a schematic view of a device 10 according to the present invention is seen in fig1 . the device 10 has , just like the devices 10 shown schematically in fig2 , 3 and 4 , a ventilator 20 which allows spontaneous breathing with a control device 30 , a dosing device 40 and a measuring arrangement comprised of a measuring device 50 . both the dosing device 40 and the measuring device 50 are connected to the control device 30 by means of bidirectional data exchange connection 41 , 52 . a patient p can be ventilated or the breathing of the patient p can be assisted by means of the device 10 . at the same time , different drugs can be fed to the patient p intravenously or by inhalation . just like the ventilator 20 shown in fig2 , 3 and 4 , the ventilator 20 in fig1 contains a ventilator unit 200 controllable by means of the control device 30 and has a breathing line 21 . the breathing line 21 has an inspiration line 22 , an expiration line 23 , a y - piece 24 and a patient line 29 . the inspiration line 22 is connected at one of its ends to the ventilator unit 200 via a connection piece 28 and at its other end to the y - piece 24 . the expiration line 23 is connected at one of its ends to the ventilator line 200 , likewise via a connection piece 29 , and at its other end to the y - piece 24 . the patient line 29 is likewise connected to the y - piece . the patient line 29 is , for example , a ventilation tube . this may be connected to an adapter ( not shown ), for example , a breathing mask . however , it may also be an intubation tube . just like the ventilator 20 shown in fig2 , 3 and 4 , the ventilator 20 in fig1 has , furthermore , a gas port 25 . fresh breathing air can be fed to the ventilator 20 by means of this gas port 25 . a breathing air source ( not shown ) can be connected to the gas port 25 . it may be a compressed air source or even a simple inlet for room air . in addition , the ventilator 20 in fig1 has , just like in fig2 , 3 and 4 , a waste gas outlet 26 . the air flowing back from the breathing line 21 can be released into the surrounding area through this waste gas outlet 26 . a disposal device ( not shown ), which removes drug residues that may possibly be present from the air flowing back , may be connected to the waste gas outlet 26 . the control device 30 is integrated in the ventilator 20 in the example shown . the ventilator unit 200 and the control device 30 may be accommodated for this simply in a common housing . just like the control device 30 shown in fig2 , 3 and 4 , the control device 30 in fig1 has a memory 31 and a computer 32 . a plurality of memories 31 may , of course , be present as well . the dosing device 40 is a device for dosing drugs that can be administered intravenously . in the example shown , the device 40 has a first drug feed line 42 for a first drug and a second drug feed line 43 for a second drug . the device 40 may have only one drug feed line or more than two drug feed lines . the dosing device 40 is connected to the control device 30 via the bidirectional data transmission means in the form of a bidirectional data transmission connection 41 . the dosing device 40 can be connected either directly to the patient or to an adapter , for example , an infusion cannula ( infusion needle ) via the drug feed lines 42 , 43 . the device 10 has , furthermore , a drug evaporator 60 . the drug evaporator 60 is connected to a port 63 for feeding the drug via a drug feed line 61 . the port 63 is arranged on or in the patient line 29 , so that a volatile drug , which is dispensed from the drug evaporator 60 , can be fed to the breathing line 21 . the patient p can therefore inhale and then exhale such a volatile anesthetic via the breathing line 21 . to collect exhaled drug gas , the device 10 has , furthermore , a drug gas intermediate storage unit 62 . the volatile drug collected therein can be inhaled by the patient p again during his next breath . the patient p can , furthermore , also exhale metabolized forms or even excess quantities of , for example , an intravenously administered drug . as a consequence , certain concentrations of a drug administered via the dosing device 40 may also be detectable as drug residues in the breathing gas . these drug residues are also collected in the drug gas intermediate storage unit 62 . the effective active ingredient quantity can be determined from the concentration of these drug residues . a sampling device 53 , which is arranged in the breathing line 21 , as is shown , preferably in the patient line 29 , is provided for checking the concentration of such a drug residue , volatile drug , the metabolized form of a volatile drug in the breathing gas or the like . a sensor , which detects the concentration of the desired substance , is arranged in this sampling device 53 . furthermore , sensors , which detect various other respiration parameters , namely , airway resistance ( rr ), end - expiratory co 2 concentration ( etco 2 ), tidal volume ( rmv ), partial oxygen saturation ( spo 2 ), respiration rate or the like , may be arranged here as well . the sampling device 53 is connected to the measuring device 50 via a data acquisition line 51 . the measuring device 50 is connected , in turn , to the control device 30 via a bidirectional data exchange connection 52 . at any rate , the measuring device 50 is designed such that it can detect both the effective active ingredient quantity of one or more administered substances and one or more of the respiration parameters described here . the embodiment variant of the device 10 according to the present invention , which is shown schematically in fig2 , also has , as was already described above in connection with fig1 , a ventilator 20 which allows spontaneous breathing , a control device 30 , a dosing device 40 and a measuring device 50 . the dosing device 40 shown in fig2 is connected to the control device 30 via a bidirectional data exchange connection 42 . the dosing device 40 also has a first drug feed line 42 and a second drug feed line 43 . the first drug feed line 42 is a drug feed line for drugs that can be administered intravenously . the first drug feed line 42 can be connected to an adapter , for example , an infusion needle . the first drug feed line 42 may also be connected directly to the patient . the second drug feed line 43 is a drug feed line for volatile drugs , which can be fed with the breathing gas flow . the second drug line 43 is connected to a port 63 for feeding the drug . the port 63 is arranged in the patient line 29 . the dosing device 40 has , furthermore , a drug evaporator 60 for providing the volatile drug . the drug evaporator 60 may be arranged in a common housing with the dosing device 40 or be a separate assembly unit . the measuring device 50 shown in fig2 is connected to the control device 30 via a bidirectional data exchange connection 52 . furthermore , the measuring device 50 has a data acquisition line 51 . the measuring device 50 is designed in this case such that it can analyze a body fluid of a patient . the data acquisition line 51 is connected to an adapter ( not shown ). the adapter may be connected either directly to the patient p or to a sampling device ( likewise not shown ). a sample of a body fluid can be transported into the measuring device 50 via the data acquisition line 51 . a sensor device can then detect the desired measured value in the measuring device 50 . as an alternative , the data acquisition line 51 may also be connected to a sensor device arranged outside the measuring device 50 , for example , to a measuring electrode for muscle action potentials or an ecg electrode . at any rate , the measuring device 50 is designed such that it can detect both the effective active ingredient quantity of one or more administered substances and one or more of the respiration parameters described here . the embodiment variant of the device 10 according to the present invention , which is shown schematically in fig3 , also has , as was already described above in connection with fig1 , a ventilator 20 which allows spontaneous breathing , a control device 30 , a dosing device 40 and a measuring device 50 . the control device 30 is shown here as an example as an external component of the ventilator 20 . it may , of course , also be integrated in the ventilator 20 . as was likewise described in connection with fig1 , the dosing device 40 is a device for dosing drugs that can be administered intravenously . in the example shown , the device 40 has a first drug feed line 42 for a first drug and a second drug feed line 43 for a second drug . the device 40 may of course have only one or a plurality of drug feed lines . the dosing device 40 is connected to the control device 30 via the bidirectional data transmission means 41 . the dosing device 40 can be connected via the drug feed lines 42 , 43 either directly to the patient or to an adapter , for example , an infusion cannula . the measuring device 50 shown in fig3 is connected to the control device 30 via a bidirectional data exchange connection 52 . furthermore , the measuring device 50 has a data acquisition line 51 . the measuring device 50 is designed in this case such that it can analyze a body fluid of a patient . the data acquisition line 51 is connected to an adapter ( not shown ). the adapter may be connected either directly to the patient p or to a sampling device ( likewise not shown ). a sample of a body fluid can be transported into the measuring device 50 via the data acquisition line 51 . a sensor device can then detect the desired measured value in the measuring device 50 . as an alternative , the data acquisition line 51 may also be connected to a sensor device arranged outside the measuring device 50 , for example , a measuring electrode for muscle action potentials or an ecg electrode . at any rate , the measuring device 50 is designed such that it can detect both the