the basic mechanical / pneumatic components of a respirator 1 constructed in accordance with the principles of the present invention are shown in fig1 . the respiratory gas proceeds via a line 2 into a reservoir 3 , for example a bellows . from the reservoir 3 , the respiratory gas is supplied via an inspiration line 4 to a further line 5 connected to a patient ( not shown ). the line 5 is also in communication with an expiration line 6 . the arrows in the lines indicate the direction of gas flow therein . the inspiration line 4 is provided with a valve 7 and a gas flow sensor 8 . the expiration line 6 is also provided with a valve 9 and a gas flow sensor 10 . additionally , a pressure sensor ( not shown ) may also be connected in each line . the signals from the flow or , ( effused ) pressure sensors are conducted to a control unit ( not shown ) which controls the opening and closing of the valves 7 and 9 dependent on the sensor signals , and dependent on the mode of respiration which has been selected and on the given boundary conditions . a gas flow sensor 11 , shown with dashed lines , can also being connected in the line 5 , which generates a signal that is also supplied to the control unit . the basic principle of the respirator in accordance with the principles of the present invention is shown in block diagram form in fig2 . a signal corresponding to the gas flow φ e in the expiration line is supplied at a terminal 20 . a reference signal corresponding to the set level of the desired gas flow φ eref in the expiration line is supplied to a terminal 21 . the difference between these two signals , i . e ., the deviation of the actual flow from the set flow , is formed in a differential amplifier 22 , and may also be amplified under certain circumstances . this difference signal is connected to a subsequent integrator 23 , whose output signal is supplied to a further amplifier 25 via a diode 24 . the reference signal is also supplied to the further amplifier 25 . a signal φ iref which is employed for controlling the valve in the inspiration line is present at the output of this amplifier 25 . the functioning of this circuit is as follows . if it is first assumed that the actual flow φ e is at the set level , the difference will be zero and thus the output signal of the amplifier 22 is zero . the integrator 23 thus does not generate an output signal . the only input signal at the amplifier 25 is thus the reference signal which , after amplification , serves the purpose of controlling the valve 7 in the inspiration line , and maintains the flow through this valve constant . when it occurs , for example due to an attempt by the patient to inhale , that φ e drops in comparison to φ eref , the difference is amplified and integrated and , as long as the integration value is positive , the difference is forwarded via the diode 24 to the amplifier 25 , and is added to the reference signal . the output signal φ iref is thus modified relative to the fixed level dependent on the actual gas flow through the expiration line . the modification results in the gas flow at the inspiration line being increased , in order to compensate for the removal of gas by the patient and to again boost the gas flow at the expiration side to the established level . it is possible within the scope of the invention to omit the diode 24 shown in fig2 and thus to have the gas flow at the inspiration side follow the gas flow at the expiration side in both directions . this would then result , given a decreasing gas flow in the expiration line , in an increase in the gas flow in the inspiration line , and vice versa . due to the presence of the diode 24 , however , adjustment of the inspiration flow is substantially limited to the inspiration phase , i . e ., to the phase wherein the gas flow in the expiration line attempts to drop below the established level due to efforts by the patient to inhale . during the expiration phase , a defined value for the inspiration gas flow is provided which is not subject to sudden fluctuations , thereby facilitating a calculation of the overall expiratory volume . an exemplary circuit for generating a control value for the valve 7 in the inspiration line , based on the block diagram shown in fig2 is shown in fig3 . the signal corresponding to the actual flow φ e is supplied to a first amplifier 30 via the terminal 20 . the reference signal φ eref is supplied via a terminal 21 to an amplifier 31 . both amplifiers 30 and 31 are for signal editing . the outputs of these two amplifiers are combined at point 32 , so that a signal is present at the point 32 corresponding to the difference of the output signals of the two amplifiers 21 and 31 . polarity and gain factors are selected so that the difference becomes zero when the actual flow corresponds to the set flow . the signal at point 32 is supplied to an amplifier 33 , essentially corresponding to the amplifier 22 of fig2 . a diode 34 is connected in parallel with a resistor in a feedback branch of this amplifier . the diode 34 becomes blocking given a negative input voltage at the amplifier 33 , and the amplification ensues according to the resistances which have been selected . an amplified signal is present at the output of the amplifier 33 which is inverted with respect to the input for that amplifier . if , by contrast , the input signal becomes positive , the diode 34 becomes transmissive and a constant output level of , for example , - 0 . 6 volts is present at the output of the amplifier 33 , independently of the size of the input signal . the output signal of the amplifier 33 is supplied to an integrator 35 which corresponds to the integrator 23 of fig2 . a capacitor 36 is connected in series with a diode 37 in the feedback branch of the integrator 35 . a further diode 38 is connected in parallel with the diode 37 and the capacitor 36 . as long as the input signal at the integrator 35 is positive , the diode 38 is in a blocking state , and the capacitor 36 is charged . if the negative voltage , ( i . e ., - 0 . 