JPS58500005A - breathing apparatus - Google Patents

Abstract

(57) [Summary] This bulletin contains application data before electronic filing, so abstract data is not recorded.

Description

[Detailed description of the invention] Title of invention: Breathing apparatus and method abstract A fluid-operated breathing apparatus includes a breathing hold circuit θO and a demand gas circuit (A). have The breathing hold circuit Oq includes a variable capacitance device (132) and an inhalation evacuation means (130) for rapidly ejecting fluid from the circuit θq when the .

If a respiratory arrest occurs, circuit 01c, the default volume of fluid As set, one or more signals (136) are activated. Breathing equipment requirements gas times Route (a) provides respiratory gas to the patient at the beginning of inhalation and for a period that is only a small part of the inhalation period. supply the

background The present invention relates to breathing apparatus and methods of operating the same, and more particularly to intermittent oxygen demand. Relating to such devices and methods of operation thereof, which feature detection of respiratory arrest and/or cessation of breathing. .

Intermittent demand oxygen flow has been used in the past to provide oxygen flow to patients. This is an attempt to reduce the generally high costs involved. Di, ara Nirbach et al. (Chest, 74: July 1, 1978, pp. 39-44) Reviewing the history of such projects, we have developed an oxygen cannulation system using intermittent-demand true flow. reports the test results observed in the system. By Auerbatsuno et al. The device reported in of the spring that works with the cannula to detect the light in two polar modes. Using a loaded diaphragm. In negative pressure mode, the reporting device Supply oxygen to the patient as long as 1,000 is detected.

In positive pressure mode, oxygen is supplied unless a stop is detected.

Fluid logic elements are also used in intermittent demand oxygen systems for inhalation and exhalation. - Detects negative and positive pressure caused by air. In this regard, the response to Durcan is U.S. Pat. No. 3,976,065 refers to a known side ventilation pipe using a fluid element, further, a single fluidic flip-flop is used as the first control element; Bias signals applied to the flip-flop in any one of multiple operating modes discloses a digital fluid ventilation device which can be obtained by adjusting the .

A known intermittent demand oxygen device detects either negative pressure or positive pressure and determines the inhalation period. Supplies oxygen to the patient. If a patient breathes at a rate of, say, 10 breaths per minute, If you were to inhale, each breath would average 6 seconds. For such patients, Inhalation is normally detected for about 2 out of 6 seconds per breath, and exhalation is normal for the remaining 4 seconds. will be detected. Therefore, the leading device will release the acid for the entire duration of the inhalation--in this case, 2 seconds. I tried to supply the material.

The current device tested by Alanirbach et al. Oxygen that flows tends to begin to undulate in a flow pattern. Until now, this swell considered unnecessary and wasteful. In some devices, other fluid elements, such as flow meters, is combined between the patient and the oxygen supply to reduce heaviness.

However, what the applicant has clinically observed is that during the breathing process, oxygen is inhaled. The point is that it is absorbed into the blood only in the early stages. 9. Oxygen effectively reaches the alveoli. It is reached during the early stages of inhalation. Oxygen applied during the later stages of inhalation , remaining in "dead spaces" such as the trachea and bronchi. As a result, the applicant: In operation of the breathing apparatus, a large volume of oxygen is applied per second and over the period of inhalation. Oxygen only during the early stages of inhalation is more effective than applying the normal amount per second Observations have demonstrated that it is more advantageous to apply

-1=, the effective initial phase may last approximately 0.25 seconds.

In many cases, the effective initial phase is about 4 or less, usually about 1 inhalation period. Therefore In addition, the amount of l-1 oxygen per second is less than the normal amount (e.g., 50 QC per second). Savings of over 100 if supplied at twice the rate of 100(-C) per second - in many cases More than Sae - One is realized. Current intermittent oxygen demand devices utilize this effective early stage of suction. It is impossible to operate according to the input phenomenon.

Respirators according to known examples aim to detect when breathing stops. Basically, respiratory arrest Halts may be caused by cessation of central nervous system output, air sabotage, or a combination of both. breathing irregularities. This disorder is associated with the syndrome of sudden child death. this state is immediately harmful in patients with chronic lung disease because cardiac arrhythmias are dangerously This is because it is caused by elemental deficiency.

Among the publicly known devices for the purpose of detecting respiratory cessation, many (Carso's American special No. 3,357,428 and Cox No. 4,206,754. (contains) periodically generates an electrical signal (as opposed to a fluidic signal) that is electrically monitored. determine whether the patient has held his breath satisfactorily or the signal can be used as a warning indication. Activate the alarm.

Known side respirators that use fluid signals to detect when breathing stops are basically fixed key A capacitance device is used to time or control the length of time between inhalations. A call like this Examples of haustors include Steward's US Pat. No. 3,191,01270; 8,659,598 and Izumatsuno 4,141,354. fluid For signal-based breath-hold detectors, fixed capacitance is inappropriate; That is, the fluid shrinkage at a fixed volume is combined with the low pressure sometimes used in fluidic logic circuits. That's because there isn't. Moreover, the fixed capacitance of the known example is , and at a rate much slower than desired for an effective breath-stop detector. It is.

In view of the above, it is an object of the present invention to Provides a breathing apparatus that supplies inspiratory gas to a patient during periods of rest, and a method of operating the same. It is toto.

An advantage of the present invention is that it provides an economical and effective way to store inspired gases such as oxygen. Providing a suction device.

