RU2747255C1 - Artificial lung ventilation device - Google Patents

Abstract

FIELD: medical technology.SUBSTANCE: invention relates to medical technology, namely to an artificial lung ventilation device designed for simultaneous ventilation of up to n patients. The device includes a stationary stator equipped with n evenly distributed along the circle windows of angular magnitude γswith n inhalation tubes connected to them for each of the n patients. The device has a rotor made with the possibility of sliding along its inner surface, containing a compressed oxygen-air mixture under excessive pressure, equipped with mn+1 or mn-1 windows evenly distributed along the circle for direct or reverse ventilation, respectively, of the angular value γr=nδ/(1+1/α)-γs, where m is the multiplication factor - any natural number: m=1, 2, 3, … , δ - a device characteristic that depends only on the numbers m and n: δ=2π/n/(mn+1) - for direct ventilation, δ=2π/n/(mn - 1) - for reverse ventilation, α - the ratio of the duration of inhalation and exhalation. In this case, the rotor speed is f=ν/(mn+1) for direct ventilation, when the directions of rotation of the rotor and the supply of oxygen-air mixture coincide, and f=ν/(mn-1) - for the reverse ventilation, when these directions are opposite, where ν is the required respiratory rate. The stator is made in the form of a compression chamber-receiver, connected to the lower open end of the rotor. The upper end of the rotor is closed by a bearing circular plate - a power element that transmits torque to the rotor from the drive shaft, which rotates at a low frequency f, compared to the breathing frequency ν. The oxygen-air mixture from the receiver can enter the inhalation tubes only when the mn+1 or mn-1 windows of the rotor and n windows of the stator overlap, these stator windows on its outer surface are equipped with flaps regulating the height of these windows. The n inhalation breathing tubes connected to the n windows of the stator, individually designed for n patients, are equipped at the other ends with non-reversible valves designed to allow patients to exhale into the atmosphere.EFFECT: technical result is the expansion of functionality, simplification of the design and increasing the reliability of the device.2 cl, 5 dwg

Description

The invention relates to medicine, namely to mechanical ventilation of the respiratory system of patients in the absence of available ventilators during outbreaks of pandemics and other emergencies. A mechanical ventilation apparatus (IVL) is a very expensive high-tech medical equipment designed for forced supply of an air mixture containing oxygen to the lungs of patients in order to saturate the blood with oxygen and remove carbon dioxide from them / Tsarenko S.V. Practical course of mechanical ventilation. Moscow, 2007; Burlakov R.I., Galperin Yu.Sh., Yurevich V.M. Artificial ventilation of the lungs (principles, methods, equipment). Moscow, 1986; Zilber A.P., Bogoyavlensky I.F., Galperin Yu.Sh., Uvarov B.S. Artificial respiration. Great Medical Encyclopedia, vol. 9. Moscow, 1978; Goryachev A.S., Savin I.A. Fundamentals of mechanical ventilation. A guide for doctors. Moscow, 2019; Satishur O.E. Mechanical ventilation of the lungs. Moscow, 2006; Kassil V.L., Vyzhigina M.A., Leskin G.S. Artificial and assisted ventilation of the lungs Moscow, 2004; Lebedinsky K.M., Mazurok V.A., Nefedov A.V. Respiratory support basics. SPb, 2008; Chang D.W. Clinical Application of Mechanical Ventilation. 3rd Edition, 2006; Hess D.R., Kacmarek R.M. Essentials of Mechanical Ventilation. 2nd Edition, 2002; Papadakos P. J., Lachmann B. Mechanical Ventilation: Clinical Applications and Pathophysiology, 2008; Pilbeam S.P., Cairo J.M. Mechanical Ventilation: Physiological and Clinical Applications. 4th Edition, 2006; Tobin M.J. Principles and Practice of Mechanical Ventilation. 3rd edition, McGraw-Hill, 2013; MacIntyre N.R., Branson R.D. Mechanical ventilation. 2nd edition, Saunders Elsevier, 2009; Chatbum R.L. Fundamentals of Mechanical Ventilation: A Short Course on the Theory and Application of Mechanical Ventilators. 2nd Edition, 2004 /.