6 volts ) is present at the input , the capacitor 36 is discharged with this constant voltage , but is not charged in an opposite direction because the diode 38 is then transmissive . the output of the integrator 35 is supplied to a further amplifier 39 , to which the reference signal φ eref from the amplifier 31 is simultaneously supplied . the sum of this amplified reference signal and the output signal of the integrator 35 is thus present at the input of the amplifier 39 . this sum , after amplification by the amplifier 39 , represents the reference signal φ iref at the terminal 26 for controlling the extent to which the valve 7 in the inspiration line is opened . as mentioned above , the diodes 34 , 37 and 38 can be omitted and the change in the gas flow in the expiration line in both directions can be correspondingly compensated , both positively and negatively , by changing the inspiration gas flow . moreover , it is possible within the scope of the invention to add further controls , such as a proportional control , in addition to the integral control , or to replace the integral control by a proportional control . further regulation via a negative feedback loop can be provided for controlling the valve 7 by monitoring the difference between a signal from the gas flow sensor 8 in the inspiration line 4 and a reference signal , and through feedback causing this difference to tend toward zero . the output of the amplifier 39 , i . e ., the signal φ iref , can be used as this further reference signal , so that the difference between the flow as measured by the gas flow sensor 8 and φ iref is maintained at or close to zero . the respective gas flows in the expiration and inspiration lines are entered over time in each of fig4 a and 4b . the time axis is subdivided into three sections a , b and c . it is assumed in section a in fig4 a that the patient gas flow is zero , i . e ., the patient is neither inhaling nor exhaling . in this case , the expiration gas flow φ e is equal to the inspiration gas flow φ i , and is constant . the patient gas flow is negative in section b , i . e ., the patient is inhaling . if it is assumed that the inspiration gas flow continues to remain constant , as indicated with dashed lines in the lower part of fig4 a , the expiration gas flow will then drop in accord with the negative patient gas flow . this is also indicated with dashed lines . it is assumed in section c that the patient gas flow is positive , i . e ., the patient is exhaling . again given the assumption that the inspiration gas flow is maintained constant , the expiration gas flow now increases accordingly . the gas flows for the respirator of the invention are shown in fig4 b . the flows in section a are the same as shown in fig4 a . in section b , however , the expiration gas flow in fig4 b remains constant , because the inspiration gas flow is correspondingly increased for compensation , beginning with the first deviation from this constant level . in section c having a positive patient gas flow , the expiration gas flow in fig4 b increases in accord with the preferred exemplary embodiment , and the inspiration gas flow is maintained constant . it is also possible within this region , as shown with dashed lines , that the control takes affect and holds the expiration gas flow constant . fig4 a and 4b show the chronological curve of the gas flows schematically . fig5 is an example of the curve of an actual expiration gas flow and an actual inspiration gas flow . again , a constant gas flow is established , i . e ., the patient is neither inhaling nor exhaling . the patient begins to inhale at point a in fig5 . this initially results in a brief drop of the expiration gas flow and to an increasing inspiration gas flow , according to the control produced by the invention . at point b , the expiration gas flow again reaches the prescribed , constant level . beginning at this time , the inspiration gas flow ( which is not excessively high ) drops according to a prescribed time function , which is a linear function in the example of fig5 whereas the expiration gas flow initially continues to rise , but then also returns to the prescribed level . the breathing volume of the patient can be calculated by integrating the difference between the two gas flows . it is also possible within the scope of the present invention to control the valve 7 in the inspiration line on the basis of the patient gas flow , instead of by means of the gas flow through the expiration line . when the patient gas flow is negative , i . e ., when the patient is inhaling , the inspiration valve is correspondingly opened . when the patient gas flow is positive , opening of the inspiration valve either remains constant , or changes according to a prescribable time function , or changes dependent on the patient gas flow . the patient gas flow can be identified with the gas flow sensor 11 in the common line 5 as shown in fig1 . although further modifications and changes may be suggested by those skilled in the art , it is the intention of the inventors to embody within the patient warranted hereon all changes and modifications as reasonably and properly come within the scope of their contribution to the art .
in a respirator having an inspiration gas flow controlled by the expiration gas flow , in order to avoid triggering difficulties , particularly in the neonatal respiration therapy , the respirator is controlled such that a continuous gas flow flows through the inspiration and expiration lines . the gas flow is measured in the inspiration line by a gas flow sensor . the measured signal from the gas flow sensor is used to control a valve in the inspiration line , or a common line connected to the inspiration and expiration lines so that a constant gas flow is maintained in the expiration line .