JP3329044B2 - Simulated respirator for artificial respirators - Google Patents

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 respirator, and more particularly to a simulated breathing apparatus capable of accurately simulating breathing by inputting various actual breaths (normal breathing, deep breathing, sighing, coughing, etc.). The present invention relates to a simulated respirator for a respirator suitable for reproducing.

[0002]

2. Description of the Related Art Conventionally, as described, for example, in Japanese Patent Application No. 5-121999 filed by the present applicant, breathing vibration (pressurized / negative pressure) generated by a breathing vibration generator is alternately applied to a vibration circuit. In addition, a ventilator for forcibly breathing a patient's lungs at a respiration rate corresponding to the frequency of the vibration circuit has been developed.
Spontaneous breathing is not possible with this ventilator (apnea)
When the patient inhales, the oxygen supplied from the oxygen source is sent to the patient's lung based on the respiratory vibration, and when exhaled, the exhaust air from the patient's lung is discharged to the atmosphere based on the respiratory vibration. Sending out. On the other hand, in order to avoid straining the lungs of patients who normally breathe spontaneously with apnea, the opening pressure of the spontaneous breathing valve provided in the expiratory circuit of the ventilator is controlled by the outlet pressure of the endotracheal tube. It is controlled to be constant.

[0003]

By the way, in the above-mentioned ventilator, especially in order to prevent a burden on the lungs even to a patient who normally breathes spontaneously with apnea, 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 becomes constant. To this end, various human breathing patterns (normal breathing, deep breathing, coughing, etc.) are required. ), It is necessary to determine the control amount of the opening of the spontaneous breathing valve. Therefore, conventionally, for example, a waveform that periodically fluctuates (for example, a sine wave or the like) is regarded as human respiration, and a device that generates the waveform is connected to an endotracheal tube of a ventilator.
Experiments have been conducted to control the spontaneous breathing valve opening so that the endotracheal tube outlet pressure is constant, but since the breathing pattern is different and complicated for each person,
The above-described apparatus that generates a periodically fluctuating waveform has a problem that it is difficult to reproduce various human respiratory patterns.

[0004]

SUMMARY OF THE INVENTION The present invention solves the above-mentioned disadvantages of the prior art. In particular, the present invention provides various types of actual breathing (normal breathing, deep breathing, sighing, coughing, etc.) by inputting various actual breathing. It is an object of the present invention to provide a simulated breathing apparatus for a respirator that can accurately reproduce simulated breathing having the same waveform.

[0005]

According to a first aspect of the present invention, there is provided a ventilator which is detachably connected to a respiratory system of an artificial respirator, wherein a predetermined amount of air as simulated respiration is provided by a telescopic operation. Normal breathing and deep breathing are provided in a simulated breathing apparatus for a ventilator including a bellows to be inhaled or discharged through a pipe, a bellows expansion and contraction mechanism for expanding and contracting the bellows, and control means for controlling the operation of the bellows expansion and contraction mechanism. Input means for inputting various actual respiration information such as sighing, coughing, etc., and respiration / waveform conversion for converting the actual respiration information input via the respiration input means into an electric respiration waveform signal Means, and wherein 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 breathing / waveform conversion means. A formation function, a target operation amount calculation function for calculating a target operation amount of the bellows expansion / contraction mechanism such that an air amount corresponding to the formed simulated breathing pattern is sucked / discharged from the conduit of the bellows, and the bellows An operation amount matching control function for controlling the operation of the bellows expansion / contraction mechanism so that the actual operation amount of the expansion / contraction mechanism matches the target operation amount is adopted. This aims to achieve the above-mentioned object.

According to a second aspect of the present invention, the control means further has a storage control function of storing data relating to a target operation amount of the bellows extension mechanism in a predetermined storage means.
The configuration is adopted.

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

According to a fourth aspect of the present invention, the respiration / waveform conversion means is configured as a flow meter.