Another object is to provide a breathing apparatus having a fluidically actuated breath hold detector. That is.

Still other objects have variable capacitances compatible with fluid logic elements. A breathing apparatus is provided having a breath hold detector and means for rapid evacuation.

overview The breathing apparatus includes a means for detecting whether the patient is inhaling or exhaling, and a means for detecting whether the patient is inhaling or exhaling. a first generating means for generating a first fluid signal indicative of a period of either inhalation or exhalation; nothing.

The first output port of the first generating means is connected to a variable capacitance device that is connected to a discharge valve. (e.g., fluidically actuated breath-hold circuits containing elastomers (Luno)) is bordered by The breath-hold circuit selectively includes one or more signaling means (e.g. counter, alarm or electrocardiogram monitor) at which time the patient Do not inhale.

A second output port of the first generating means is in communication with a fluidically actuated demand gas control circuit. There is. In various embodiments thereof, the demand gas control circuit includes a second fluid signal corresponding to the first fluid signal. a period of time that is related to the period of the first fluid signal by a predetermined relationship. generating a second fluid signal having a second fluid signal; The demand oxygen control circuit is further coupled to the second fluid signal. a source means including a responsive valve means at a time associated with the period of the second fluid signal; control the application of inspired gas to the patient during the period. Preferably, inhalation to the patient The gas application period is less than 0.25 of the inhalation period.

A laminar chemotaxis amplifier was used as a detection means, and initial attempts to inhale and exhale Detects very small pressures such as those generated by

Brief description of the drawing The foregoing and other objects, characteristics and advantages of the present invention will be realized by the preferred embodiments illustrated in the accompanying drawings. The embodiments will be apparent from the detailed description that follows, and in the drawings reference numerals will be used in each figure. It refers to the same part. The drawings are not necessarily to scale and do not provide a detailed description of the invention. It's going to be.

FIG. 1 is a schematic diagram of a breathing apparatus according to an embodiment of the present invention.

FIG. 2 is a schematic diagram illustrating suitable sensing means for use in the present invention.

Figures 3A, 3B and 30 respectively illustrate suitable first generation means for use in the present invention. FIG. 3 is a schematic diagram illustrating different embodiments;

FIG. 4 is a schematic diagram illustrating a request control circuit according to an embodiment of the present invention.

Figures 5A, 5B and 5C are graphs illustrating various methods of delivering inspired gas to a patient. It is f.

Brief description of the drawing FIG. 1 shows one implementation of the present invention that includes a respiratory arrest generation circuit 10 and a demand gas control circuit 20. 1 illustrates a breathing apparatus according to an example;

The embodiment of FIG. It includes a cannula or nasal fork device 22. For example, the nose can be sealed due to the nasal thickness. 0 For simplicity, a mask is used instead of a nose fork device when there is a chain or conduit. , pipes, channels, and other closed fluid conduits are hereinafter referred to as lines. It is called as.

The sensing means 26 is capable of detecting the direction and duration of pressure flow in the patient's respiratory system. It is a very good device. In other words, the detection means 26 detects whether the inhalation is caused by the patient's intention to inhale. It is possible to detect the negative pressure caused by exhaled air and the positive pressure caused by exhaled air. As commonly known from Figure 1 The sensing means 26 includes a first control boat 28 connected to the sensing line 24; A second control port 30 . fluidly connected to a control valve 32 . Fluid by line 38 Power flow port 349 connected to source 36 and two output ports or output legs 4 Contains 0.42.

The illustrated fluid source 26 connected to the sensing means 26 in FIG. A small pump or conventional well supply to provide oxygen or other desired fluids. It may be placed. The embodiments described below include a plurality of fluid sources 46 (each source being essentially similar to fluid source 36). ), but instead the fluid element is A single source, such as source 36, may be connected by suitable fittings. if you wish For example, a restrictor 48, such as a variable restrictor or pressure regulator, can be used to They may be connected directly.

As seen in FIG. 2, one embodiment of the sensing means 26 includes a plurality of fluid amplifiers suitable for encompasses. In particular, the embodiment of FIG. Examine the three-stage amplification network. However, other embodiments of the detection means 26 may include It may have an appropriate number of stages depending on the degree of amplification. Both fluid amplifiers (each a first control port (shown as 50a, 52a and 54a); a second control port; (50b, 52b and 54b) i Power flow ports (50C+ 52C+ 54 C) i first output port (50d.

52dl 54d); and a second output boat (50e1526154e) Ru.

The amplifiers 50+52 and 54 are connected in three stages as follows. output port 50d is connected by line 56 to control port 52a. Out capo) 52d is control baud) 54C by line 60 and output port 52 e is connected by line 62 to control port 54a. Each power flow input port ports are connected to one fluid source: ports 52G and 54C are connected to source 46. The other port 50C is connected to a source 36 via line 34. No. As seen in Figure 2, the control port 50a is connected to the sensing line 24; The control port 50b is substantially the second control port 30 of the detection means 26; The output cap (P) 54d is connected to the output arm 40 of the detection means 26; The port 54c is connected to the output arm 42 of the detection means 26.

The amplifiers 50, 52 and 54 of the detection means 26 in FIG. They are connected so that the gain is 6:1. Amplifiers 50, 52 and 5 of FIG. 4 is a conventional fluid flow fluid amplifier operating at sufficiently low pressures that the flow is unchanging. or a laminar fluid amplifier. Laminar fluid amplifiers are highly sensitive , using laminar flow rather than vortex flow as in typical Commander-type devices.

