RESPIRATOR DEVICE PARTICULARLY FOR USE IN PERINATAL MEDICINE

Abstract: A respirator device especially for the respiratory treatment of new-born and inmate infants and for their adaptation to natural breathing. The device comprises oxygen and air ducts, means for adjusting the composition, temperature, humidity and other parameters of the gas mixture, a patient junction and pressure adjusting valve means coupled to the junction shunting the gas flow in the junction in such a way that the gas pressure being positive both in expiration and inspiration. The respiration demand of the patient is sensed by a means responsive to pressure-drops which controls a starting signal generator and a beat generator. The beat generator controls the valve means. The device can be adjusted to controlled respiration, controlled assisted respiration, inspected and assisted respiration and continuous positive airway pressure modes, whereby it can be adapted to various respiratory diseases. In the inspecting modes a respiration stoppage detector senses the spontaneous inspirations and in response to a stoppage exceeding a predetermined waiting period performs controlled respiration for a given period of time and starts an alarm.

Description: RESPIRATOR DEVICE PARTICULARLY FOR USE IN PERINATAL MEDICINE Field of the Invention The invention relates to a respirator device intended both for controlled breathing of new-born and premature infants or of laboratory animals and for making the infants to adapt to natural breathing, which device can be used in hospital wards as well as during transportation. The respirator comprises respective oxygen and air receiving ducts, means, for adjusting the composition of the oxygen-air mixture, a conduit for transporting the mixture, a patient junction coupled to the conduit, a respiratory beat generator and a pressure adjusting valve means controlled by the beat generator. Background Art In the field of perinatal medicine there are a large number of diseases in which controlled respiration is required due to the lack or in¬ sufficiency of breathing. In L -a significant part of cases requiring such respiration the problem is caused by some kinds of pulmonary malfunction, how- ever, certain other types of diseases (e.g. para¬ lysis of*the breathing centre, etc.) also require controlled respiration. Of the respiratory problems of new-born and premature infants the -idiopathical distress syndrome has a high incidence and it forms a major factor in perinatal mortality. The controlled respiration raises in perinatal medicine a number of special demands which are different from normal respiratory practice. For that reason the miniaturization of conventional respiratory devices can not solve the specific problems of perinatal respiratory diseases. Although there are already a number of respirator devices designed particularly for use in perinatal medicine, everyday practice has -shown that they could not solve in general the problems in this particular field and they proved to be useful in comparatively narrow fields of indications only. The handling of pneumatically controlled respirators designed for perinatal medicine is often inconvenient and such respirators can not be used, for the treatment of a number of respiratory problems. For example one problem connected with such respirators lies in that the pressure of the expirated gas can not be adjusted to the required values. According to an other problem in the ex- pirating periods pressures below the athmospheric value might take place i.e. the respiration with continuous positive pressure and the respiration with alternating positive pressure can not be implemented, although such kinds of respiration are considered to be necessary for the repiratory treatment of new-born infants. The above summarized problems are also connected with respirators controlled electronically, because in such respirators the possibility of adjusting the pressure of expirated gas below the atmospheric value is also not excluded. Apart from these main problems conventional respirators do not meet the complex requirements of perinatal respiration when their other facilities like handling capabilities, adjustability and the performance in various breathing modes are considered. The practice in perinatal respiratorical therapy necessitates that the mode of respiration should be brought in correspondence with the type of the actual respiratory problem. That kinds of respirator devices are required which can provide for a controlled mechanical respiration with alternat ing positive pressure if the lack or insufficiency of spontaneous breathing is detected. This can be effected by an atmospheric pressure at the ending phase of the expiration, or by adjusting a slight positive pressure at the end of the expiration. In many respiratory disturbances it is required that the spontaneously breathing new-born or inmate baby can breath from a continuously streaming oxygen-air mixture with positive pressure. Object of the invention The object of the invention is to provide a respirator device which can meet the complex demands of perinatal respiration and which