[0009]

According to the first aspect of the present invention, various actual breathing information such as normal breathing, deep breathing, sighing, and coughing input through the breathing input means is converted into a respiratory waveform signal, and based on the respiratory waveform signal. Form a simulated breathing pattern having the same waveform as the input breathing waveform, calculate the target operation amount of the bellows expansion and contraction mechanism so that the air volume corresponding to the simulated breathing pattern is inhaled / discharged from the bellows pipeline, and In order to control the operation of the bellows expansion and contraction mechanism so that the actual amount of movement of the mechanism matches the target amount of movement, a simulated breath having the same waveform as various actual breaths input through the breath input means is connected to the bellows conduit. Can be output from Thus, if the pipe of the bellows of the simulated breathing apparatus is connected to the respiratory system of the ventilator, it becomes possible to test the ventilator under the same conditions as the actual spontaneous breathing of the patient.

According to the second aspect of the present invention, the control means includes:
Further, since a function of storing data relating to the target operation amount of the bellows expansion / contraction mechanism in the predetermined storage means is provided, it is possible to reproduce the same simulated respiration any number of times.

According to the third aspect of the present invention, the bellows extending / contracting mechanism is constituted as a crank mechanism for extending / contracting the bellows and a motor for operating the crank mechanism, and the amount of air corresponding to the simulated breathing pattern is sucked from the pipe of the bellows. / Calculates the target rotation angle of the motor so that it is discharged, and controls the operation of the motor so that the actual rotation angle of the motor matches the target rotation angle. It becomes possible.

According to the fourth aspect of the present invention, since the breathing / waveform converting means is constituted as a flow meter, normal breathing, deep breathing, sighing, coughing, etc. inputted via the breathing input means are converted into a flow rate waveform. As a result, a simulated breathing pattern corresponding to the flow waveform can be easily formed. As a result, the same waveform as various actual breaths such as normal breathing, deep breathing, sighing and coughing input through the breathing input means can be obtained. It is possible to accurately reproduce the simulated breathing that the user has.

[0013]

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

First, before describing the simulated breathing apparatus of the present embodiment, the configuration of the ventilator will be described with reference to FIG. 2. The ventilator 1 includes a blower 2 as a pressure generation source,
A vibration generating device 3, an infection blocking device 4, a vibration circuit 5,
An inspiratory circuit 7 connected to an oxygen source 6, an exhalation 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 for controlling each unit, a display unit 15 and the like.

The blower 2 is driven by a blower motor 16 to generate a pressurized pressure at a discharge port 1A and to generate a pressure at a suction port 1B.
A negative pressure is generated. Vibration generator 3
Operates the known rotary valve 3A driven by the rotary valve motor 17 so that the pressurized pressure and the negative pressure are changed by the vibration circuit 5
To be given alternately. The infection blocking device 4
The diaphragm 4 </ b> A is configured by a known mechanism provided with a diaphragm 4 </ b> A interposed in the middle of the vibration circuit 5 and following the pulsation generated by the vibration generator 3.

The oscillating circuit 5 includes an inhalation circuit 7 and an expiration circuit 1
0, communicating with the common circuit 11 and the tracheal tube 13
The patient's lungs are forcibly breathed at a respiration rate corresponding to the frequency of the vibration circuit 5.
The intake circuit 7 is supplied with oxygen from the oxygen source 6. The exhalation circuit 10 discharges air exhausted from the patient's lungs to the atmosphere via the spontaneous breathing valve 9.

The spontaneous breathing valve 9 is provided near the atmosphere opening port 8 of the expiration circuit 10 so as to be openable and closable.
, The outlet pressure of the tracheal tube 13 is kept constant. The pressure sensor 12 is provided near the outlet of the tracheal tube 13, and detects the outlet pressure of the tracheal tube 13 and outputs the detected pressure 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
7 is controlled to rotate the rotary valve 3A of the vibration generator 3. The control unit 14 controls the movement of the diaphragm 4A of the infection blocking device 4 and controls the opening of the spontaneous breathing valve 9 based on the detection signal of the pressure sensor 12 so that the outlet pressure of the tracheal tube 13 is constant. It is supposed to. The display unit 15 displays data related to the outlet pressure of the tracheal tube 13, data related to the optimal opening of the spontaneous breathing valve 9, and the like based on a command from the control unit 14.