This type of laminar fluid amplifier is available from the Tritic Company of Columbia, Mary. Ru. In either case, the sensing means 26 detects the initial Inhalation can be detected.

The breathing apparatus of FIG. 1 further includes a first control boat 66, a second control boat 68, a first a first generating means including an output port or leg 70 and a second output boat or leg 72; It includes 64.

FIG. 3A illustrates in detail one embodiment of a suitable generating means for use in the present invention. Ru. Generating means 64A of FIG. 3A includes a fluidic amplifier 74 and a NOR gate 76. Ru. The amplifier 74 includes a first control boat 74a; a second control boat 74b; a first outlet door 74C; a first outlet door 74d; and a second outlet door 4e. . In the embodiment of FIG. 3A, control ports 74a and 74b are substantially the respective control ports 68 and 66 of the generating means 64A; 4C is connected to source 46: and output port door 4e is connected to . N0I (gate 76 is connected to control port 76a, power flow port 76C1 first output It includes a port door 6d and a second exit port door 6e. What can be understood from Figure 3 , power flow 76C is connected to source 46 and output port door 6° 766 is connected to source 46. 1 to the output arms 70 and 72 of the generating means, respectively. NOR game The line 78 connecting the port 76b and the output port 74d to the control port 75a is connected to amplifier 74 by.

FIG. 38 illustrates a second embodiment of the first generating means suitable for use in the present invention.

In particular, FIG. 3B shows a laminar current ratio amplifier 79 and a laminar stalled flip-flop 80. The first generating means 64B is illustrated. The fluidic flip-flop 80 is Furthermore, it includes two laminar current ratio amplifiers 81 and 82. Amplifiers 79, 81 and 8 2 are set up by the amplifiers 50, 52, 54 and 74 mentioned in Alpha Vent labeled input, power flow, and output ports. It has a Similarly, each amplifier has its power flow input connected to source 46. .

Amplifier 81 of flip-flop 80 is connected to amplifier 79 by line 83°84. -- line 83 connects control board 81b to output port door 9d. ゛, Rai/84 connects the control port 81a to the output port door 9e. flip-flo Amplifiers 81 and 82 of top 80 are connected to line 85°0. 86 and two return paths described below. Line 85 is the output point. Connect port 81d to control board 82b, and line 86 controls output port 81e. Connects to port 82a. The feedback path 87a connects the output port 81e and input port of the amplifier 81. ) 81bk interconnection, and the feedback path 87b connects the output port 81d and input port of the amplifier 81. The ports 81a are interconnected. The control manual port doors 9a, 79b are essentially 1 generation means (, 4B each control port 68° 66, output port 82 d and 82e are connected to the output arms 70 and 72, respectively. Commonly listed as 88 The various resistors shown are located at various points in flip-flop 80. and are included in the return paths 87a and 87b.

FIG. 3C illustrates a third embodiment of the first generating means also suitable for use in the present invention. do. In particular, FIG. 3C shows electrohydraulic amplifier 90 and bistable fluidic flip-flop. A first generating means 64Ci including a tap 92 is illustrated. Amplifier 90 and Flynnpoof Rosop 92 includes alphabetically labeled human power ports and power flow ports as described above. It has a port and an output port. Flip-flop 92 lies at 93°94 ysp, -1 line 93 is connected to amplifier 90 and outputs control port 92b. Line 94 connects control port 92a to output port 90C. ingredient. The control ports 90a, 90b are substantially connected to each of the first generating means 64e. control port 68.66 and output 1 Ports 92Cl and 92C are connected to output arms 72 and 70, respectively. amplifier Output port 90e of 90 is geometrically loaded so that the signal is applied to amplifier 90. either when the signal is not applied to its input port 90b or when a signal is applied to its input port 90b. At times, a fluid signal is generated at leg 72 of generating means 64C. 2 in Figure 3C means 6 A first generating means similar to the means illustrated as 4 was developed by Corning Glass Company. sensor trigger (code 192681).

FIG. 1 illustrates one embodiment of a demand gas control circuit 20. FIG. Demand gas control circuit 20 For example, it includes second generating means 96 and source means 98 .

The second generation means 96 of the demand gas control circuit 20 is a first output boat 96 which is popular. a; Second output port 96bi connected to north means 98 via line 100 19 first power port 96C7 connected to source 46 and line 102 It includes a second human powered boat 96 connected to the output arm 70 of the generating means 64. Second outbreak Means 96 further includes a first end 10 that intersects perpendicularly with input port 96C. 4a and a second end 104b perpendicularly intersecting input port 96G on the other hand. It includes a closed fluid circuit 104. Ends 104a and 104b are input ports 96G It is linear at the intersection with. The fluid path 104 is connected to a fluid restriction device 106 and/or a key. It includes one or more timing means, such as a capacitance device 108. Figure 1 Implementation 2 As shown in the example, the throttle device 106 is a variable resistance and the capacitance 108 is a variable capacitance like an elastomer balloon. Squeezing device 106 and capacitor The capacitance 108 may be a similar throttling device or capacitor with different values and capacitances. Can be exchanged with chest of drawers.