The aim of the invention is to create a very inexpensive, simple, reliable ventilator operating in the forced breathing mode in time, designed to compensate for the sudden lack of standard equipment in catastrophic pandemics leading to mass respiratory failure of the population. The main feature of the proposed device is the ability to simultaneously connect several patients to one ventilator at once, both without the risk of cross-contamination or contamination of the device itself.

Devices that allow to successfully conduct mechanical ventilation simultaneously to several patients were urgently created in 2020 in the Russian Federation due to the presence of bactericidal filters that provide 99.9% protection against bacteria and viruses / Electronic resource https://www.interfax.ru/russia/ 701318 /. The state corporation Rostec was tasked with considering the possibility of developing prototypes of disposable sets of lung ventilation circuits for two, three or four patients, similar to foreign ones. The development is a system of disposable breathing circuits, adapters and filters for ventilation of the lungs of up to four patients, excluding cross-contamination between them / Electronic resource https://tass.ru/ekonomika/8104865/.

The creation of inexpensive "multi-seat" ventilators is a forced measure, in the event of a "worst-case scenario" of a mass shortage of expensive equipment, such as modern ventilators. The ventilator adjusts for lung volume, airway resistance, and lung and chest compliance. Of course, patients with approximately the same lung volume should be connected to the same ventilator, guided by the “do no harm” principle. For more fine tuning, there are stator window dampers in front of the inspiratory hose, which also function as a plug for the breathing circuit to shut it off in the absence of a patient.

The closest to the present invention in technical essence is a multiplier-spool ventilator adopted as a prototype / Sviyazheninov E.D. Multiplier-spool ventilator. Patent for invention of the Russian Federation No. 2735759. Priority 05/12/2020 /. The prototype device includes a stationary stator equipped with n windows evenly distributed around the circumference through which breathing circuits supply the oxygen-air mixture to n patients. A uniformly rotating hollow rotor slowly slides along the inner surface of the stator, containing an oxygen-air mixture under the excess pressure required for mechanical ventilation of the lungs, equipped with mn + 1 or mn-1 evenly distributed around the circumference of the windows for direct or reverse ventilation, respectively, where m is the multiplication coefficient - any natural number: m = 1, 2, 3,…. Due to this, the rotor speed is mn + 1 or mn-1 times less than the required respiratory rate of patients. This is absolutely necessary to suppress the power of the sliding frictional forces of the rotor along the inner surface of the stator and heat generation. Portions of the oxygen-air mixture through n breathing circuits located around the circumference of the ventilator are delivered to n patients. In the version of the device with mn + 1 rotor windows, the sequence of operation of the stator breathing circuits coincides with the direction of rotation of the rotor - direct ventilation. In the variant of the device with mn-1 rotor windows, the sequence of operation of the stator breathing circuits is opposite to the direction of rotation of the rotor - reverse ventilation. The rotary spool acts as a sliding valve - the simplest, most reliable and inexpensive device. In contrast to the reciprocating movements traditionally used in spool devices, uniform rotation is completely devoid of their disadvantages: the occurrence of inertial forces and sticking zones of the spool in the vicinity of its zero speeds.

In the prototype, both valves of the breathing circuit - inhalation and exhalation - are active because they are controlled by a rotating rotor. Therefore, expiratory breathing tubes are routed to the atmospheric section of the ventilator, loading the germicidal filters to avoid the risk of contamination of the ventilator. In the proposed device, this problem is completely solved.