When the respirator 1 inhales a patient who cannot breathe spontaneously (apnea), oxygen supplied from an oxygen source is supplied to the patient based on the respiratory vibration generated by the vibration generator 3 . When exhalation is performed on a patient who cannot breathe spontaneously (apnea), the air discharged from the patient's lungs is sent to the atmosphere based on the respiratory vibration generated by the respiratory vibration generator 2. Has become.

Next, the configuration of the simulated breathing apparatus according to the present embodiment will be described with reference to FIG. 1. A simulated breathing apparatus 20 includes a bellows 22 provided with a tube 21 for connecting a ventilator, 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 and 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. , D / A converter 28, port unit 29, A / D converter 30, counter 31,
The configuration includes a computer 32, an external memory 33, and a monitor 34.

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

The computer 32 is composed of, for example, a personal computer. The computer 32 performs various calculations described below and controls the respective parts of the simulated breathing apparatus. The computer 32 has an internal memory 36 for storing predetermined data. 37 and the like. The arithmetic control unit 35
The flow rate waveform signal supplied from the / D converter 30 is time-integrated to calculate the amount of inhaled air and the amount of exhaled air for each cycle of input breathing, and the bellows expands / contracts from the amount of air inhaled and exhaled. The rotation angles (maximum angle, minimum angle, start angle) of the motor for use 24 are calculated.

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

The D / A converter 28 converts the motor rotation command signal from digital to analog and converts the signal into a motor driver 25.
To be supplied to The motor driver 25 is
Bellows expansion / contraction motor 24 based on motor rotation command signal
Is rotated by a predetermined angle. The motor driver 25 supplies the motor control information to the arithmetic and control unit 35 of the computer 1 through the port unit 29,
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 extension / contraction motor 24 is adapted to extend / contract the bellows 22 via a crank mechanism 23 which will be described later. The detected piece 24 is provided on the outer peripheral surface of the bellows expansion / contraction motor 24 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 affixed. Top dead center detector 38
Is constituted by, for example, a photoelectric switch. When the detection target piece 24 of the bellows expansion / contraction motor 24 is detected, that is, when the crank mechanism 23 reaches the top dead center, the detection signal is transmitted to the computer 1 through the port unit 29. Is supplied to the arithmetic control unit 35.

The construction of the bellows 22, the crank mechanism 23, and the bellows expansion / contraction motor 24 will now be described with reference to FIGS. 3 and 4. The bellows 22 includes a top plate 22A.
, 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... A plurality of bolts 41A, 41B ...
Is fixed to the side plate 40B of the base 40 through the base. In the drawing, reference numeral 40C denotes a bottom plate of the base 40, reference numerals 40D and 40E denote support members for supporting the top plate 40A on the side plate 40B, and reference numeral 40 denotes a support member.
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 cylindrical outer ring portion 24A that is rotatable and a core 24B that is fixed to a hollow portion inside the outer ring portion 24A. The outer ring portion 24A rotates around the core 24B when the bellows expansion / contraction motor 24 is driven. A disc-shaped flange 43 is fixed to an 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.

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 provided with an operating shaft 44 passing through the center of each of these members. An operating shaft 44 projecting upward from the top plate 22A of the bellows 22
Has been fixed through. The operating shaft 44 projecting downward from the bottom plate 22B of the bellows 22 is attached to a top plate 40A of the base 40.
The mounting member 45 and the plurality of bolts 45 are
A, 45B, 45C, and 45D are fitted to the fixed bush 46 via the same.

A male thread 44B formed at the lower end of the operating shaft 44 is screwed into a female thread 47B formed at the upper inside of the first link 47. The spherical hollow portion formed inside the lower portion of the first link 47 has a ball 4
7A is rotatably inserted via 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. A male screw portion 49A formed at a lower portion of the connection shaft 49 is screwed through a lock nut 50 to a female screw portion 48B formed at an upper inner portion of the second link 48.

