flow rate waveform can be easily formed, and as a result, the same waveform as various actual breaths such as normal breath, deep breath, sigh, and cough input via the breath input means can be obtained. It is possible to accurately reproduce the simulated breathing that it has.

[0013]

Embodiments of the present invention will be described below with reference to the drawings.

First, before describing the simulated breathing apparatus of this embodiment, the structure of the artificial respirator will be described with reference to FIG. 2. The artificial respirator 1 includes a blower 2 as a pressure source,
The vibration generator 3, the infection blocking device 4, the vibration circuit 5,
An inhalation circuit 7 connected to an oxygen source 6, an expiratory circuit 10 equipped with an atmosphere opening 8 and a spontaneous breathing valve 9, a common circuit 11, and a tracheal tube 13 equipped with a pressure sensor 12.
And a control unit 14 that controls each unit, a display unit 15, and the like.

The blower 2 is driven by a blower motor 16 to generate a pressurizing force at the discharge port 1A and the suction port 1B.
It is designed to generate negative pressure. Vibration generator 3
Is operated by a known rotary valve 3A driven by a rotary valve motor 17 to generate a pressurizing pressure and a negative pressure.
Are given alternately. The infection blocking device 4
The diaphragm 4A is constituted by a known mechanism that is inserted in the middle of the vibration circuit 5 and equipped with the diaphragm 4A, and the diaphragm 4A can be swung following the pulsation generated by the vibration generator 3.

The vibrating circuit 5 includes an inspiratory circuit 7 and an expiratory circuit 1.
0, communicating with common circuit 11 and tracheal tube 13
The patient's lungs are forcibly breathed at a breathing rate corresponding to the frequency of the vibrating circuit 5.
The intake circuit 7 is supplied with oxygen from the oxygen source 6. The expiratory circuit 10 is designed to discharge the air discharged from the lungs of the patient to the atmosphere via the spontaneous breathing valve 9.

The spontaneous-breathing valve 9 is provided in the vicinity of the atmosphere opening port 8 of the expiratory circuit 10 so as to be freely opened and closed.
The outlet pressure of the tracheal tube 13 is kept constant based on the opening / closing control by the. The pressure sensor 12 is installed near the outlet of the tracheal tube 13, and detects the outlet pressure of the tracheal tube 13 and outputs it to the control unit 14.

The control unit 14 controls the drive of the blower motor 16 to control the rotation of the blower 2, and the rotary valve motor 1
The rotary valve 3A of the vibration generator 3 is rotationally controlled by driving and controlling the rotary actuator 7. Further, the control unit 14 controls the movement of the diaphragm 4A of the infection blocking device 4 and controls the opening degree of the spontaneous breathing valve 9 so that the outlet pressure of the tracheal tube 13 becomes constant based on the detection signal of the pressure sensor 12. It is supposed to do. The display unit 15 is adapted to display data relating to the outlet pressure of the tracheal tube 13, data relating to the optimum opening degree of the spontaneous breathing valve 9, and the like based on a command from the control unit 14.

In the ventilator 1, when a patient who cannot breathe spontaneously (apnea) is inhaled, the oxygen supplied from the oxygen source is used by the vibration generator 2 to generate the patient's breathing vibration. When the patient is inhaled to the lungs and cannot exhale spontaneously (apnea), the air discharged from the lungs of the patient is sent to the atmosphere based on the respiratory vibration generated by the respiratory vibration generator 2. Has become.

Next, the structure of the simulated breathing apparatus of this embodiment will be described with reference to FIG. 1. In the simulated breathing apparatus 20, a bellows 22 equipped with a ventilator connecting tube 21 and a crank mechanism for expanding and contracting the bellows 22. 23, a bellows expansion / contraction motor 24 for driving the crank mechanism 23 to expand / contract the bellows 22, a top dead center detector 38, a motor driver 25, and a flow meter 27 equipped with a breathing pattern input tube 26. , A D / A converter 28, a port unit 29, an A / D converter 30, a counter 31,
It is configured to include a computer 32, an external memory 33, and a monitor 34.