This problem is solved by the fact that the inhalation valves are active, and the exhalation valves are passive: the inhalation tubes are equipped with non-reversible valves. When inhaling, portions of the oxygen-air mixture from the ventilator through the inhalation tubes enter the patient's airways, and exhalation from the non-reversible valves immediately goes into the atmosphere, at a distance from the ventilator, with a given frequency and ratio of inhalation-exhalation durations. Thus, the exhalation mixture does not flow back into the hose - there is no "reverse". There is no need for an exhalation hose for the breathing circuit, which in this version becomes a single hose with a non-reversing valve box at the end. The patient can inhale spontaneously from the atmosphere through the expiratory opening of the non-reversing valve. The valve box includes a safety valve that opens at a selected threshold pressure (for example, 50 cm of water column, in order to avoid barotrauma of the patient) and "releases" excess pressure into the atmosphere. A PEEP (positive end-expiratory pressure) valve can be connected to the expiratory opening of the valve box. In addition to expanding functionality, the design of the device is simplified, its reliability is increased and the cost is reduced.

The stated essence is illustrated by drawings, where in FIG. 1 shows a longitudinal section of the ventilator, FIG. 2 - cross-sections along the section A-A of the ventilator for four patients, n = 4, for successive multiplication factors m = 1, 2, 3, ..., for direct ventilation, in Fig. 3 - cross sections along the section A-A of the ventilator for six patients, n = 6, for successive multiplication factors m = 1, 2, 3, ..., for reverse ventilation, in Fig. 4 - time scans of the overlap area S of four stator windows, n = 4, connected to 4 inhalation tubes, and rotor windows, which function as sliding valves, in Fig. 5 is a time base on the same time scale of the airway pressures P in four patients, n = 4, for an exemplary 1: 3 inspiratory-expiratory ratio.

Ventilator diagram

The artificial lung ventilation apparatus (Fig. 1) consists of a rotor 1, the lateral surface of which is equipped with windows 2 evenly distributed around the circumference mn + 1 or mn-1 for direct (Fig. 2) or reverse (Fig. 3) ventilation, respectively, where m - multiplier coefficient - any natural number: m = 1, 2, 3,…, n - the number of respiratory circuits extending from the ventilator to n patients and evenly spaced around its perimeter. The rotor 1 rotates inside the stator 3, the lateral surface of which is equipped with n uniformly distributed around the circumference windows 4 of the angular value γ, with n breathing circuits connected to them. The stator windows on its outer surface are equipped with axially moving dampers 5 adjusting the height of these windows, up to a complete plug of the windows to turn off any breathing circuits in the absence of some of the n patients. Each breathing circuit consists of a tube, or hose, inhalation 6 and a non-reversing valve 7.

Thus, n inhalation tubes 6 are connected with one end to the corresponding n windows of the stator 4, and the other with n non-reversible valves 7, which provide n patients with an oxygen-air mixture through the patient's nozzles 8 through endotracheal tubes for invasive ventilation and face masks for non-invasive ventilation.

The non-reversing valve 7, or the valve box, is designed to direct the inhaled and exhaled air flows through different channels and works as follows / Tsarenko S.V. Practical course of mechanical ventilation. Moscow, 2007; Burlakov R.I., Galperin Yu.Sh., Yurevich V.M. Artificial ventilation of the lungs (principles, methods, equipment). Moscow, 1986; Zilber A.P., Bogoyavlensky I.F., Galperin Yu.Sh., Uvarov B.S. Artificial respiration. Great Medical Encyclopedia, vol. 9. Moscow, 1978 /. During artificial inhalation, the oxygen-air mixture under pressure through the hose 6 and the valve box 7 from the nozzle 8 enters the patient's respiratory tract. During artificial exhalation, the increased pressure in front of the valve box 7 disappears, and the exhaust air from the patient's respiratory tract through the outlet 9 of the non-reversing valve 6 goes into the atmosphere. Thus, the exhalation mixture does not flow back into the inhalation hose 6 - there is no "reverse". The patient can make a spontaneous inhalation from the atmosphere through the exhalation branch pipe 9. The valve box 7 includes a safety valve that opens at a certain threshold pressure and "releases" the excess pressure into the atmosphere. An end-expiratory positive pressure valve can be connected to the exhalation port of the valve housing 9.