can be capable of providing respiration in a perinatal ward or, if it is required, during transportation. The respirator device -should have various modes of operation that enable, the therapy of respiratory problems of new-born and inmate infants with different grave and origin including t-he specific perinatal diseases like the idiopathic respiratory distress syndrome, as well gs the device should be able to make the baby leave off- respiratory treatment under inspected breathing. Summary of the Invention According to the invention a respirator device has been provided, especially for the respiratory treatment of new-born and inmate infants which comprises respective oxygen and air receiving ducts, means for adjusting the composition of the oxygen-air mixture, a conduit for transporting the mixture, a patient junction coupled to the conduit, a beat generator for determining the rythm of breathing and a pressure adjusting valve means controlled by the output of the beat generator, in .which according to the invention the respirator comprises a respira¬ tion demand detector with an input coupled to the patient junction and capable of detecting the pressure drop caused by the air intake of the patient during the expiration period of the device, a starting signal generator which in response to the detected pressure drop generates a corresponding starting pulse, a mode controller for adjusting the operational mode according to the actual requirement of the treatment, the beat generator comprises a generator unit provided with respective control inputs for the selection of continuous, triggered and r ' etrigger- ed modes of signal generation, the mode controller is used to couple the required one of these inputs to the output of the starting signal generator, and the pressure adjusting valve means is coupled to the patient junction and providing adjustable positive ΪSUR O.'. pressures both in inspiration and expiration at the junction by the controlled release of the oxygen-air mixture in the atmosphere. In a preferable embodiment the output of the starting signal generator is coupled to the input of a respiration stoppage detector for providing an appropriate signal when no' output pulse is received from the starting signal generation within a pre¬ determined period of time, and this signal is coupled by the mode controller to the beat generator. The respirator device according to the in¬ vention can be used in four basic modes of operation i. e. controlled respiration for use in the absence of spontaneous breathing; controlled assisted respir- ation intended for use in the occurrence of repeated spontaneous breathing; inspected and assisted respir¬ ation which can be used after the formation of sufficient spontaneous breathing; and inspected continuous positive airway pressure mode for use in respiratory therapy. The invention is based on the particular way of watching the spontaneous inspiration of the patient and on the specific reaction generated in response thereto. The watching operation is carried out by the respiration demand detector made preferably of a pressure difference - capacitanceconverter utiliz¬ ing a metal membrane, in which a reference pressure is. established in accordance 'with the preadjusted expiration pressure, The respirator device according to the invention is capable of providing the new-born infant suffering from a respiratory disease with the required amount of streaming ionized gas lead to its trachea which gas is fresh, having adjustable composition, humidity and inspiration and expiration pressure with controlle rate and duty cycle, and owing to its various ad- justable modes of operation it provides a possibility for making the patient leave off instrumental respir¬ ation in such a way that a smoo.th transition is pro¬ vided towards the normal breathing in the atmospheric air. Description of the Drawings Fig. 1 shows the general block diagram of the respiratory apparatus according to the invention; Fig. 2 shows the respiration demand detector in sectional elevation view; Fig. 3 is a more detailed block diagram of the electrical units of the respiratory apparatus; Fig. 4 and 5 shows signal condition curves measured in typical points of the start¬ ing signal generator; Fig. 5 shows signal curves measured in typical points of the bea generator; Fig. 7 shows the pressure versus time curves in all the four -operational modes; and Fig, 8 illustrates in diagrammatic form the restarting operation of the generator in controlled assisted mode. Detailed Description of the Invention Reference is made now to Fig. 1 showing the general block diagram of the respirator according to the invention. Oxygen stored in a predetermined over- pressure is lead to the respirator through oxygen receiving duct 1 and pressurized air is coupled to the respirator through an air receiving duct 2. The output of the oxygen receiving duct 1 is connected through an oxygen filter 3, a pin-valve 5 and a flow. meter 7 to a common conduit used for the transportati of oxygen-air mixture- Similarly the air receiving duct 2 is connected to the same conduit through an air filter 4, a pin-valve 