The source means 98 of the demand gas control circuit 20 is connected to the suction gas source 11 by line 114. The demand valve connected to 2 weighs 110 kg. demand valve 110 and source 112 on line 114; A regulator 116 and a flow meter 118 are interposed therebetween. The demand valve 110 also a fluid transport means or line 120 for supplying incoming gas to nasal fork device 22; It is connected. Bypass line 122 with bypass switch 124 The request valve 110 is connected between the valves 114 and 120 to selectively short circuit the request valve 110. Regarding this point The demand valve 110 may be any suitable type, such as a moving part valve or a diaphragm valve. However, the ALCON Series A Model 7986 valve is actually preferred.

A second embodiment of a suitable demand gas control circuit is illustrated in FIG. This control circuit 20 ' includes second generating means 96' and source means 98'. The second generating means is line 10 0' connected to source means 98') 96M; closed to atmosphere. Second output port 96b'; first port 96C' connected to source 46; The second human power connected to the output arm 70 of the first generating means 64 by line 102' It encompasses port 96d'. As in the embodiment of FIG. Device 96 has respective ends 104a, 104bt--a fluid path 104 and a timer. ng means 106 and 108.

Source means 98 is connected to a suitable source 112 by line 114, as shown in FIG. diaphragm valve 110. Demand valve 110 is connected to the The first input port 1ioa is connected to the line 114, and the first input port 1ioa is connected to the line 114. 2-man powered boat 110b: output port 1lOb connected to fluid transport means 120; It also has a flexible diaphragm 110d. The embodiment shown in Figure 1 and Similarly, the embodiment of FIG. 4 also includes a bypass switch 124. Including 122 ins.

In either the embodiment of FIG. 1 or FIG. 4, the demand gas control circuit further includes a Counter display labeled 160 in Figure 1 and 160 in Figure 4 Contains circuits. Circuit 160 of FIG. 1 is connected to line 100 by line 164. includes a connected air counter 162.

The circuit 160 of FIG. Generates an electrical signal with a duration equal to the duration of the fluidic signal applied as input It includes two pressure electrical devices 166, 168 suitable for

Device 166u is connected to line 120 on line 170 and device 166 connects to line 120 on line 170. The device 1 is electrically connected to the display device 176 by a wire 174; 68 is 4 It is electrically connected to a display device 180 by a lead wire 178. Dis The play devices 176, 180 each have a clock means, a reset means and a readout device. O containing illustrated components such as means for reading (such as digital readout) In either the FIG. 1 or FIG. 4 embodiment, an oscillator 126 is connected on line 120. (nasal fork tool 22) and the source means (110 or 116). stomach.

The oscillator 126 emits a high frequency wave in the direction of the inhaled gas flow that increases the diffusion of gas into the lungs. used to make a living. The oscillator 126 is, for example, a rotary motor or It may also include a pump. Bypass line 127 is connected with switch 128 to Its ends are connected to line 120 and are on opposite sides of oscillator 126. switch 128 The selective action of effectively shorts out the oscillator 126 and provides a non-oscillating flow of inspired gas.

The breath hold circuit 10 is fluidly connected to the output arm 72 of the first generating means 64 and Ejector [130 (like a mushroom valve); variable capacitance device 182 (e.g. e.g., elastomeric balloons); digital fluidic devices (e.g., NOR gates); and at least one signaling means (e.g. a pneumatically operated digital counter). data 136ai alarm 186b i and electrocardiogram monitor 136C) including.

Variable capacitance devices 132 and 5 of breath-hold circuit 10 NOR gate 134 is connected to output leg 72 of first generating means 64 by line 138. Connect. Fluid resistance 140 is connected to first generating means 64 and variable capacitor on line 138. intervening between the control device 132 and the device 132. Fluid path or line 142Pi, fluid resistance 140 and connected parallel to line 138. Mushroom discharge valve 130 is on channel 142 present and closes when a fluid signal is applied thereto from the direction of the generating means 64. works.

The NOR gate 134 connects to the first caboto 134ai line 1 connected to the source 46. 2nd human-powered boat 134b connected to 38; 1st outgoing boat 134 connected to the atmosphere G, and a second output capo (134d) connected to the signal converting means. this At the point, output capo) 134d is connected to the power switch 14 by line 144. 6 and also connected to lines 144, 148 and Nyoshikakunta 136a. . Pressure electric switch 146 is connected to alarm means by suitable leads 148-150. 136b and electrically connected to the electrocardiogram monitor 136c. Alarm means 136b is possible It may be an audible alarm, a visual alarm, or both.

Pressure/electrical device 152 connects first generator 64 and fluid resistance 1 by line 154. Pneumatically abuts a portion of line 138 between 40 and 40. Pressure electric device 152, Generates an electrical signal having a duration equal to the duration of the fluid signal applied as input It is of the model type. The pressure electric device 152 is connected to the display by the lead wire 156. device 1586 electrically connected to. Display device 158 is connected to device 176.180. It is of the type described.

Before explaining the operation of the breathing apparatus mentioned above, it should be noted that oxygen is rapidly inhaled. Applicants believe that during the respiratory process clinical This is what I have observed. To illustrate this observation, sections 5A, 5B and 50 Reference is made to the figure. To illustrate, if a patient breathes at a rate of lO breaths per minute. On average, each breath lasts about 6 seconds. To illustrate this example, FIGS. Each graph has a time axis that increases from 0 to 6 seconds. For simplicity, The second axis of the graph is incremented from 0 to 6 liters per minute, indicating the delivery of inspired gas to the patient. It shows the supply ratio.