In the axial direction (Fig. 1), the rotor 1 is a hollow rotating drum. One end surface of the rotor is equipped with a bearing circular plate 10 - a power element that transmits torque to the rotor 1 from the drive shaft 11 rotating at a low frequency f compared to the breathing frequency ν. The other end of the rotor is open. With this open end, the hollow rotor communicates with the compression chamber-receiver 12, a storage tank of the compressed oxygen-air mixture intended for forced supply to patients. The compression chamber-receiver is large enough to smooth out pressure fluctuations caused by the pulsating supply of the oxygen-air mixture and its intermittent flow. The lateral outer surface of the rotor slides slowly over the inner surface of the stator with low friction. The windows of the rotor 2 periodically overlap the windows of the stator 4, providing access to the oxygen-air mixture into the inhalation hoses 6 under the required pressure, which flows further into the non-reversing valve 7 and through the patient's nozzle 8 into his airways. Exhaust air containing carbon dioxide is discharged through the exhalation port 9.

Let it be required to create a respiratory rate v with the ratio of the durations of inhalation and exhalation α = a / b.

Then the rotor speed should be f = ν / (mn + 1) or f = ν / (mn-1) - for the corresponding number of windows mn + 1 or mn-1 on its lateral surface. In the first case, the sequence of operation of the breathing circuits coincides with the direction of rotation of the rotor - forward ventilation, and in the second - opposite to it - reverse ventilation. The rotor windows must have an angular value γ _r = nδ / (1 + 1 / α) -γ _s , where α is the ratio of inhalation and exhalation, and γ _s , as indicated above, is the angular value of the stator windows.

How the ventilator works

The principle of operation of the ventilator is that a slowly rotating rotor quickly turns on (inspiratory period) and turns off (expiratory period) the supply of oxygen-air mixture to each patient. Semi-open single-hose breathing circuits are used: one end of the breathing tubes is connected to the source of the oxygen-air mixture, the other to the non-reversing valve. For the period of inhalation, the sliding valves of the rotor open the hose to the compression chamber-receiver, and the oxygen-air mixture through this hose enters the patient's respiratory tract, for the period of exhalation, it is closed, and the spent air mixture from the outlet of the non-reversing valve escapes into the atmosphere, i.e. e. the expiratory mixture does not flow back into the hose.

To illustrate the principle of operation of the sliding valves of the rotary valve and to analyze the inspiratory-expiratory switchings, FIGS. 2 for direct ventilation and FIG. 3 - for reverse. FIG. 4, 5 show the time sweep of the opening area of the stator windows S and the resulting pressures in the airways of patients P for the ratio of the durations of inhalation-exhalation α = a / b = 1/3. Here, for the sake of clarity, the direct ventilation mode is shown for a ventilator designed for four patients, i.e. with 4 breathing circuits, n = 4. Reverse ventilation and / or a different number of circuits work in exactly the same way.

The direction of rotation of the rotor 1 is shown by a circular arrow marked with the letter f (Figs. 2, 3). Further, f will also denote the rotational speed of the rotor 1. The angular rotational speed of the rotor 1 is denoted by ω and is ω = 2πf.

The front edges of the windows of the rotor 1 in the course of its rotation are denoted by rotating beams r _i (solid lines), and the front edges of the stator windows 4 - by fixed beams s _j (dashed lines), with indices i, j corresponding to the ordinal numbers of the rotor windows 2 and stator windows four.

A key feature of the proposed circuit, as seen in FIG. 2, 3 is that:

1. Consecutive angles between the rays r _i , s _i , i = 2, 3, 4 ... are (i-1) δ, i.e. form a natural sequence (1, 2, 3,…) δ.