The flow meter 27 measures various actual breaths (for example, normal breath, deep breath, sigh, cough, etc.) inputted through the breathing pattern input tube 26 by the operator (or patient) of the simulated breathing apparatus. However, analog flow rate waveform signals (respiration waveform signals) corresponding to various input breaths are supplied to the A / D converter 30. The A / D converter 30 performs analog / digital conversion of the flow rate waveform signal and supplies it to the arithmetic control unit 35 of the computer 32.

The computer 32 is composed of, for example, a personal computer, and performs an operation described later and controls each part of the simulated breathing apparatus, an operation control part 35 for storing predetermined data, and an operation part including a keyboard. It is equipped with 37 etc. The arithmetic control unit 35
The flow rate waveform signal supplied from the / D converter 30 is integrated over time to calculate the intake air amount and the exhalation air amount for each cycle of the input breath, and at the same time, expand and contract the bellows based on the inhalation air amount and the exhalation air amount. The rotation angle (maximum angle, minimum angle, start angle) of the motor 24 is calculated.

Further, the arithmetic control unit 35 calculates a target angle for each cycle when the bellows expansion / contraction motor 24 is controlled (described later) and stores it in the external memory 33 as a file of the target angle of one breathing pattern, and the bellows is stored. A digital motor rotation command signal is supplied to the D / A converter 28 so that the rotation angle of the expansion / contraction motor 24 matches the target angle. In this case, control 1 in the external memory 33
Since the target angle for each cycle is stored, various simulated respiratory waveforms with the same waveform can be reproduced any number of times. Further, the arithmetic control unit 35 causes the monitor 34 to display the comparison result and control information between the target flow rate and the actual flow rate, and
The rotation angle is calculated for each control cycle of the bellows expansion / contraction motor 24.

The D / A converter 28 converts the motor rotation command signal into a digital / analog signal, and the motor driver 25.
To be supplied to. The motor driver 25
Bellows expansion / contraction motor 24 based on the motor rotation command signal
Is rotated by a predetermined angle. Further, the motor driver 25 supplies the motor control information to the arithmetic control unit 35 of the computer 1 via the port unit 29, and
An encoder signal corresponding to the rotation of the motor is supplied to the arithmetic control unit 35 of the computer 32 via the counter 31.

The bellows expansion / contraction motor 24 expands / contracts the bellows 22 via a crank mechanism 23 described later. Further, on the outer peripheral surface of the bellows expansion / contraction motor 24, the detected piece 24 is arranged so as to face the top dead center detector 38 when the crank mechanism 23 reaches the top dead center (when the motor rotation angle is 0 degree). Is attached. Top dead center detector 38
Is composed of, for example, a photoelectric switch, and when a detected piece 24 of the bellows expansion / contraction motor 24 is detected, that is, when the crank mechanism 23 reaches the top dead center, a detection signal is transmitted via the port section 29 to the computer 1. Is supplied to the arithmetic and control unit 35.

The structure of the bellows 22, the crank mechanism 23, and the bellows expansion / contraction motor 24 described above will now be described with reference to FIGS. 3 and 4. The bellows 22 is a top plate 22A.
And a bottom plate 22B and a bellows member 22C mounted between the top plate 22A and the bottom plate 22B. Inside the bellows 22, the tracheal tube 13 of the ventilator 1 is provided.
The ventilator tube 21 is detachably connected to the ventilator tube 21. When the bellows 22 expands and contracts, a simulated breathing waveform corresponding to the expansion and contraction is supplied to the ventilator 1 via the ventilator tube 21 and the tracheal tube 13.