6 and a flow meter 8. A safety valve 9 is coupled to the common conduit for preventing the establishment of pressures above a predetermined maximum value. The common conduit passes a gas-mixture heater 10, a means 11 for adjusting the relative humidity of the mixture and an ioniza'tor 12, by which the mixture can be adjusted to a required temperature and humidity and it can also be ionized. The temperature of the gas leaving the ionizator 12 is sensed by a temperature detector 13 which generates an analogue electrical temperature control signal coupled to the control signal coupled to the control input of the gas-mix¬ ture heater 10. The conduit of the oxygen-air mixture is coupled through a connection 14 to a patient junction 17 and this latter is formed substantially by a closed little room communicating with four openings. The first opening is connected to the connection 14 for receiving the overpressurized oxygen-air mixture. The second opening is connected to a second connec¬ tion 15, through which it is coupled to a mano¬ meter 18 and to a respiration demand detector 19. The third opening is coupled through a connection 16 to pressure adjusting valves 24, The oxygen-air mixture is released through the valves 24 to the free atmosphere under predetermined pressure values. The pressure prevailing in the respirator is deter¬ mined by the condition of the valves 24. The fourth opening of the patient junction 17 is connected through a suitably designed flexible tube to the respiratory system of the new-born or of the patient under treatment. The respiration demand detector 19 is" designed substantially as a pressure-capacitance transducer, which is capable of converting the pressure changes occurring in the patient junction 17 relative to a predetermined reference pressure value into a capacitance-change. An exemplary embodi- meπt of the respiration demand detector 19 will be described in connection with Fig. 2. The output of the respiration demand detector 19 is coupled to a starting signal generator 20 which senses the pressure drop caused by the spontaneous intake of the new-born and generates a starting signal. The output of the starting signal generator is coupled to a beat generator 21 and to a respiration stoppage detector 22. In certain modes of operation of the respirator the respiration stoppage detector 22 senses if the spontaneous breathing of the new-born has stopped throughout a given period of time, and in such conditions it generates a signal for the beat generator «21 and for an alarming device 25. The beat generator 21 is adapted to adjust the parameters of the respiratory cycles and a mode controller 26 is used for setting the mode of operation of the beat generator 21. The output of the beat generator 21 is coupled through an ampli¬ fier 23 to the control input of the pressure adjust¬ ing valves 24 and provides for.the appropriate control of the valves. Now reference will be made to Fig. 2 in which the structural design of a preferable embodi¬ ment of the respiratory demand detector 19 is shown. The respiratory demand detector comprises a case 30 defining a cylindrical inner room devided into two parts by a metal membrane 31. The upper part co p- rises a duct 32 connected to conduit 33 through which the inner room is coupled to a pressure adjust¬ ing assembly 34 adapted to set a required over¬ pressure for reference purposes. A disc 35 is arrang¬ ed in the case 30 spaced above the metal membrane 31 provided with a plurality of perforations. At the other side of the metal membrane 31 opposite to the disc 35 an other disc 36 is provided which also has perforations and on the surface of the disc 36 that faces the membrane 31 an electrically conductive coating is provided. The metal membrane 31 and the disc 36 together form a capacitor and the two ter¬ minals thereof are coupled to the input of the starting signal generator 20 (Fig. l). The lower space of the case 30 communicates through a duct 37 with a flexible tube 38 which is coupled to the manometer 18 and to the connection 15 of the patient junction 17. The pressure adjusting assembly 34 comprises a piston displaceable in a cylindrical house and its axial displacement is adjusted by a threaded knob 39 by which the pressure acting on the upper side of the metal membrane 31 can be set to the desired value. During operation of the respirator a slight- ly increased pressure compared to the atmospheric one (e.g. 0.4 to 0.5 kPa) is established in the respiratory system of the patient even in the ex¬ piration phase, " and the pressure adjusting assembly 34 is used to establish a reference pressure in the space above the metal membrane 31 which is lower by about 0.05 kPa than the required expiration pressure. If the new-born provides a pressure-drop higher than this 0.05 kPa value during inspiration in the interior of the patient junction 17, then the pressure below the metal membrane 31 will be small¬ er than that prevailing above the membrane 31, and the pressure in the upper part established by the pressure adjusting assembly 34 displaces the metal membrane 31 towards the lower disc 36, whereby the capacitance of