FIG. 5A illustrates an apparatus for continuously supplying inspired gas to a patient. 5th A The graph in the figure shows a roughly horizontal straight line, and the area under the line plate corresponds to the amount of gas supplied. Approximately match. For the 6 second period shown, the gas supply is approximately 0.8+) liters (=32 22X 1 minute minutes TτN x 6 seconds). Breathe for 6 seconds Since only about 2 seconds are required for suction, using the continuous feeding device of Figure 5A , a considerable amount of loss occurs.

The more frugal prior art intermittent demand devices supply inspired gas only during inspiration. supply Such a device is represented by FIG. It shows the subsequent approximately parallel glands. The gas supplied in Figure 5B is approximately 0.1 liters. It is.

7 As mentioned above, in operating the breathing apparatus, the normal The rapid phase of the effect of inhalation rather than the volume rate increases the volume of inhaled gas per minute. The applicant has observed that it is most advantageous to apply

Therefore, Figure 5C shows that it is preferable to give a large volume of oxygen during the rapid stage of inhalation. Illustrating Applicants' discoveries of the following. The fast phase of this effect is during the inhalation period. About 1/4 or less (normally about 1/8). In particular, Fig. 5c shows a time period of about 0.25 seconds. [5pike] S of subsequent oxygen flow of approximately 6 liters per minute is illustrated. Therefore , 1 minute in Figure 5c X-"25 seconds) or less. Operates in the manner described below and has the configuration described above. facilitates the delivery of inspired gases, such as oxygen, to the patient according to the method of Figure 5C. .

When the patient attempts to inhale, the negative pressure created in the nasal fork device 22 and line 24 is detected. Detected by means 26.

As mentioned above, the detection means 26 can detect negative pressure as small as 0.5 milliliters of water. Ru. When detecting negative pressure caused by inhalation, the detection means 26 uses a fluid signal at the output leg 42. generate a number.

Regarding the above, and regarding the embodiment of the sensing means 26 illustrated in FIG. The negative pressure on the inlet 24 causes a power flow to be applied to the boat 34 of the sensing means 26. Capo) Deflects to 50e. The resulting fluid signal is passed along line 58 to amplifier 5. This is applied to the second control boat 52a.

8 As a result, the power flow input boat 52C of the amplifier 52 is transferred to the output port 52Cl. deflection and generate a signal on line 60. In a similar manner, the signal on line 60 is applied to control port 54C of amplifier 54, which results in a fluid signal being detected. occurs on the output leg 42 of the sensing means 26. For the illustrated embodiment, the sensing means 26 Each stage of the amplifier delivers a gain of approximately 6 to 1.

The fluid signal on the output leg 42 of the sensing means 26 is applied to the control port 68 of the first generating means. and finally, as will be explained below in each variant of the means 64. This results in a body signal being generated and applied to output port 0.

The first fluid signal has a period approximately equal to the patient's inhalation period.

In the generating means 64A of the embodiment shown in FIG. 3A, the signal on the output leg 42 is amplified. The power flow applied to the control boat 74a of the vessel 74 and the power flow applied to the boat 74C. is deflected to output port door 4d, thereby generating a fluid signal on line 78. do. The fluid signal on line 78 is applied to control port 76a of NOR gate 76. and deflects the power flow entering cuff 76C to output cuff 6d, thereby and generates a first fluid signal at the output leg 7o.

In the generating means 64B of the embodiment shown in FIG. 3B, the signal of the output leg 42 is amplified. is applied to control port 79a of device 79 to output power flow entering input port door 9C. capo) 79d, thus causing a fluid signal 9 on line 83. occurs. The fluid signal on line 83 is connected to a flip-flop 80, specifically a control button. This applies to amplifier 81 in port 81b. The fluid signal on line 83 is the power flow The input port 81C is deflected toward the output port 81e, so that the line 86 and A fluid signal is generated on both return lines 87a. The signal on line 86 is fed to amplifier 82 is applied to the control port 82a of the power flow input port 82C of the output boat 8. 2e direction, thereby generating a first fluid signal at the output membrane 7°.

In the generating means 64C of the embodiment shown in FIG. Applies to 0a. The output membrane 42 signal overcomes the geometric loads and the input of the power flow. Deflects port 90C to output port 90d, thereby providing a fluid signal on line 93. occurs. The signal on line 93 is the control port of bistable flip-flop 92. 2b and in the same manner enters port 92C to the output port 92b to generate a first fluid signal at output membrane 70.

The explanation of the operation of the inhalation phase of the breathing apparatus is based on the demand gas control circuit shown in Fig. 1 and Fig. 4. 20, the first fluid signal generated by means 64 at output membrane 70 is connected to line 1 This applies to the second generating means 96 on the 02. As is clear from Figure 1, line 1 In the absence of fluid signal on 02, generator 0 Power flow entering stage 96 (bow) 96C is communicated to atmosphere through output port 96a. Ru. However, when the first fluid signal is applied on line 102 to second generating means 96 The power flow entering the output port 96C for a certain period of time is determined by the method described below. Deflect to 6b. The first fluid signal on the line 102 is transmitted to the second generating means 96 (baud) 96. C], the power flow entering 96C is from the output port 96a to the output port 96a. -) a second fluid signal on line 100 deflected to 96b and applied to source means 98; occurs. The first fluid signal on line 102 also includes timing means (e.g. 106 and a capacitance device 108).