A ball 48A is rotatably inserted through a grease into a spherical hollow portion formed in a lower portion inside the second link 48, and a mounting shaft is attached to a side surface portion of the spherical surface of the ball 48A. The distal end surface of the first member 51 is fixed and caulked. A male screw portion 51A formed at the base end portion of the mounting shaft 51 is screwed via a nut 43B to a female screw portion 43A formed at a position eccentric from the center of the flange 43. Connecting shaft 49 and the second link 48 of the first link 47 is freely predetermined angle (e.g. 20-30 degrees) swing together to Figure 4 the lateral direction of the ball 47A as a fulcrum.

The operating shaft 44, the first link 47, the second link 48 and the like constitute the crank mechanism 23. Figure
Top dead center of the 4, reference numeral P1 is a crank mechanism 23, the bottom dead center of the code P 3 is a crank mechanism 23, the midpoint of the code P 2 is the top dead center and the bottom dead center, a circle represented by reference numeral K is a crank mechanism 23 5 shows the trajectory of the center of the ball 48A of the second link 48 constituting the second link 48.

When the bellows expansion / contraction motor 24 is driven by the motor driver 25, the bellows expansion / contraction motor 2
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 about the center of the ball 48A and draws a trajectory K. As a result, the operating 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 second bellows member 22C is fully extended upward and the crank mechanism 23 comes to the bottom dead center with the predetermined rotation of the bellows expansion / contraction motor 24, the bellows member 22C of the bellows 22 is most contracted downward.

Here, a method of calculating the target angle of the bellows expansion / contraction motor 24 will be described. Various actual breaths (eg, normal breath, deep breath, sigh, etc.) input through the breathing pattern input tube 26 and the flow meter 27 will be described. In the case of reproducing a cough or the like as a simulated breathing waveform by the expansion and contraction of the bellows 22, the flow rate within one cycle of control of the bellows expansion and contraction motor 24 corresponds to "bellows displacement x one 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 speed of the bellows expansion and 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. X = R (1−cos θ + ρ / 4 (1−cos 2θ) ) (1) V = Rω (sin θ + ρ / 2 · sin 2θ) (2) The following relational expression holds. The arithmetic and control unit 35 of the computer 32 sequentially substitutes an angle in the range of, for example, 0 to 180 degrees into the crank angle θ in predetermined increments, and controls the angle closest to the target bellows displacement X to control the bellows expansion / contraction motor 24. The target angle in the cycle is determined.

Here, FIG. 6 to FIG.
FIG. 8 is an explanatory diagram when the arithmetic control unit 35 calculates the rotation angle of the bellows expansion / contraction motor 24 based on the inhalation flow rate / expiration flow rate for each cycle of input breathing. FIG. 6 is a diagram showing a start point, an end point, a difference between suction and discharge of the bellows expansion / contraction motor 24 when the suction operation is performed before the discharge operation and the flow rate during the discharge operation is large, and FIG. FIG. 8 is a diagram illustrating a start point, an end point, a difference between suction and discharge of the bellows expansion / contraction motor 24, and the like in a case where the flow rate during the suction operation is larger than the discharge operation before the discharge operation. 6 and 7, the start point and the end point are located far from the top dead center because the sucking operation is earlier than the discharging operation.

FIG. 8 is a diagram showing the start point / end point, the difference between the suction and the discharge of the bellows expansion / contraction motor 24, etc. when the discharge operation is performed before the suction operation and the flow rate during the discharge operation is large. FIG. 9 shows a case where the discharge operation is performed before the suction operation and the flow rate during the suction operation is large.
FIG. 3 is a diagram illustrating a start point, an end point, a difference between suction and discharge, and the like of the bellows expansion / contraction motor 24. In FIG. 8 and FIG. 9, the start point and the end point are close to the top dead center because the spouting operation is earlier than the sucking operation.