the above mentioned capacitor will be increased. Now reference- will be made to Fig. 3 in which the units used for adjusting the parameters of the respiration is shown in detail. The two terminals of the pressure-sensing capacitor of the respiration demand detector 19 is coupled to the inputs of an astable multivibrator 201 that define the duty cycle thereof. An other astable multivibrator 202 is running together with the first astable multi- vibrator 201 which has the same nomάnal frequency and fixed duty cycle. The two multivibrators are synchronized in such a way that each of their periods is started in the same moment. The outputs of the astable multivibrators 201 and 202 are coupled to respective inputs of a logical gating circuit 203 formed expediently by a half anti- . valence gate, and the output of the gating circuit 203 is coupled to an integrating circuit 204. The above circuits form together the starting signal generator 20 shown in Fig. 1. Before discussing the other parts of the apparatus in detail the generat¬ ion of the starting signal will be explained in connection with Figs. 4 and 5.. The astable multivibrator 202 generates constant frequency pulses with periods Tl (Fig. 4a). The starting of the respective periods of the astable multivibrator 201 coincides with that of the multivibrator 202. It is supposed that before the moment to no inspiration takes place and the width of the output pulses of the astable multi¬ vibrator 201 is smaller than that of the other multivibrator 202 (Fig. 4b), After the moment to inspiration takes place, whereby the capacitance of the capacitor in the respiration demand detector 19 increases and this increase extends the width of the astable multivibrator 201. The astable multi¬ vibrator 201 is adjusted in such a way that the width of its output pulses reach the width of the pulses of the other multivibrator 202 when the pressure established by the inspiration of the new-born just equals to the reference pressure set by the pressure adjusting assembly 34. The logical 0 and 1 symbols shown in Fig. 4c illustrate the output variables at the outputs of the astable multivibrators 201 and 202 and of the logical gating circuit 203. The output of the gating circuit 203 is on logical 1 level only then if the output of the astable multivibrator 201 is on 1 level and the output of the astable ultivib- rator 202 is on 0 level. This condition can take place during inspiration only. Fig. 5a illustrates the signals at the input of the integrating circuit 204 and Fig. 5b shows, the integrator output. During the inspiration period of the new- born the gating circuit 203 provides respective output pulses in each period of the astable multi¬ vibrators 201 and 202, and the output signal of the integrating circuit 204 increases in a step-wise manner due to the integration of such output pulses. In Figs. 4 and 5 enlarged time-scale is used compar¬ ed to the respiration cycles, which means that the integrated pulse shown in Fig, 5b is very short compared to a respiratory cycle i.e. the integrator output produces practically immediately a pulse in response to the detection of the inspiration. The The integration process is required for the elimination of random distrubances and for the sake of neglecting the insufficient inspiration efforts. All sufficient inspiration of the new-born is associated with the generation of a respective pulse. Reference is made again to Fig. 3 in which it is illustrated that the output of the integrat¬ ing circuit 204 is coupled on the first hand to the input of the respiration stoppage detector 22 (which can be e.g. a retriggerable radnostable multivibrator), and on the other hand to the input of a gating circuit 213. The gating circuit 213 comprises an other input receiving the output of the respiration stoppage detector 22 and four other control inputs which in accordance with the four operational modes are coupled to the outputs of the mode controller 26. The gating circuit 213 has three output terminals driven in accordance with the selected mode of operation, and these -BUR output terminals are coupled to respective " inputs of a sawtooth generator 211. The sawtooth generator 211 comprises a trigger input 214, a re-triggered input 215, an astable input 216 and a frequency adjusting input 217. The frequency adjusting input 217 is coupled to a potentiometer (not\shown) for setting the respiration frequency. The output of the sawtooth generator 211 is coupled to the signal input of a comparator 212 wh_fch latter has a reference input 218 coupled to a potentiometer (not shown) adjusting the ex¬ piration-inspiration ratio. The sawtooth generator 211, the comparator 212 and the gating circuit 213 form together the beat generator 21 shown in Fig. 1. Fig. 3 illustrates the pressure adjusting valves 24 consisting of an electrically controlled expiration valve 242 and a pneumatic inspiration valve 241. The valves 241 and 242 communicate with the free atmosphere, ^ and the pressure treshold levels at which they let the gas mixture flow out to the free space can be adjusted within wide ranges by means of respective treshold adjusting