The timing means controls the passage of the first fluid signal around the closed loop fluid path 104f. Delay for some predetermined amount of time. In other words, the approximate value selected for the resistance of the variable resistor 106 is 2, and the capacitance device 108 with approximately the largest capacitance is selected, so that the closed A first fluid signal traveling through the same loop fluid circuit 104 is configured such that the signal There is a predetermined delay before reaching the second end 104b of the circuit 104. closed loop When the first fluid signal traveling through the fluid path 104 reaches the second end 104b, The fluid pressures on each side of the fluid flow entering port 96C are balanced and the fluid flow is is now deflected from port 96b, but instead returns to the atmosphere through bow) 96a. It spreads.

In this way, the second generating means 96 a second fluid signal is applied to line 102 from output membrane 7o; has a period of time related to the period of the first fluid signal. The first line in line 102 1 fluid signal on line 100 and a second fluid signal on line 100. under predetermined relationships depending on the values and dimensions chosen for the timing means. be. Such values and dimensions should be chosen for this example, and this such that the period of the second fluid signal with respect to the period of the first fluid signal, i.e. the inhalation period. The ratio is 0.25 or less. In many cases, if desired, the ratio is approximately It is sufficient if it is 0.125.

Valve means 110 of source means 98 is configured to provide intake gas from a source 112 along line 114. be supplied with. Valve means 110 provides a second fluid signal such as that received in line 100. The gas is given to the patient on line 120 for a period of time corresponding to the period of time. Therefore, In accordance with the predetermined relationships described above, the source means 98 may Supply inspiratory gas to the patient between. Regarding the demand gas controller 20' of the embodiment of FIG. the first fluid signal 2 on the output membrane 70 of the generating means 64; In this application, the fluid flow entry port 960' is connected from the output port 96a to the output port 960'. 96b for a time approximately equal to the time required for the first fluid signal. for a period of time through a closed loop fluid path 104, after which the fluid Balance fluid pressure on both sides of the flow.

In accordance with the above points, the fluid path 104 is similar to the fluid path 104 of the FIG. Similar timing means such as resistor 106' and capacitance 108 are included. No. In the embodiment of Figure 4, the value and dimensions of the timing means are greater than or equal to Lie; is selected so that it is 0.875 or more. Of course, the second fluid signal is is applied on line 100' only during the period after the power flow enters. Port 96C' is used during the initial phase of inhalation and during a short period thereafter. It communicates with the atmosphere via b'.

Valve means 110' of source means 98' directs intake gas from source 112' to line 114. and in the absence of a second fluid signal on line ioo', line 1 At 20, inspiratory gas is delivered to the patient. At this point, a second fluid is added to line 100'. The presence of the signal indicates that the diaphragm i o d' is loaded, but the pressure generated at the input port 110b in the other lie is applied to the die. deflecting the aphram 110d' and via the valve means 110'; Intake gas passes out of the output port 110C. Therefore, for the embodiment shown in FIG. In accordance with the predetermined timing relationships discussed above, valve means 110 is activated after the first phase of inhalation. Inspiratory gas is delivered to the patient for 0.5 minutes.

The counter display circuit 160, 160 of each embodiment is It provides the physician with data regarding the patient's respiratory activity and required gas regulators. line Counter 162 of FIG. Increased each time. In this way, the counter 162 is Tabulate the number of inhalations. The counter 162' in FIG. Similarly, each time an inhalation is intended (the output of means 96' each time the force passes into the atmosphere).

The operator or attending physician can view the line 12 on the display device 176 and 180. The period of inspiratory gas delivery to the patient at 0 and indicated by the fluid signal at line 102. The patient's inhalation period can be observed to ensure that the In this regard, the fluid signal are converted into electrical signals by each of the devices 166, 168. duration of electrical signal is timed by devices 176 and 180. Devices 176 and 180 read.

Display a numerical value (preferably a digital value) that corresponds to the period in the means, and cent by law. The display device 176, 180 is For example, the variable resistor 106 and/or 4 of the second generating means 96 may be adjusts and calibrates the timing means of capacitance 108, or selects This is particularly useful because it allows for selective changes.

Regarding the demand gas controller 20, 20' of each of the embodiments of FIGS. It should be understood that the two controllers are easily attachable and have the desired force. , delivering inspiratory gas over the inhalation period. This is done in several ways. Ru. For example, if the value of the throttle device 116 is lower than the output at the output port 96b over suction, The path 104 where the resistance occurs may be selected such that it has the greatest resistance. Or other examples As (not shown), the bypass line has one switch and the second generator Stages 96 may be selectively shorted. In this mode of operation, the first and second The default relationship between the two fluid signals is a 1:1 ratio or a fraction of /1.

Again, the required gas control means 20, 20' of the respective embodiments of FIGS. 1 and 4 , the breathing apparatus is connected to the appropriate bypass switch (124 in FIG. 1 and 1 in FIG. 4). 24) can be operated in continuous mode. Switch 124 (or 124) is closed, the intake gas flows into lines 114, 122 and 120 (or 11 4, 122 and 120) from source 112 (or 112'). make it possible.

For both embodiments of the demand gas controller shown in FIGS. 1 and 4, each flow rate 111 8 (118' in FIG. 4) is the valve means 5 110 (or 110) and the source 112 (or 112) between the nasal fork tool 22 Should be connected. Otherwise, the "5pike J S" shown in Figure 5C will fall and become sweet, resulting in insufficient gas supply.