FIG. 10 shows a bellows expansion / contraction motor 24.
FIG. 3 is a diagram of a target angle with respect to a time for each cycle of the control of FIG. 3. In the case of the sucking operation, the target angle falls from the angle of the start point to the offset angle. FIG. And the computer 32
Is stored as a file in the external memory 33 at the angles T1, T2, T3,.

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

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

The arithmetic and control unit 35 of the computer 32 of the simulated breathing apparatus 20 performs initialization such as erasing the contents displayed on the monitor 34 based on a predetermined operation of the operation unit 37 by the operator of the simulated breathing apparatus 20 (step S1). ), Calculate constants and the like used in the calculation of this process (step S)
2). When the operator of the simulated breathing apparatus 20 gives an instruction to newly create a reproducible waveform of a breathing pattern from the operation unit 37 (Yes in step S3), the processing from step S4 is executed, and the breathing pattern is input from the operation unit 37. If no instruction to create a new reproduced waveform is given (No at Step S3), the processing after Step S14 is executed.

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

The flow meter 27 measures various breathing patterns (eg, normal breathing, deep breathing, sighing, coughing, etc.) blown through the breathing pattern input tube 26, and outputs flow waveform data corresponding to various breathing patterns. (Respiration data) is A
/ D converter 30. As a result, the arithmetic and control unit 35 of the computer 32 acquires the flow rate waveform data (respiration data) 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 operator performs the operations in steps S5 and S6 again, while recreating the reproduced waveform of the breathing pattern. Is not input again (No at Step S8), the operation unit 37 instructs not to input again.

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

The arithmetic control unit 35 determines that the total flow rate is
If the total flow rate is less than the capacity of the bellows 22, if the total flow rate is less than the capacity of the bellows 22, the maximum angle, the minimum angle,
A start angle is calculated (step S12), and a target angle for each control cycle of the bellows expansion / contraction motor 24 is calculated (step S13).

If the data relating to the target angle of each control cycle of the bellows expansion / contraction motor 24 is to be stored in the external memory 33 as a file (Yes at step S18), the arithmetic control unit 35 determines whether the operator of the simulated breathing apparatus 20 is operating. Step S
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). If the data relating to the target angle for each control cycle is not stored as a file in the external memory 33, (No at Step S18), the arithmetic control unit 35 directly performs the process at Step S20.

On the other hand, if the operator of the simulated breathing apparatus 20 does not give an instruction to newly create a reproducible waveform of a breathing pattern from the operation unit 37 (No at step S3), the arithmetic control unit 35 A file to be read is selected (step S14). If there is no file (No at step S15), the process is terminated. If there is a file (yes at step S15), the file selected from the external memory 33 is deleted. Read data (step S1
6) The data is graphically displayed on the monitor 34 (step S17). After that, the processing shifts to the processing of 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 extension / retraction motor 24 to operate. The bellows expansion / contraction motor 24 is rotated through the motor driver 25 by a predetermined rotation until the detection target piece 24 attached to the outer peripheral surface of the bellows is detected (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 determines the current angle of the bellows expansion / contraction motor 24 from the motor driver 25 to the counter 31. (Step S24), and calculates the deviation between the target angle of the bellows expansion / contraction motor 24 and the current angle (Step S25).

Further, the arithmetic and control unit 35 converts the deviation between the target angle and the current angle of the bellows expansion / contraction motor 24 into a rotation command value to be supplied to the D / A converter 28 (step S26). The rotation command value is output to the D / A converter 28 so that the angle of 24 coincides with 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, and as a result, the motor driver 2
5 rotates the bellows expansion / contraction motor 24 to a target angle.

If there is still target angle data of the bellows expansion / contraction motor 24 corresponding to the breathing pattern (Yes at step S28), the arithmetic and control unit 35 proceeds to steps S22 to S22.
While repeating the processing in step S28, if there is no target angle data (No in step S28), it is determined whether or not to execute the same breathing pattern again (step S2).
9).