The bottom plate 22B of the bellows 22 is fixed to the top plate 40A of the base 40 via a plurality of bolts 39A, 39B, 39C ... And the base end of the bellows expansion / contraction motor 24 is Plural bolts 41A, 41B ...
It is fixed to the side plate 40B of the base 40 via. In the figure, reference numeral 40C is a bottom plate of the base 40, reference numerals 40D and 40E are support members for supporting the top plate 40A on the side plate 40B, and reference numeral 40.
Reference characters F and 40G denote support members that support the side plate 40B on the bottom plate 40C.

The bellows expansion / contraction motor 24 is configured as a direct drive motor (DD motor), and has a rotatable cylindrical outer ring portion 24A and a core 24B fixedly mounted in a hollow portion inside the outer ring portion 24A. When the bellows expansion / contraction motor 24 is driven, the outer ring portion 24A rotates around the core 24B. A disk-shaped flange 43 is fixed to the end surface of the outer ring portion 24A of the bellows expansion / contraction motor 24 on the side facing the crank mechanism 23 via a plurality of bolts 42A, 42B, ....

Further, the top plate 22A of the bellows 22, the bellows member 22C, the bottom plate 22B, and the top plate 40A of the base 40 are equipped with an operating shaft 44 penetrating through the central portions of these members. The operating shaft 44 protruding upward from the top plate 22A of the
Is fixed through. The operating shaft 44 protruding downward from the bottom plate 22B of the bellows 22 is provided on the top plate 40A of the base 40.
The mounting member 45 and the plurality of bolts 45 in the hole 40A 'of
It is fitted to the bush 46 fixed via A, 45B, 45C and 45D.

The male screw portion 44B formed on the lower end portion of the operating shaft 44 is screwed into the female screw portion 47B formed on the upper inner portion of the first link 47. In the spherical hollow portion formed in the inner lower portion of the first link 47, the ball 4
7A is rotatably inserted through grease, and the upper end surface of the connecting shaft 49 is fixed and caulked to the lower surface of the spherical surface of the ball 47A. The male screw portion 49A formed on the lower portion of the connecting shaft 49 is screwed to the female screw portion 48B formed on the inner upper portion of the second link 48 via a lock nut 50.

A ball 48A is rotatably inserted through grease into a spherical hollow portion formed in an inner lower portion of the second link 48, and a mounting shaft is attached to a spherical side surface portion of the ball 48A. The tip surface of 51 is fixed and crimped. The male screw portion 51A formed at the base end portion of the mounting shaft 51 is screwed to a female screw portion 43A formed at a position eccentric from the center of the flange 43 via a nut 43B. The connecting shaft 49 and the second link 48 of the first link 47 are integrally swingable in a left-right direction in FIG. 3 at a predetermined angle (for example, 20 to 30 degrees) about the ball 47A as a fulcrum.

The operation shaft 44, the first link 47, the second link 48 and the like described above constitute the crank mechanism 23. 3, reference numeral P1 is the top dead center of the crank mechanism 23, reference numeral P2 is the bottom dead center of the crank mechanism 23, reference numeral P3 is the midpoint between the top dead center and the bottom dead center, and the circle indicated by reference character K is the crank mechanism 23. The locus | trajectory of the center of the ball 48A of the 2nd link 48 which comprises is shown.

When the bellows expansion / contraction motor 24 is driven by the motor driver 25, the bellows expansion / contraction motor 2 is driven.
Since the flange 43 fixed to the outer ring portion 24A rotates with the rotation of the outer ring portion 24A of No. 4, the second link 48 rotates around the center of the ball 48A and draws the locus K. As a result, the actuating shaft 44 moves in the vertical direction, so that the bellows member 22C of the bellows 22 expands and contracts.

When the crank mechanism 23 reaches the top dead center with the predetermined rotation of the bellows expansion / contraction motor 24, the bellows 2
When the bellows member 22C of No. 2 fully extends upward and the crank mechanism 23 reaches the bottom dead center with the predetermined rotation of the bellows expansion / contraction motor 24, the bellows member 22C of the bellows 22 contracts most downward.