effective active ingredient quantity of one or more administered substances and one or more of the respiration parameters described here . the embodiment variant of the device 10 according to the present invention , which is shown schematically in fig4 , also has , as was already described above in connection with fig1 , a ventilator 20 which allows spontaneous breathing , a control device 30 , a dosing device 40 and a measuring arrangement comprising a measuring device 50 . the control device 30 is shown in this case as an example as an external component of the ventilator 20 . it may , of course , also be integrated in the ventilator 20 . as was already described in connection with fig1 and fig3 , the dosing device 40 is a device for dosing drugs that can be administered intravenously . in the example shown , the device 40 has a first drug feed line 42 for a first drug and a second drug feed line 43 for a second drug . the device 40 may of course have only one or a plurality of drug feed lines . the dosing device 40 is connected to the control device 30 via the bidirectional data transmission means 41 . the dosing device 40 can be connected via the drug feed lines 42 , 43 either directly to the patient or to an adapter , for example , an infusion cannula . the device 10 according to the present invention shown in fig4 has , the measuring arrangement comprises in addition to the first measuring device 50 , a second measuring device 50 ′. like the measuring device 50 already described in connection with fig2 and 3 , the first measuring device 50 is connected to the control device 30 via a bidirectional data exchange connection 52 . furthermore , the measuring device 50 has a data acquisition line 51 . the measuring device 50 is designed here such that it can analyze a body fluid of a patient . the data acquisition line 51 is connected to an adapter ( not shown ). the adapter may be connected either directly to the patient p or to a sampling device ( likewise not shown ). a sample of a body fluid can be transported into the measuring device 50 via the data acquisition line 51 . a sensor device can then detect the desired measured value in the measuring device 50 . as an alternative , the data acquisition line 51 may also be connected to a sensor device arranged outside the measuring device 50 , for example , a measuring electrode for muscle action potentials or an ecg electrode . at any rate , the measuring device 50 is designed such that it can detect both the effective active ingredient quantity of one or more administered substances and one or more of the respiration parameters described here . the second measuring device 50 ′ is connected to the sampling device 53 by a line 51 ′ and to the control device 30 by a bidirectional data exchange connection 52 ′. fig5 shows the schematic chronological sequence of a breathing exercise , which can be carried out by means of a device according to the present invention . the device described in fig1 , 2 , 3 and 4 is operated using the above - described method for operating the device . the patient can be weaned from mechanical ventilation or ventilatory assist by means of such a breathing exercise . at the same time , it can be observed whether the risk of respiratory depression is present if the patient shall , e . g ., be extubated . fig5 shows four different curves , v - wob , mw , md , saf , which extend along the time axis t , namely , the percentage of the work of breathing that is provided by the ventilator , hereinafter called the ventilator work of breathing v - wob ; the drug effect curve mw ; the drug dosing md , and the curve describing the patient &# 39 ; s ability to breath spontaneously , saf . the percentage of the work of breathing that is provided by the ventilator , i . e ., the work of breathing of the ventilator v - wob , is reciprocal to the patient &# 39 ; s lung function ( not shown ). axis y of the schematic diagram represents a fictitious number axis in which , as is common practice , higher numerical values are arranged at the top and lower numerical values at the bottom . four times t 1 , t 2 , t 3 and t 4 , namely , the start time t 1 of the drug reduction , the start of the breathing exercise t 2 , the nominal end of the breathing exercise t 3 , which corresponds to the end of the drug reduction , and the effective end of the breathing exercise t 4 are shown on the time axis t . the drug dose administered is reduced for the period between the start time t 1 and the nominal end of the breathing exercise t 3 , which can be recognized on the basis of the drug dosing curve md . the drug dosing curve md drops at the start time t 1 to a markedly reduced level . the drug dose administered is reduced at this time . the drug dosing curve md rises again to the previous level at the nominal end of the breathing exercise t 3 . consequently , the drug dose administered is raised again at this time . therefore , there is a period of drug reduction δt