If the same breathing pattern is to be executed again, the arithmetic and control unit 35 executes the processing of steps S22 to S28. If the same breathing pattern is not executed again, the arithmetic control unit 35 calculates the target angle of the bellows telescopic motor 24 from the target angle. The calculated respiratory volume and the respiratory volume calculated from the actually rotated angle are graphically displayed on the monitor 34 (step S3).
0). The above is the flow of control in the present embodiment.

Thereafter, using various simulated breathing waveforms (normal breathing, deep breathing, sighing, coughing, etc.) reproduced by the simulated breathing apparatus 20, the outlet pressure of the tracheal tube 13 of the ventilator 1 becomes constant. When the control amount of the opening of the spontaneous breathing valve 9 is determined in advance, the respirator tube 21 of the bellows 22 of the simulated respirator 20 is connected to the tracheal tube 13 of the respirator 1 and the simulated respiratory waveform is artificially ventilated. Output to the container 1.

Thus, the control unit 14 of the ventilator 1
Controls the opening of the spontaneous breathing valve 9 based on the detection signal of the pressure sensor 12 so that the outlet pressure of the tracheal tube 13 becomes constant. Display unit 15
Displays data relating to the outlet pressure of the tracheal tube 13, data relating to the optimal opening of the spontaneous breathing valve 9, and the like based on a command from the control unit 14.

As described above, according to the present 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 is inputted. Outputting (reproducing) a simulated breath having the same waveform as the input breath from the ventilator connection tube 21 of the bellows 22 to drive and control the bellows expansion / contraction motor 24 based on the flow rate of the breath waveform. Can be.

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

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

Furthermore, according to the present embodiment, the bellows 2
Since the amount of air for inhaling / expiring in 2 is changed, it is possible to reproduce complicated and subtle simulated breathing.

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

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

[0063]

As described above, according to the simulated breathing apparatus for a respirator according to the first aspect of the present invention, various actual breathing, such as normal breathing, deep breathing, sighing, and coughing, which are input through the breathing input means. The respiratory information is converted into a respiratory waveform signal, and a simulated respiratory pattern having the same waveform as the input respiratory waveform is formed based on the respiratory waveform signal, and an air volume corresponding to the simulated respiratory pattern is inhaled / exhaled from a bellows conduit. In order to control the operation of the bellows expansion and contraction mechanism so that the actual operation amount of the bellows expansion and contraction mechanism coincides with the target operation amount, the target operation amount of the bellows expansion and contraction mechanism is calculated as described above. Simulated breathing having the same waveform as actual breathing can be output from the bellows conduit. This allows
By connecting the bellows pipe of the simulated breathing apparatus to the respiratory system of the respirator, it is possible to test the respirator under the same conditions as the actual spontaneous breathing of the patient.

According to the simulated respirator for ventilators of the second aspect of the present invention, the control means further has a function of storing data relating to the target operation amount of the bellows expansion and contraction mechanism in the predetermined storage means. This makes it possible to reproduce the same simulated respiration as many times as possible.

According to a third aspect of the present invention, the bellows expansion and contraction mechanism is constituted as a crank mechanism for expanding and contracting the bellows and a motor for operating the crank mechanism, and the air volume corresponding to the simulation breathing pattern. Calculates the target rotation angle of the motor so that is sucked / discharged from the pipe of the bellows, and controls the operation of the motor so that the actual rotation angle of the motor matches the target rotation angle.
There is an effect that a simulated respiration having a complicated and subtle waveform can be reproduced.

According to the fourth aspect of the present invention, since the respiratory / waveform converting means is configured as a flow meter, normal breathing, deep breathing, sighing, and the like input through the respiratory input means are provided. It is possible to easily form a simulated breathing pattern corresponding to the flow waveform by converting cough or the like into a flow waveform. As a result, as described above, normal breathing, deep breathing, sighing, There is an effect that it is possible to accurately reproduce a simulated breath having the same waveform as various actual breaths such as a cough.