The method of calculating the target angle of the bellows expansion / contraction motor 24 will now be described. Various actual breaths (eg, normal breath, deep breath, sigh, etc.) input via the breathing pattern input tube 26 and the flow meter 27. When a cough) is reproduced by expanding and contracting the bellows 22 as a simulated respiratory waveform, the flow rate within one cycle of control of the bellows expanding and contracting motor 24 corresponds to “bellows displacement × 1 cycle time”. The flow rate of the pattern is converted into a target bellows displacement for each control cycle.

Next, the target bellows displacement of the bellows 22 is X, the bellows speed is V, the angular velocity of the bellows expansion / contraction motor 24 is ω, the crank long arm of the crank mechanism 23 is L, the crank short arm is R, and the crank angle is θ. Then (see FIG. 5), X = R (1-cos θ + ρ / 4 (1-cos 2θ) ... (1) V = Rω (sin θ + ρ / 2 · sin 2θ) ... (2) The relational expression holds, The arithmetic control unit 35 of the computer 32 sequentially substitutes the angle in the range of 0 to 180 degrees into the crank angle θ in a predetermined step, and the bellows is the angle closest to the target bellows displacement X. The target angle in the control cycle of the expansion / contraction motor 24 is determined.

6 to 9 show the computer 3
It is explanatory drawing when calculating the rotation angle of the bellows expansion-contraction motor 24 based on the flow volume of suction | inhalation / flow volume of exhalation for every cycle of input breathing by the calculation control part 35 of 2. FIG. 6 is a diagram showing the start point / end point of the bellows expansion / contraction motor 24, the difference between suction and discharge, and the like when the flow of the suction operation is earlier than that of the discharge operation and the flow rate during the discharge operation is large. It is a figure which shows the start point, the end point of the bellows expansion-contraction motor 24, the difference of suction and discharge, etc., when operation | movement precedes discharge operation | movement and the flow volume at the time of suction operation is large. In FIGS. 6 and 7, since the sucking operation precedes the exhaling operation, the start point and the end point are located far from the top dead center.

FIG. 8 is a diagram showing the start point / end point of the bellows expansion / contraction motor 24, the difference between suction and discharge, etc. when the discharge operation precedes the suction operation and the flow rate during the discharge operation is large. FIG. 9 shows a case in which the discharge operation precedes the suction operation and the flow rate during the suction operation is large,
It is a figure which shows the start point, the end point, the difference of suction and discharge, etc. of the bellows expansion-contraction motor 24. In FIG. 8 and FIG. 9, since the spitting action precedes the sucking action, the start point and end point are close to the top dead center.

FIG. 10 shows a bellows expansion / contraction motor 24.
Is a diagram of the target angle with respect to the time for each control cycle, the target angle decreases from the start point angle to the offset angle in the sucking motion, and the target angle changes from the offset angle to the end point in the discharging motion. It shows a state of rising to. And the computer 32
The arithmetic control unit 35 stores the angles θ1, θ2, θ3 ... At the times T1, T2, T3 ... As a file in the external memory 33.

That is, in this embodiment, the bellows expansion / contraction motor 24 is intermittently driven between the start point and the end point shown in FIGS.
Actual breathing input by the human through the breathing pattern input tube 26 (eg, normal breathing, deep breathing, sighing, coughing, etc.)
Simulated breathing having the same waveform as is output from the ventilator-connecting tube 21 of the bellows 22.

Next, the operation of this embodiment constructed as described above will be described with reference to FIGS. 11 and 12.