2. The rotating device has an axial symmetry of mn + 1 or mn-1 order, i. E. when it is rotated around the axis of rotation by an angle of 2π / (mn + 1) or an angle of 2π / (mn-1), respectively, it coincides with itself.

It is these two circumstances that effectively ensure the full cycle of uniform sequential operation of all n breathing circuits, not for the full period of rotation of the spool rotor 1, but only for mn + 1 or mn-1 part of it.

The device works as follows. The oxygen-air mixture from the compression chamber-receiver 12 can enter the inhalation tubes 6 only when the windows of the rotor 2 and the stator 4 overlap - let's call this opening, or turning on, the stator windows. Otherwise, the stator windows are closed or turned off. When the rotor 1 rotates, the stator windows are opened (turned on) and closed (turned off) in turn, adjusting the inhalation phases (Figs. 2, 3). The time sweeps for the opening area of the stator windows S connected to the inspiratory tubes and the pressures P in the patient's airways for the ratio of the inhalation-exhalation cycles α = a / b = 1/3 are shown in Fig. 4, 5, respectively.

Let the stator window I turn on at the initial moment of time (Fig. 2). The oxygen-air mixture under the action of a pressure gradient begins to flow from the compression chamber-receiver 12 through the inhalation tube 6 and the valve box 7 to the patient's nozzle 8 and then to his respiratory tract. The time-varying area S of the opening stator window as a function of time is the trapezoid shown in FIG. 4. When the stator window is turned off, the oxygen-air mixture does not enter the inhalation tube 6, and the exhalation phase begins. The exhaust air under the influence of the pressure drop from the patient's respiratory tract through the nozzle 8 and the exhalation nozzle 9 of the non-reversing valve 7 is released into the atmosphere.

Such a time law of the area of opening of the stator windows (Fig. 4) corresponds to a well-defined time base of the pressure in the patient's airways P, on the same time scale shown in Fig. 5. This is a rapid increase in positive excess pressure, slowing down during filling of the lungs, followed by a drop in pressure after the start of exhalation. For each breathing circuit, for example the first one marked in FIG. 4, 5 in Roman numeral I, the inspiration phase begins from the zero point in time and ends with the moment of dimensionless time (ω / δ) t = 1. Further, from the moment of time (ω / δ) t = 1 to (ω / δ) t = 4, the exhalation phase lasts. The process is periodic and repeats with a period (ω / δ) T = 4. The work of each next breathing circuit lags behind in phase by (ω / δ) t = 1 from the previous one. Time scans of the area of opening of the stator windows S of pressures P for all n breathing circuits, n = 4, from I to IV, are shown in Fig. 4, 5, respectively.

при прямой вентиляции в направлении, совпадающем с направлением вращения ротора, или на угол

при обратной вентиляции в направлении, противоположном направлению вращения ротора. Физический смысл угла δ следующий: при γ=δ реализуется непрерывный режим работы аппарата ИВЛ, в котором периоды вдоха соседних контуров не перекрываются, а непрерывно следуют друг за другом: в момент окончания периода вдоха какого-либо контура начинается период вдоха соседнего дыхательного контура. Количественные соотношения, характеризующие непрерывный режим, будут приведены ниже.When the ventilator is operating, switching from inhalation to exhalation of the breathing circuit of each patient occurs when the rotor is turned through an angle γ = γ _r + γ _s . The inhalation of each next patient relative to the previous one begins when the rotor is turned at an angle

with direct ventilation in the direction coinciding with the direction of rotation of the rotor, or at an angle

with reverse ventilation in the opposite direction to the direction of rotation of the rotor. The physical meaning of the angle δ is as follows: when γ = δ, a continuous mode of operation of the ventilator is realized, in which the periods of inhalation of adjacent circuits do not overlap, but continuously follow each other: at the end of the inhalation period of any circuit, the inhalation period of the adjacent breathing circuit begins. The quantitative ratios characterizing the continuous mode will be given below.