[Brief description of the drawings]

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

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

FIG. 3 is a front view, partially omitted, showing a configuration of a bellows, a crank mechanism, a bellows expansion / contraction motor, and the like in the embodiment.

FIG. 4 is a right side view of the bellows / crank mechanism / bellows extension motor shown in FIG.

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

6 (a) is an explanatory diagram showing each flow rate when the suction operation is performed before the discharge operation, and FIG. 6 (b) is the start point / end point of the bellows expansion / contraction motor; FIG.

FIG. 7A is an explanatory diagram showing each flow rate in a case where the suction operation is performed before the discharge operation, and FIG. 7B is a diagram illustrating a start point, an end point, and a difference between the suction and the discharge of the bellows expansion / contraction motor. FIG.

8 (a) is an explanatory view showing each flow rate when the discharging operation is performed before the sucking operation, and FIG. 8 (b) is the start point / end point of the bellows expansion / contraction motor; FIG.

FIG. 9A is an explanatory diagram showing a flow rate when a discharging operation is performed before a sucking operation, and FIG. 9B is a start point / end point of a bellows expansion / contraction motor, a difference between suction and discharging, and the like. FIG.

10A is an explanatory view showing a target angle of a bellows expansion / contraction motor in a suction operation and a discharge operation, and FIG.
0 (b) is an explanatory diagram in which a part in FIG. 10 (a) is enlarged.

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

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

[Explanation of symbols]

Reference Signs List 1 artificial respirator 13 tracheal tube as respiratory system 20 simulated breathing apparatus 21 artificial respirator connection tube as conduit 22 bellows 23 crank mechanism as bellows expansion and contraction mechanism 24 bellows expansion and contraction motor as bellows expansion and contraction mechanism 26 respiratory input Tube for inputting breathing pattern as means 27 Flow meter as breathing / waveform conversion means 32 Computer 33 External memory as storage means 35 Calculation control unit as control means

Continuation of front page (58) Field surveyed (Int.Cl. ⁷ , DB name) A61M 16/00 G09B 9/00

Claims (4)

(57) [Claims] 1. A bellows having a pipeline detachably connected to a respiratory system of a ventilator, and inhaling or discharging a predetermined amount of air as a simulated breath through the pipeline by expansion and contraction operation, In a simulated breathing apparatus for a respirator, comprising: a bellows expansion / contraction mechanism for expanding / contracting the bellows; and control means for controlling the operation of the bellows expansion / contraction mechanism, various actual breathing information such as normal breathing, deep breathing, sighing and coughing. And respiration / waveform conversion means for converting the actual respiration information input via the respiration input means into an electric respiration waveform signal, wherein the control means comprises: / A simulated breathing pattern forming function of forming a simulated breathing pattern having the same waveform as the waveform of the input breath based on the breathing waveform signal output from the waveform converting means; A target operation amount calculation function for calculating a target operation amount of the bellows expansion / contraction mechanism such that an air amount corresponding to the pattern is sucked / discharged from the conduit of the bellows; A simulated breathing apparatus for an artificial respirator, comprising: a movement amount matching control function for controlling the operation of the bellows expansion / contraction mechanism so as to match a target movement amount. 2. The artificial respiration according to claim 1, wherein said control means further comprises a storage control function of storing data relating to a target operation amount of said bellows extension mechanism in a predetermined storage means. A dexterous respirator. 3. The bellows expansion and contraction mechanism is configured as a crank mechanism for expanding and contracting the bellows and a motor for operating the crank mechanism, and a target operation amount calculation function of the control means corresponds to the simulated breathing pattern. is performed by the air amount calculates a target rotation angle of the motor as inhaled / discharged from the conduit of the bellows, the operation amount consistent control function of said control means, the actual rotation angle of the motor The artificial respirator according to claim 1 or 2, wherein the simulation is performed by controlling the operation of the motor so as to match the target rotation angle. 4. A simulated respirator according to claim 1, wherein said respiratory / waveform converting means is constituted as a flow meter.