During zero suction, the generating means 64 applies a first fluid signal to the output leg 70 instead of the output leg 72. Therefore, the breath-hold circuit 10 receives no fluid signal. The fact is that during inhalation, the variable key Fluid recovered by the tank device 132: C. Rapidly discharged to the mushroom exhalation valve 130. the valve is closed by a fluid signal applied to fluid path 142. It is et al. Variable capacitance and evacuation of device 132 in conjunction with mushroom discharge valve 130 The lag i-mer feature facilitates rapid fluid release from the variable capacitance device 132. make it easier. Fixed capacitance does not perform this function properly; It is incompatible with the low pressure used in logic circuits.

When the patient exhales, positive pressure is generated in the sensing line 24 at the nasal fork device 22. . Sensing means 26 senses positive pressure and generates a fluid signal on its output leg 40. Figure 2 In the embodiment of the detection means 26 shown in FIG. Positive pressure is applied to control boat 50a of 0, thereby causing power entering boat 50e. The flow is deflected to the output capo 50d, which generates a signal on line 56. La The signal at input 56 is applied to control port 52b of amplifier 52; generates a signal on line 62 and 6 It is applied to the control boat 54a of the increase/fukuki 54. I will explain this point in detail However, it should be understood that amplifiers 52 and 54 operate as described above with respect to the negative pressure operation button. It operates according to the same principle as the sea urchin. Of course, the fluid signal is determined by the negative pressure operation button. applied to the opposite input port and emitted to the opposite output port. Ru.

The fluid signal in line 40 is applied to the control boat 6, 3 of the first generating means 64 and Output leg 72 may be A first fluid signal is generated at the first fluid signal.

With the generating means 64AK of the embodiment shown in FIG. 3A, the fluid signal of the output leg 40 is The control boat 74G, into which the power flow enters, exits. This causes the power to be communicated to the atmosphere through the port doors 4e-i. Therefore, the fluid signal is NOR It is not sent to line 78 for application to gate 76. N O11, gate 76 The boat 76C into which the power flow enters is deflected and discharged to the output leg 72.

In the generating means 64B of the embodiment illustrated in FIG. 3B, the signal of the output leg 40 is amplified. It is applied to the control boat 79b of the vessel 79 and deflects the boat 79C into which the power flow enters. As a result, a signal is generated on line 84. The signal on line 84 is sent to output leg 72. It is applied to the flip-frog 80 which finally generates the first fluid signal. to this point Although I have not explained this in detail, what you should understand is that the flip-flop 8 The amplifiers 81 and 82 consisting of - operates according to the same principles described above with respect to the Of course, the amplifier 81 ．． The signal to 82 may be applied to the opposite human port than described above, and also to the output port. The force signal may be emitted from the opposite output port.

In the generating means 64C of the embodiment shown in FIG. 3C, the fluid signal of the output leg 40: It is applied to the control boat 90b of the power amplifier 90 and the power flow enters and exits the port 90C. is deflected to power port 90e, thus generating a signal on line 94.

A control port (92a) to which a signal 94 of a bistable flip-flop 92 is applied allows the power to be The boat 92C into which the flow enters is deflected toward the output boat 92d, and the first Generates a fluid signal.

In contrast to the three embodiments of the first generating means 64 described above, what should be noted is that the third Generating means 64B in Figure B is used for its output in order to switch from leg 70 to leg 72. This requires exhalation. On the other hand, the generation means 64A, 64C are used to stop the inhalation. In this case, the output is automatically switched from leg 70 to leg 70.

While in the positive pressure operating mode, the first generating means ε4 generates a first fluid signal on the output leg 72. Therefore, no fluid signal is applied to the demand gas control circuit at output control 70. Figure 1 and As described separately above with respect to each embodiment of the demand gas controller shown in FIG. In the absence of a fluid signal on the output leg 70 of the generating means 64, the suppression of the source means 98 occurs. occurs. In this way, during exhalation, (d) inspiratory gas is applied to the patient. do not have.

Generating means 64 generates a first fluid signal at output leg 72 in response to the sensed positive pressure. When the fluid signal is applied to the breath hold circuit 10 by line 138. the The signal travels along line 138 until it encounters fluid resistance 140. resistance Resistor 140 blocks the path of the fluid signal applied to line 138, thereby The signal travels through fluid path 142. The fluid signal traveling around path 142 is Running the fluid signal along line 138 and into variable capacitance device 132 Close the mushroom exhalation valve 130. The fluid signal is generated when the generating means 64 generates the fluid signal. is continuously applied to variable capacitance device 182 as long as it remains active.

During normal breathing, the generating means 64 causes the variable capacitance device 132 to reach its maximum The output leg 72 stops generating fluid signals for a long time until it is filled to a large capacity. this In this respect, it should be recalled that the generating means 64 detects that the inhalation is detected by the detecting means 26. When informed, it no longer emits a fluid signal at output q72. in this case , the patient is breathing satisfactorily and there are no periods of respiratory arrest.

On the other hand, in abnormal breathing, when the patient is unable to inhale, the generating means 64 outputs the output leg 72. continues to generate fluid signals.

Therefore, the variable capacitance device 132 is inflated to its maximum capacitance. When the power flow input to the NOR gate 134 reaches a pressure that expands the Rubo 9 The output port 134c is switched to the output port 134d by the output port 134a. . In this manner, N0FL gate 134 can be used either alone or in combination. A fluid signal is provided on line 144 that is used to operate various signaling means. generate a number. As shown in FIG. 1, the fluid signal on line 144 is 48, the NOR gate increments each time it switches. This is applied to the linear counter 136a.