Corresponding time bases for other ratios of inspiratory-expiratory duration, other than 1/3, can be constructed in a similar way.

Technical characteristics of the ventilator. Summary of basic formulas

The main characteristics of ventilators are the respiratory rate ν and the ratio of the durations of inspiration-expiration α = a / b on each breathing circuit. Note that the ratio of the durations of inhalation-exhalation a / b in the English-language literature is traditionally denoted by i / e (from the English "inspiration, inhalation" - inhalation, "expiration, exhalation" - exhalation).

The respiratory rate v is determined exclusively by the rotor speed f:

ν = (mn + 1) f - for direct ventilation and

ν = (mn-1) f - for inverse.

The ratio of the durations of inhalation-exhalation α = a / b is determined by the design angle γ, universal, depending only on the numbers m, n, but not on the design parameters, the angle δ and the number of stator windows n equal to the number of breathing circuits of the ventilator:

α = a / b = γ / (nδ-γ),

1 / α = b / a = n δ / γ-1,

where γ = γ _r + γ _s is the total angular value of the rotor and stator windows,

δ = 2π / n / (mn + 1) - for direct ventilation,

δ = 2π / n / (mn-1) - for inverse,

whence follows the formula for choosing the constructive angle γ = γ _r + γ _s :

γ = nδ / (1 + 1 / δ).

The closed state time τ (the time of overlapping the rotor and stator windows) is:

τ = 1 / (1 + 1 / α) / ν = (γ / δ) / (nν).

For the particular case of continuous γ = δ ventilation we have:

τ = 1 / (nν).

An example of calculating a ventilator

So, the main characteristics of ventilators are the respiratory rate v and the ratio of the durations of inspiration-expiration α = a / b on each patient's breathing circuit.

The respiration rate ν is determined by the rotor speed f, which allows a simple change in the operating mode:

ν = (mn + 1) f - for direct ventilation and

ν = (mn-1) f - for inverse.

The ratio of the durations of inhalation-exhalation α = a / b is determined by the design angle γ, universal, that is, independent of the design angles, but depending only on the numbers m, n by the angle δ and the number of stator breathing circuits n:

where γ = γ _r + γ _s is the total angular value of the rotor and stator windows,

δ = 2π / n / (mn + 1) - for direct ventilation,

δ = 2π / n / (mn-1) - for inverse.

An example of calculating the direct ventilation mode when the sequence of the breathing circuits coincides with the direction of rotation of the rotor.

As a first example, we calculate the direct ventilation scheme for a 4-circuit stator, n = 4, by means of mn + 1-window rotor, for successive values of the multiplication factor m = 1, 2, 3 (Fig. 2). Let the required respiratory rate on each of the respiratory circuits be 20 beats per minute, or ν = .33 Hz, i.e. breathing period - 3 s. Then the period of rotation T and the frequency of rotation f of the rotor will be:

An example of calculating the reverse ventilation mode when the sequence of the breathing circuits is opposite to the direction of rotation of the rotor.

As a second example, we calculate the reverse ventilation scheme for a 6-circuit stator, n = 6, by means of an mn-1-windowed rotor, for successive values of the multiplier coefficient m = 1, 2, 3 (Fig. 3). Let the required breathing rate on each of the stator breathing circuits still be 20 cycles per minute, or ν = .33 Hz, the breathing period is 3 s. Then the period of rotation T and the frequency of rotation f of the rotor will be:

General conclusion. Considering that for a single-window rotor the rotation period would be 3 s, we see that for a multiplier rotor the rotation period increases by an order of magnitude or more. Thus, the effect of respiration rate multiplication is clearly visible, which manifests itself in mn + 1 or mn-1-fold decrease in the required rotational speeds of the multi-window rotor. This is due to the fact that the entire rotation time of the multi-window rotor is effectively spent on its main function - the sequential supply of the oxygen-air mixture to the stator windows for patients, and the unproductive idle rotation of the rotor just to turn its single window towards the stator windows is completely excluded.