The arithmetic control unit 35 of the computer 32 of the simulated breathing apparatus 20 performs initialization such as deleting the display contents of the monitor 34 based on a predetermined operation of the operating unit 37 by the operator of the simulated breathing apparatus 20 (step S1). ), The constants used in the calculation of this process are calculated (step S
2). When the operator of the simulated breathing apparatus 20 gives an instruction to newly create a reproduced waveform of the breathing pattern from the operation unit 37 (Yes in step S3), the processing from step S4 is executed and the breathing pattern from the operation unit 37 is executed. When there is no instruction to newly create the reproduced waveform of (No in step S3), the processing of step S14 and thereafter is executed.

When the operator of the simulated breathing apparatus 20 gives an instruction to newly create a reproduced waveform of the breathing pattern from the operation unit 37 (Yes in step S3), the file name for saving the reproduced waveform is input from the operation unit 37. After input (step S
4) Input various breathing patterns (for example, normal breathing, deep breathing, sighing, coughing, etc.) from the breathing pattern input tube 26 (step S5).

The flow meter 27 measures various breathing patterns (for example, normal breathing, deep breathing, sighing, coughing, etc.) blown through the breathing pattern input tube 26, and flow rate waveform data corresponding to the various breathing patterns. (Breathing data)
Supply to the / D converter 30. As a result, the arithmetic control unit 35 of the computer 32 takes in the flow rate waveform data (respiration data) that has been analog / digital converted by the A / D converter 30 (step S6), and displays the waveform on the monitor 34 (step S7).

When the operator of the simulated breathing apparatus 20 re-inputs the reproduced waveform of the breathing pattern from the operation unit 37 (Yes in step S8), the operations of steps S5 and S6 are performed again while the reproduced waveform of the breathing pattern is reproduced. When not re-inputting (No in step S8), the operation unit 37 instructs not to re-input.

Along with this, the arithmetic control unit 35 of the computer 32 calculates the target bellows speed for each control cycle of the bellows expansion / contraction motor 24 (step S9), and the total flow rate at the time of suction of the bellows 22 and at the time of discharge thereof. After calculating the total flow rate (step S10), it is determined whether the total flow rate is equal to or larger than the capacity of the bellows 22 (step S1).
1).

The operation control unit 35 determines that the total flow rate is the bellows 22.
If the total flow rate is less than the capacity of the bellows 22 when the capacity is greater than or equal to the capacity of the bellows 22, the maximum angle, the minimum angle of the bellows expansion / contraction motor 24 during the simulated breathing operation,
The start angle is calculated (step S12), and the target angle for each control cycle of the bellows expansion / contraction motor 24 is calculated (step S13).

When the data relating to the target angle for each control cycle of the bellows expansion / contraction motor 24 is stored as a file in the external memory 33 (Yes in step S18), the arithmetic control unit 35 is operated by the operator of the simulated breathing apparatus 20. Step S
When a file is created with the file name input in step 4 (step S19) and the respiratory data is displayed on the monitor 34 (step S20), the data relating to the target angle for each control cycle is not saved as a file in the external memory 33. (No in step S18), the arithmetic control unit 35 directly performs the process of step S20.

On the other hand, when the operator of the simulated breathing apparatus 20 does not give an instruction to newly create a reproduced waveform of the breathing pattern from the operation unit 37 (No at step S3), the arithmetic and control unit 35 reads from the external memory 33. A file to be read is selected (step S14), and when there is no file (No at step S15), the present process is terminated, while when there is a file (affirmation at step S15), the file selected from the external memory 33 is deleted. Read the data (step S1
6) The data is displayed as a graph on the monitor 34 (step S17). After this, the process proceeds to step S20.

After displaying the breathing data on the monitor 34, the arithmetic control unit 35 initializes the motor driver 25 via the port unit 29 (step S21), and the top dead center detector 38 causes the bellows expansion motor 24 to move. Until the detected piece 24 attached to the outer peripheral surface of the motor driver 25
The bellows expansion / contraction motor 24 is rotated by a predetermined amount via (step S22).