inputs 243 and 244. When no control signal is generated by the amplifier 23, the path of the conduit coming from the connection 16 is open towards the expiration valve 242 and the comparatively low pressure treshold set for the expiration valve 242 determines the pressure prevailing in the system. This treshold level is typically by 0.4 to 0.5 kPa higher than the normal atmospheric pressure. When a control sig- nal is generated by the amplifier 23, the passage through the expiration valve 242 is cut off and the pressure in the system will be determined by the treshold level set for the inspiration valve 241 which corresponds typically to an over-pressure of 1.5 to 2.5 kPa. The inspiration valve 241 is ineffective during expiration because the expiration valve 242 with its lower treshold level prevents the increase of pressure above that value. The operation of the respirator according to the invention will be described in connection with the time diagrams shown in Figs, 6 to 8. It is true for all modes of operation that the respirator receives through the oxygen receiv- ing duct 1 and the air receiving duct 2 oxygen and air with predetermined pressure from respective sources not shown in the drawing. The ratio of the oxygen and the air can be adjusted to desired values by the pin valves 5 and 6, and the rotational flow meters 7 and 8 indicate the extent of the instantaneous gas flow. The adjustment of the temperature and the relative humidity of the gas mixture and the ionizatioπ of the same is carried out by the units shown in Fig. 1, whereby a stεriliz- ed gas mixture with required temperature, humidity and composition will flow through the connection 14 towards the patient junction 17. The respirator according to the invention can be operated by the mode controller 26 in four modes of operation. The first mode is the controlled respiration which should be used in the absence of spontaneous breathing. In this mode the pressure of the streaming gas mixture is rythmically changed between BUR£ respective pre-adjustable inspiration and ex¬ piration pressure values. The number of breathing cycles as well as the ratio of expiration to inspiration can also be adjusted within wide ranges. In this mode of operation the astable input 216 of the sawtooth generator 211 receives an enable signal, and the frequency of. the sawtooth generator 211 can be set by an adjusting potentio¬ meter not illustrated in Fig. 3, and the sawtooth generator 211 generates a continuous train of sawtooth signals. Fig. 6a shows the output of the sawtooth generator 211 and the reference level R of the comparator 212. When the increasing sawtooth signal reaches the reference level R, the comparator 212 is turned over (Fig. 6b) and the expiration pe¬ riod is started. The logical value 1 of the compa¬ rator output corresponds to inspiration and the logical value 0 corresponds to expiration. If the frequency of the sawtooth signals is changed, the ratio of the expiration period to the inspiration • will not change. The moments t-,, t 2 « t j respective¬ ly indicate boundaries of time sections in the respective associated periods, in which the ratio of the exp./insp. sections is constant. Obviously, the expiration-to-inspiration ratio can be changed freely within wide limits by changing the reference level R, and the so-adjusted ratio is independent from the frequency setting. Fig. 7 shows the pressure-versus-time diagram for the controlled respiration mode A, and it can be seen that the pressure is changed independently from the breathing efforts of the new-born. The second mode B is the controlled assisted respiration which is recommended when repeated U ι C_ spontaneous breathing is experienced. In this mode a controlled respiration -process takes place (dia¬ gram B in Fig. 7) and the respiration demand detec¬ tor 19 is used to sense the moments when the patient begins breathing in. If such an inspiration is sensed (the moments of which being indicated by short vertical arrows in Fig.7), the respirator is immediately switched over to inspiration, which means that the respirator is made to adapt itself to the breathing rythm of the patient. This process is illustrated in Figs. 8a and 8b in detail. In the controlled assisted respiration position of the mode controller 26 the re-triggered " input 215 of the sawtooth generator 211 receives the enable signal. In this mode the sawtooth generator 211 oscillates continuously just as in the previous mode and the pressure in the system changes periodi¬ cally according to the preset values. In this mode, however, at each spontaneous inspiration a corres- ponding pulse is generated at the output of the integrating circuit 204. The gating circuit 213 passes the pulse associated with the spontaneous inspiration to the re-triggered input 215 of the sawtooth generator 211, -which in response to such control starts immediately a new sawtooth cycle. In Fig. 8a the short vertical arrows indicate the inspiration moments, and it can be seen that in response to such events always a new cycle is started which begins with an inspiration cycle. The demand of the patient for inspiration will