Line 144 in turn transfers the fluid signal in line 144 electrically to lines 148 and 150. It is connected to a pressure/electrical switch 146 which converts it into a signal. Line 148 electricity The signal activates the electrocardiogram (ECG) monitor 136C and the voltage on line 148°150. The air signal activates alarm 136b. As mentioned above, alarms are visible and audible. Or it may be both.

Various sizes and types of elastomeric balloons or other suitable devices can be used as variable capacitors. device 132. exercised by the device as an element of its selection. The elongation of the elastomer and the maximum fluid storage capacity of the device are considered. example For example, a breath hold circuit 10 may be configured to indicate that the patient has not inhaled within a 20 second interval. If desired, do not allow NOR gate 134 to trigger the switch for those 20 seconds. The device 132 is selected to accommodate the fluid volume generated by the generating means 64. It will be done. Of course, when the patient reaches zero, the variable capacitance device 132 reaches its maximum capacity. Previously, once inhaled, the device 132 in conjunction with the mushroom valve 130 can be used in the manner described above. Shrinks more quickly.

The display device 158 of the breath hold circuit 10 is displayed to the operator or attending physician. The person's exhalation period can be timed. Display device 158 displays pressure/voltage Similar components in the counter display circuit described above may be used with the air device 152. It works in much the same way as the minutes.

Although the present invention has been described in terms of a preferred embodiment, various modifications may be made without departing from the scope of the invention. It is to be understood that, to the extent not departing from this, the invention is constituted by the present invention. For example, Counters 162 may be connected to lines 120 or 102 alternately.

2. The present invention relates to a breathing apparatus adapted for clinical purposes (e.g. with patients). However, it is understood that it can be applied to other fields as well. For example, the present invention Can be used for gas replenishment or respiratory arrest detection in aviation, underground, and sewage environments. Ru.

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Claims (1)

[Claims] 1. Breathing gas is delivered at the beginning of inhalation and for a small portion of the inhalation period That's how the breathing apparatus works. 2. The process of detecting pressure flow in the breathing system; displaying the duration of the pressure flow; The process of generating a first fluid signal having a certain period of time, the process of generating a first fluid signal having a certain period of time; Step of generating a second fluid signal having a certain period associated with the period of the fluid: Previous applying breathing gas to the patient during a period of time related to the period of the second fluid signal; A method of operating a breathing apparatus, comprising: a controlling stroke; 3. Supplying breathing gas at the beginning of inhalation and during a period that is only a small part of the inhalation period; breathing apparatus. 4. Means for detecting pressure flow in the breathing system: fluidly connected to the detecting means and having a period of time indicative of the period of pressure flow; a first generating means for generating; fluidly connected to said first generating means; A second fluid signal having a certain period related to a period of the first fluid signal according to a predetermined relationship. a second generating means for generating a signal; fluidly connected to the second generating means, and in response to the second fluid signal, the patient for a period of time related to the period of the second fluid signal. source means for controlling the application of breathing gas to; and from said source means; a fluid transport means for transporting the inspired gas to the breathing system. Device Place. 5. said source means supplying respiratory gas for a period of time coinciding with the period of said second fluid signal; The apparatus of claim 4 for providing. 6. said source means for a period of time commensurate with the absence of said second fluid signal therein; 5. Apparatus according to claim 4 for providing breathing gas. 7. Means for detecting pressure flow in the breathing system, in which case the means comprises at least one a laminar flow stoichiometric fluid device; in fluid communication with the sensing means; means for generating a fluid signal having a period of time indicative of the period of said pressure flow; fluidly connected to the generating means and responsive to the fluid signal; a software for controlling the application of breathing gas to the breathing system for a period of time related to a period of time; breathing apparatus, consisting of 8. Step of detecting pressure flow in the breathing system; first step associated with the pressure flow. generating a fluid signal; applying the first fluid signal to a variable capacitance device; during which the device continuously applies the first fluid signal for a predetermined period of time. A predetermined maximum capacity for storing a fluid volume approximately equal to a certain fluid volume caused by a process of releasing the variable capacitance in relation to the pressure flow; The variable capacitance is increased by continuously applying the first fluid signal for a period longer than the period prepared for the purpose. When the pressure developed in the capacitance device exceeds the maximum capacity of the variable capacitance device, Activation of a breathing apparatus for detecting when breathing stops, comprising the step of activating a signaling means. Method. 9. Means for detecting pressure flow in the breathing system; and transmitting a first fluid signal associated with the pressure flow at a first output boat. generating means; a variable capacitance fluidly connected to a first output of the generating means; a device, wherein the device generates a signal by continuously generating and applying the first fluid signal for a predetermined period of time; has a default maximum capacity for storing a fluid volume approximately equal to the fluid volume that is stored. Applicable evacuation means fluidly connected to the variable capacitance device, wherein the means is connected to the first output. Robo! - generating the first fluid signal, and the first generating means is connected to the first output port; open when not generating the first fluid signal; and the variable capacitance device; 2 pressure sensitive signaling means, in which case the means is for a period of time greater than a predetermined time; The pressure developed in the variable capacitance means by continuous application of the first fluid signal to Because it is adapted for operation when the maximum capacity of the variable capacitance device is exceeded. A breathing device that detects when breathing stops.