Next, the arithmetic control unit 35 rotates the bellows expansion / contraction motor 24 to the start angle via the motor driver 25 (step S23), and the current angle of the bellows expansion / contraction motor 24 is counted from the motor driver 25 to the counter 31. (Step S24), the deviation between the target angle of the bellows expansion / contraction motor 24 and the current angle is calculated (step S25).

Further, the arithmetic control unit 35 converts the deviation between the target angle of the bellows expansion / contraction motor 24 and the current angle into a rotation command value to be supplied to the D / A converter 28 (step S26), and the bellows expansion / contraction motor. The rotation command value is output to the D / A converter 28 so that the angle of 24 matches the target angle (step S27). As a result, the D / A converter 28 supplies the digital / analog converted rotation command to the motor driver 25.
5 rotates the bellows expansion / contraction motor 24 to a target angle.

If the target angle data of the bellows expansion / contraction motor 24 corresponding to the breathing pattern still exists (Yes in step S28), the calculation control section 35 starts from step S22.
While the process of step S28 is repeated, if there is no target angle data (No at step S28), it is determined whether the same breathing pattern is to be executed again (step S2).
9).

When the same breathing pattern is executed again, the arithmetic control unit 35 executes the processing of steps S22 to S28, while when the same breathing pattern is not executed again, from the target angle of the bellows expansion / contraction motor 24. The calculated respiration rate and the respiration rate calculated from the actually rotated angle are displayed as a graph on the monitor 34 (step S3).
0). The above is the flow of control in the present embodiment.

After that, the outlet pressure of the tracheal tube 13 of the artificial respirator 1 is made constant by using various simulated breathing waveforms (normal breath, deep breath, sigh, cough, etc.) reproduced by the simulated breathing apparatus 20. When determining the control amount of the opening degree of the spontaneous breathing valve 9, the ventilator tube 21 of the bellows 22 of the simulated breathing apparatus 20 is connected to the tracheal tube 13 of the ventilator 1, and the simulated respiratory waveform is artificially breathed. Output to container 1.

As a result, the controller 14 of the ventilator 1
Controls the opening of the spontaneous breathing valve 9 to an optimum opening so that the outlet pressure of the tracheal tube 13 becomes constant based on the detection signal of the pressure sensor 12. Display unit 15
Displays data relating to the outlet pressure of the tracheal tube 13, data relating to the optimum opening degree of the spontaneous breathing valve 9, etc., based on a command from the control unit 14.

As described above, according to this embodiment, when various breaths (normal breath, deep breath, sigh, cough, etc.) are inputted from the breathing pattern input tube 26 of the simulated breathing apparatus 20, the computer 32 makes an input. Since the bellows expansion / contraction motor 24 is drive-controlled based on the flow rate of the respiratory waveform to expand / contract the bellows 22, the artificial breathing tube 21 of the bellows 22 outputs (reproduces) a simulated respiration having the same waveform as the input respiration. You can

As described above, the spontaneous breathing valve 9 is arranged so that the outlet pressure of the endotracheal tube 13 of the ventilator 1 becomes constant.
It becomes possible to perform the test of the ventilator 1 under the same conditions as the actual spontaneous breathing of the patient, such as controlling the opening degree of the patient to be in an optimum state. Furthermore, bellows 2
Continuous breathing is also possible according to the number of expansions and contractions of 2.

Further, according to the present embodiment, the target angle for each cycle when the bellows expansion / contraction motor 24 is controlled is calculated and stored in the external memory 33 as a file of the target angle of one breathing pattern. Various simulated breaths having the same waveform can be reproduced from the ventilator-connecting tube 21 of the bellows 22 any number of times.

Further, according to this embodiment, the bellows 2 is controlled by controlling the rotation angle of the bellows expansion / contraction motor 24.
Since the amount of inhaled / exhaled air in 2 is changed, it is possible to reproduce complicated and delicate simulated breathing.