there¬ fore be immediately satisfied. The third mode C of the respirator is the inspected and assisted respiration. This mode is preferable when during the therapy a sufficient spontaneous breathing is established. In this mode there is no controlled respiration with fix ' ed frequency, and the rythm of respiration is determin¬ ed only by the inspiration demand of the patient. In diagram C of Fig. 7 the inspiration moments are illustrated by the short vertical arrows. Each inspiration is sensed by the respiration demand detector 19 and a corresponding starting pulse is generated by the starting signal generator 20, A mode controller 26 controls now the gating circuit 213 to send the enable signal to the trigger input 214 of the sawtooth generator 211 and to es¬ tablish a path between the output of the respiration stoppage detector 22 and the astable input 216 of the sawtooth generator 211. Sawtooth generation will take place only then, if the trigger input 214 receives a control signal from the output of the integrating circuit 204. This occurs always at the beginning of the spontaneous inspiration of the patient. In the starting period of the sawtooth gene- rator 211 an inspiration begins which is followed by an expiration period which lasts till the next start¬ ing moment. It can be seen in diagram C of Fig. ' 7 that each spontaneous inspiration is associated with the beginning of an inspiration period. The rythm of the breathing is determined by the demand of the patient. The inspecting function lies in that in every inspiration moment the respiration stoppage detector 22 starts a waiting period which is about 15 sec. lon If the subsequent inspiration occurs within the wait¬ ing period, then a new waiting period is tarted and the condition of the respiration stoppage detector 22 will not change. If the waiting period is finished - IS - and no inspiration occurs, it will change the logical condition of the respiration stoppage detector 22 and the astable input 216 of the sawtooth generator will be activated and a cont- rolled respiration will take place according to the controlled respiration mode for a predetermined period of time. At the same time the respiration stoppage detector 22 controls the alarming device 25, whereby a sufficient alarm will be generated. In diagram C of Fig. 7 the period T„ shows the waiting period that corresponds to the maximum stoppage of the breathing. This is followed by the controlled respiration for a period T^. This period T, lasts typically for 10 seconds and its value can be freely adjusted between appropriate limits. If a spontaneous breathing begins following the controlled respiration period, the assisted respir¬ ation will be continued. The fourth mode of operation D of the respiration is the inspected continuous positive airway pressure mode. (C.P.A.P..). This mode D is very similar to the C.P.A.P. mode commonly used in respiratory therapy, in which the patient spon¬ taneously breathes from the streaming gas mixture with positive pressure. The difference compared to the conventional C.P.A.P. mode lies in the way of responding to a stoppage of spontaneous breathing. Contrary to the conventional modes the inspection is not performed by the nursing personnel, but automatically by the inspection function of the respirator. The mode controller 26 establishes now a path through the gating circuit 203 between the output of the respiration stoppage detector 22 and the astable input 216 of the sawtooth generator 211. Owing to this constructional design controll¬ ed respiration does not take place until a respirat- ion stoppage is sensed and the sawtooth generator 211 is not running either. The inspiration of the patient is inspected in the way described earlier and at the beginning of each inspiration period the respiration stoppage detector 22 starts respective waiting periods T 2 . In diagram D of Fig. 7 the inspiration moments are indicated by short vertical arrows. If no inspiration is sensed during the predetermined waiting period T 2 , the respiration stoppage detector 22 enables the alarming device 25 and controls the sawtooth generator 211 to start astable oscillation for a period T,. Resulting from such control a controlled respiration will take place for a period of 10 seconds, whereafter the respirator returns to the C.P.A.P. mode and to the inspection of the respiration. It can be seen from the above description of the respirator according to the invention that besides its simple circuit design it can be used quickly and effectively in any kind of respiratory disturbances. With the above described design the respirator can not establish pressure less than the atmospheric value. The construction of the respirator according to the invention can be realized in small sizes in portable casing and it can also be arranged in an incubator. The application of such a respirator pro¬ vides for the possibility of being gas-sterilized in assembled condition and it provides also for the appropriate setting of the composition, temperature and humidity of the gas mixture, for its ionization and for the adjustment of required respiratory para¬ meters.