Note that the above tables for a 4-window stator with direct ventilation and 6-window with reverse ventilation are very similar. This confirms that both direct mn + 1 and reverse mn-1 ventilation, where n is the number of breathing circuits equal to the number of stator windows, m = 1, 2, 3, ... is the multiplication factor, mn + 1 and mn-1 are the number of rotor windows have the same efficiency. Therefore, throughout the text, they are mentioned in parallel.

When n is small, for example, 4, as in the first example, it is more advantageous to use direct ventilation, when n is large, for example, 6, as in the second example, the reverse, because the structural width of the rotor windows is approximately the same.

The main thing is that by increasing the multiplication coefficient m, it is possible to infinitely reduce the sliding speed of the rotor along the inner surface of the stator in order to suppress the power of friction forces and heat generation, due to which rotary spools are still of little use in mechanical engineering compared to reciprocating, despite their great simplicity , reliability, efficiency, absence of inertial loads and rotor sticking zones in the vicinity of their zero speeds.

This is how the multiplier principle works, meaning that a low rotor speed results in a high speed of the stator response wave. An additional "bonus" is the ability to change the direction of the stator wave to the opposite direction of the rotor rotation during reverse ventilation.

The ratio of the durations of inspiration-expiration α = a / b:

where γ = γ _r + γ _s is the total angular value of the rotor and stator windows, δ = 2π / n / (mn + 1) - for direct ventilation, δ - 2π / n / (mn-1) - for reverse ventilation, is determined by the choice constructive angle γ:

Let α = a / b = 1. Then γ = nδ / 2. For n = 4 γ = 25, and for n = 6-γ = 3δ.

With an increase in the required ratio of the durations of inhalation-exhalation α = a / b, the design angle γ = γ _r + γ _s increases, limiting itself to the upper limit γ = nδ = 4δ. With a decrease in the ratio of the durations of inhalation-exhalation α = a / b, the values of the constructive angle γ = γ _r + γ _s decrease.

For continuous ventilation γ = δ, when the periods of breaths of adjacent circuits do not overlap, but continuously follow each other, namely, this case is shown in Fig. 6, the ratio is true:

At the same time, for n-contour ventilators serving simultaneously n patients at once, n = 2, 3, 4, ... continuous ventilation gives very important values of the ratio of inhalation-exhalation durations α = a / b: α = 1, 1 / 2, 1/3, ...

Conclusions. Technical result

1. An inexpensive, simple, reliable ventilator has been proposed, designed for the simultaneous connection of several patients at once, both without the risk of their cross-contamination or contamination of the apparatus itself.

2. The device can be relevant in case of catastrophic pandemics leading to mass respiratory failure of the population in order to make up for a sudden shortage of very expensive standard equipment.

3. Due to the multiplier effect, the distribution of the oxygen-air mixture is carried out by the simplest and most reliable slow-rotating sliding valve spools that provide the required breathing rates. At low speeds of rotation of the rotors, the power of frictional forces and heat generation are suppressed, which determines the functionality of the device. The optimal mode of the ventilator with a rotating multi-window rotor inside the multi-window stator has been achieved according to the criterion of serving several patients at once.

4. Varying the breathing rate is done by simply changing the rotor speed. The ratio of the durations of inspiration and expiration is determined by the choice of the total angular value of the rotor and stator windows.

5. The multiplier rotating device is especially effective for the implementation of high-frequency ventilation when other means are difficult.

References

1. Tsarenko SV. Practical course of mechanical ventilation. Moscow, 2007.

2. Burlakov R.I., Galperin Yu.Sh., Yurevich V.M. Artificial ventilation of the lungs (principles, methods, equipment). Moscow, 1986.