Furthermore, according to this embodiment, simulated breathing can be reproduced without using a high-pressure air generator for generating high-pressure air, a negative pressure source, a compressor, etc.
It is possible to reduce the size and cost of the simulated breathing apparatus.

In this case, in this embodiment, the actual breathing of the human (normal breath, deep breath, sigh, cough, etc.) inputted from the breathing pattern input tube 26 is converted into a flow rate waveform by the flow meter 27, and the flow rate waveform is concerned. Although the simulated breath is formed based on the above, the present invention is not limited to this, and the input actual human breath is converted into a pressure waveform by, for example, a pressure gauge, and the simulated breath is formed based on the pressure waveform. It is also possible to

[0063]

As described above, according to the artificial respirator simulated breathing apparatus of the present invention of claim 1, various actual breaths such as normal breath, deep breath, sigh and cough inputted through the breath input means are realized. Respiratory information is converted into a respiratory waveform signal, a simulated respiratory pattern having the same waveform as the input respiratory waveform is formed based on the respiratory waveform signal, and the air volume corresponding to the simulated respiratory pattern is inhaled / exhausted from the bellows conduit. In order to calculate the target operation amount of the bellows expansion and contraction mechanism as described above and control the operation of the bellows expansion and contraction mechanism so that the actual operation amount of the bellows expansion and contraction mechanism matches the target operation amount, various types of inputs input via the breath input means are performed. Simulated breathing having the same waveform as actual breathing can be output from the bellows conduit. This allows
By connecting the conduit of the bellows of the simulated breathing apparatus and the breathing system of the ventilator, the ventilator can be tested under the same conditions as the actual spontaneous breathing of the patient.

According to the artificial respirator simulated breathing apparatus of the present invention of claim 2, the control means further has a function of storing data relating to the target operation amount of the bellows expansion-contraction mechanism in a predetermined storage means. The effect that the same simulated breath can be reproduced any number of times is achieved.

According to the artificial respirator simulated breathing apparatus of the third aspect of the present invention, the bellows expansion / contraction mechanism is configured as a crank mechanism for expanding / contracting the bellows and a motor for operating the crank mechanism, and the air volume corresponding to the simulated breathing pattern. The target rotation angle of the motor is calculated so that the air is sucked in / discharged from the pipe of the bellows, and the operation of the motor is controlled so that the actual rotation angle of the motor matches the target rotation angle.
It is possible to reproduce simulated breathing having a complicated and delicate waveform.

According to the artificial respirator simulated breathing apparatus of the fourth aspect of the present invention, since the respiration / waveform conversion means is configured as a flow meter, the normal respiration, the deep respiration, the sigh, and the respiration which are input via the respiration input means. A cough or the like can be converted into a flow rate waveform to easily form a simulated breathing pattern corresponding to the flow rate waveform. As a result, similar to the above, normal breathing, deep breathing, sighing, and breathing input via the breathing input means can be performed. It is possible to accurately reproduce simulated breathing having the same waveform as various actual breaths such as cough.

[Brief description of drawings]

FIG. 1 is a block diagram showing a configuration of a simulated breathing apparatus according to an embodiment of the present invention.

FIG. 2 is a block diagram showing the configuration of an artificial respirator to which the simulated breathing apparatus of this embodiment is connected.

FIG. 3 is a front view of the bellows / crank mechanism / bellows expansion / contraction motor and the like according to the present embodiment with some parts omitted.

FIG. 4 is a right side view showing a configuration of the bellows / crank mechanism / bellows expansion / contraction motor shown in FIG. 3 with some parts omitted.

FIG. 5 is an explanatory diagram for calculating a relational expression of a bellows expansion / contraction motor angular velocity / crank angle / bellows displacement / bellows velocity in the present embodiment.

FIG. 6 (a) is an explanatory diagram showing each flow rate in the case where the sucking operation precedes the discharging operation, and FIG. 6 (b) shows the start point / end point / difference between sucking and discharging of the bellows expansion / contraction motor. It is explanatory drawing which shows etc.