Claims: Claims 1. Respirator device, particularly for the respiratory treatment of new-born and inmate infants, comprising an oxygen and an air duct, means for adjusting the composition of the oxygen-air mixture, a conduit for transporting the mixture, a patient junction coupled to the conduit, a beat ge¬ nerator for determining the rythm of breathing and pressure adjusting valve means controlled by the output of the beat generator, c h a r a c t e r i z - e d by comprising a respiration demand detector (19) with an input coupled to the patient junction (17) and capable of detecting the pressure drop caused by the inspiration of the patient during the expiration period of the device, a starting signal generator (20) which in response to the detected pressure drop generates a corresponding starting pulse, a mode controller (26) for adjusting the operational mode according to the actual require¬ ment of the treatment, the beat generator (21) comprises a generatoj- unit provided with respective control inputs for the selection of continuous, triggered and expediently retriggered modes of signal generation, the mode controller (26) is used to couple the required one of these inputs to. the output of the starting signal generator (2θ), and ■ the pressure adjusting valve means (24) being coupl¬ ed to the patient junction (17) and providing ad¬ justable positive pressures .both in inspiration and expiration at the junction by the controlled release of the oxygen-air mixture in the atmosphere. 2. The respirator device as claimed ig claim 1, c h a r a c t e r i z e d in that the output of the starting signal generator (20) is coupled to the input αf a respiration stoppage detector " (22) for providing an appropriate signal when no out¬ put pulse is received from the starting signal generator (22) within a predetermined period of time, and the output of the starting signal gene¬ rator (22) is coupled to a control input of the beat generator (21). 3. The respirator device as claimed in claim 2, c h a r a c t e r i z e d in that the generator unit in the beat generator (21) is a sawtooth generator (211) having a trigger input (214), a re-triggered input (215) and an astable input (216), and the beat generator (2l) comprises a gating circuit (213) controlled by the mode cont- roller (26.), and the outputs of the gating circuit (213) are coupled to the respective inputs of the sawtooth generator (211) and an input of the gat¬ ing circuit (213) is coupled to the output of the starting signal generator (20) and an other input thereof is coupled to the output of the respiration stoppage detector (22). 4. The respirator device as claimed in claim 3, c h a r a c t e r i z e d in that the beat ge¬ nerator (2l) comprises a comparator (212) having a signal input coupled to the output q_f the sawtooth generator (211), a reference input (218) coupled to a means for adjusting the expiration-to-inspiration ratio and an output coupled through an amplifier (23) to the pressure adjusting valve means (24). 5. The respirator device as claimed in claim 1, c h a r a c t e r i z e d in that the respiration demand detector (19) is formed by a membrane-operat¬ ed pressure difference to capacitance transducer hav¬ ing a case (3θ) divided by a metal membrane (31) in two parts, a pressure adjusting assembly (34) is coupled to one of said parts, and the other part communicating with the interior of the patient junction (17), 6. The respirator device as claimed in claim 5, c h a r a c t e r i z e d in that the starting signal generator (2θ) comprises a pair of synchro¬ nously started astable multivibrators. (201, 202), the first astable multivibrator (20l) comprises a control input for adjusting the duty cycle being coupled to the output of the respiration demand detector (19), said generator (20) comprises addit¬ ionally a gating circuit (203) having respective in¬ puts coupled to the outputs of the astable ulti- vibrators (201, 202), and an integrating circuit. (204) having an input coupled to the output of the gating circuit (203) and its output forming the output of the starting signal generator (20). 7. The respirator device as claimed in claim 2, c h a r a c t e r i z e d in that the respiration stoppage detector (22) is formed by a monostable multivibrator and having an output coupled to an alarming device (25) for generating breathing stoppage alarm. 8, The respirator device as claimed in claim 1, c h a r a c t e r i z e d in that the pressure adjusting valve means (24) comprising a controlled expiration valve (242) having a control input coupl¬ ed to the output of the beat generator (21) and a pneumatic input coupled to the patient junction (17) which in rest condition defining the .expiration pressure, and an inspiration valve (241) having an input coupled to the patient junction (17) and in the on condition of the expiration valve (242) de- BUK, _ v p ι fining the inspiration pressure. 9. The respirator device as claimed in claim 1, c h a r a c t e r i z e d in that the oxygen duct (l) is connected to an oxygen filter (3), a valve (5) and a flow meter (7), and the air duct (2) is connected to an air filter (4), an other valve (δ) and a flow meter (8), the output of the two flow meters (7 and 8) are coupled together to the inlet of the conduit for the oxygen-air mixture and the conduit communicating with a safety valve (9), the conduit is coupled to a gas heater (10), a means for adjusting the humidity (ll), an ion- isator (12) and a temperature detector (13), further¬ more the input of the respiration demand detector (19) is connected to a manometer (18). BϋR

Inventors: KISZEL JANOS, NAGY LASZLO, PAPP LASZLO
Applicants: KISZEL JANOS, NAGY LASZLO, PAPP LASZLO, VAS ES MUESZERIPARI SZOEVETKEZ, VAS ES MUESZERIPARI SZOEVETKEZET
Application year: 1981
Main classification: A61H31
IPC codes: A61M16