3. Zilber AP, Bogoyavlensky IF, Halperin Yu.Sh., Uvarov BS Artificial respiration. Great Medical Encyclopedia, vol. 9.Moscow, 1978.

4. Goryachev A.S., Savin I.A. Fundamentals of mechanical ventilation. A guide for doctors. Moscow, 2019.

5. Satishur O.E. Mechanical ventilation of the lungs. Moscow, 2006.

6. Kassil V.L., Vyzhigina M.A., Leskin G.S. Artificial and assisted ventilation of the lungs. Moscow, 2004.

7. Lebedinsky K.M., Mazurok V.A., Nefedov A.V. Respiratory support basics. SPb, 2008.

8. Chang D.W. Clinical Application of Mechanical Ventilation. 3rd Edition, 2006.

9. Hess D.R., Kacmarek R.M. Essentials of Mechanical Ventilation. 2nd Edition, 2002.

10. Papadakos P. J., Lachmann B. Mechanical Ventilation: Clinical Applications and Pathophysiology. 2008.

11. Pilbeam S.P., Cairo J.M. Mechanical Ventilation: Physiological and Clinical Applications. 4th Edition, 2006.

12. Tobin M.J. Principles and Practice of Mechanical Ventilation. 3rd edition, McGraw-Hill, 2013.

13. MacIntyre N.R., Branson R.D. Mechanical ventilation. 2nd edition, Saunders Elsevier, 2009.

14. Chatburn R.L. Fundamentals of Mechanical Ventilation: A Short Course on the Theory and Application of Mechanical Ventilators. 2nd Edition, 2004.

15. Electronic resource https://www.interfax.ru/russia/701318.

16. Electronic resource https://tass.ru/ekonomika/8104865.

17. Sviyazheninov E. D. Multiplier-spool ventilator. Patent for invention of the Russian Federation No. 2735759. Priority 05/12/2020 (prototype).

Claims (2)

1. A device for artificial lung ventilation, designed for simultaneous ventilation of up to n patients, including a fixed stator, equipped with n uniformly distributed around the circumference windows of the angular value γ _s with n breathing tubes connected to them for each of n patients, and made with the ability to slide along its inner surface is a rotor containing a compressed oxygen-air mixture under excess pressure, equipped with mn + 1 or mn-1 windows evenly distributed around the circumference for direct or reverse ventilation, respectively, the angular value γ _r = nδ / (1 + 1 / α) - γ _s , where m is the multiplication coefficient - any natural number: m = 1, 2, 3, ..., δ is the device characteristic depending only on the numbers m and n: δ = 2π / n / (mn + 1) - for direct ventilation , δ = 2π / n / (mn-1) - for reverse, α is the ratio of the durations of inhalation and exhalation, while the rotor speed is f = ν / (mn + 1) for direct ventilation, when the directions of rotation of the rotor and oxygen supply -air mixtures coincide and f = ν / (mn-1) - for the reverse, when these directions are opposite, where ν is the required breathing frequency, characterized in that the stator is made in the form of a compression chamber-receiver communicated with the lower open end of the rotor, then as the upper end of the rotor is closed with a circular bearing plate - a power element that transfers torque to the rotor from the drive shaft rotating at a low frequency f, compared to the breathing rate ν, the oxygen-air mixture from the receiver can enter the inhalation tubes only with mutual overlap mn + 1 or mn-1 rotor windows and n stator windows, these stator windows on its outer surface are equipped with dampers adjusting the height of these windows, and n breathing tubes connected to n stator windows, individually designed for n patients, are equipped with non-reversing valves at the other ends, made with the possibility of exhalation of patients into the atmosphere. 2. The artificial lung ventilation apparatus according to claim 1, characterized in that the flaps adjusting the height of the stator windows are made with the possibility of a complete plug in cases of non-use of any of the n windows of the stator and the corresponding breathing tubes due to ventilation of the number of patients less than n.

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