FIG. 7 (a) is an explanatory view showing each flow rate in the case where the sucking operation is ahead of the discharging operation, and FIG. 7 (b) is the difference between the start point / end point / the difference between the sucking and discharging of the bellows expansion / contraction motor. It is explanatory drawing which shows etc.

FIG. 8 (a) is an explanatory diagram showing each flow rate in the case where the discharge operation is ahead of the suction operation, and FIG. 8 (b) is the start point / end point / difference between suction and discharge of the bellows expansion / contraction motor. FIG.

FIG. 9 (a) is an explanatory diagram showing a flow rate in the case where the discharge operation is earlier than the suction operation, and FIG. 9 (b) is the start point / end point of the bellows expansion / contraction motor, the difference between the suction and the discharge, and the like. FIG.

FIG. 10 (a) is an explanatory view showing a target angle of the bellows expansion / contraction motor in the sucking operation and the discharging operation, FIG.
0 (b) is an enlarged view of a part of FIG. 10 (a).

FIG. 11 is a flowchart of the first half part of the control operation in this embodiment.

FIG. 12 is a flowchart of the latter half of the control operation in this embodiment.

[Explanation of symbols]

1 Ventilator 13 Tracheal tube as a respiratory system 20 Simulated breathing apparatus 21 Ventilator connection tube as a conduit 22 Bellows 23 Crank mechanism as a bellows expansion mechanism 24 Bellows expansion motor as a bellows expansion mechanism 26 Breathing input Respiratory pattern input tube as means 27 Respiratory / waveform conversion means as flow meter 32 Computer 33 External memory as storage means 35 Arithmetic control unit as control means

Claims (4)

[Claims] 1. A bellows, which has a duct removably connected to a breathing system of an artificial respirator, and inhales or discharges a predetermined amount of air as simulated breathing through the duct by expansion and contraction operation. In a simulated breathing apparatus for a ventilator, which includes a bellows expansion / contraction mechanism for expanding / contracting the bellows and a control means for controlling the operation of the bellows expansion / contraction mechanism, various actual respiratory information such as normal breathing, deep breathing, sighing and coughing. Breathing input means for inputting, and breathing / waveform transforming means for transforming the actual breathing information input via the breathing input means into an electrical breathing waveform signal, wherein the control means controls the breathing / A simulated breathing pattern forming function for forming a simulated breathing pattern having the same waveform as the waveform of the input breath based on the respiratory waveform signal output from the waveform converting means, and the calculated simulated call A target operation amount calculation function for calculating a target operation amount of the bellows expansion / contraction mechanism so that an air amount corresponding to the pattern is sucked / discharged from the conduit of the bellows, and an actual operation amount of the bellows expansion / contraction mechanism is A simulated breathing apparatus for a respirator, comprising: a motion amount matching control function of controlling a motion of the bellows expansion / contraction mechanism so as to match a target motion amount. 2. The artificial respiration according to claim 1, wherein the control means further has a memory control function of storing data relating to a target operation amount of the bellows expansion / contraction mechanism in a predetermined storage means. Artificial breathing apparatus. 3. The bellows expansion / contraction mechanism is configured as a crank mechanism for expanding / contracting the bellows and a motor for operating the crank mechanism, and a target operation amount calculation function of the arithmetic control means corresponds to the simulated breathing pattern. The calculation is performed by calculating a target rotation angle of the motor so that the amount of air taken in is discharged / inhaled from the conduit of the bellows, and the operation amount coincidence control function of the arithmetic control unit controls the actual rotation of the motor. The artificial respirator simulated breathing apparatus according to claim 1 or 2, wherein the artificial respiration apparatus is implemented by controlling the operation of the motor so that the angle matches the target rotation angle. 4. The artificial respirator simulated breathing apparatus according to claim 1, wherein the respiration / waveform conversion means is configured as a flow meter.