between the start time t 1 and the nominal end of the breathing exercise t 3 . corresponding to the drug dose administered , the effect of the drugs administered is at first high before the start time t 1 and then drops slowly after the start time t 1 , as is recognized from the drug effect curve mw . the breathing exercise t 2 starts as soon as the effect of the drugs administered has dropped to a preset level . the drug effect increases again as a consequence of the repeated increase in drug dosing after the nominal end of the breathing exercise t 3 . before the start time t 1 , the patient is in a state in which the patient is either fully or partially ventilated and in which his own ability to breathe spontaneously is markedly reduced by the effect of the drugs administered and by other external effects . this is seen from the saf curve describing the patient &# 39 ; s ability to breath spontaneously . this is at a low level before the start time t 1 and rises slowly starting from the start time t 1 until the start of the breathing exercise t 2 . the ability to breathe spontaneously starts to drop again slowly with the nominal end of the breathing exercise t 3 as a consequence of the repeated increase of drug dosing . this drop accelerates with the effective end of the breathing exercise t 4 , after which the saf curve describing the ability to breathe spontaneously drops again to a low level . the work of breathing of the ventilator , v - wob , shows that a large percentage of the work of breathing is assumed by the ventilator before the start time t 1 . this percentage also remains constant until the start of the breathing exercise t 2 . the work of breathing of the ventilator , v - wob , drops to a lower level with the start of the breathing exercise t 2 . this means that the ventilator assumes a lower percentage of the work of breathing and the percentage of the work of breathing that must be performed by the patient is increased . the work of breathing of the ventilator , v - wob , increases again to the original level between the nominal end of the breathing exercise t 3 and the effective end of the breathing exercise t 4 . this means that the ventilator will again assume a higher percentage of the work of breathing with the resumption of a higher drug dosing and the reduced ability to breath spontaneously , which can be expected as a consequence . it is seen in fig5 that a first transition period uz 1 is located between the start time t 1 and the start of the breathing exercise t 2 and that there is a second transition period uz 2 between the nominal end of the breathing exercise t 3 and the effective end of the breathing exercise t 4 . the period of nominal breathing exercise tt is located between the start of the breathing exercise t 2 and the end of the nominal breathing exercise t 3 , i . e ., between the first transition period uz 1 and the second transition period uz 2 . the drug dosing curve md is at a low level during the first transition period uz 1 , i . e ., a reduced drug dose is administered . the drug effect curve mw drops slowly during this transition period uz 1 . this drop is monitored by means of the device 10 according to the present invention , which is shown in fig1 , 2 , 3 and 4 . in particular , the effective drug concentration is detected by means of a measuring device 50 , 50 ′ corresponding to step c of the method according to the present invention for operating the device 10 . at the same time , the saf curve describing the ability to breathe spontaneously rises during the transition period uz 1 . this rise is likewise monitored with the device 10 shown in fig1 , 2 , 3 and 4 . in particular , the respiration parameters are detected by means of a measuring device 50 , 50 ′ corresponding to step a of the method according to the present invention for operating the device 10 . both the detected respiration parameters and the detected effective drug concentrations are processed in the control device 30 of the device 10 , and , as was described above , decision values are determined . the start of the breathing exercise t 2 can be set on the basis of these decision values . the control device 30 can thus transmit a control command to the ventilator 20 at this time , so that the ventilator 20 reduces the ventilation or ventilatory assist of the patient until the level desired during the period of the nominal breathing exercise tt is reached . the first transition period uz 1 is followed by the period of the nominal breathing exercise tt . the patient &# 39 ; s ability to breathe spontaneously is suppressed only slightly or not at all during this period . the effective quantity of the drugs administered with a respiration - depressant side effect is correspondingly adjusted . the device 10 described in fig1 , 2 , 3 and 4 detects the respiration parameters and the effective drug concentration during this period as well by means of the measuring device or measuring devices 50 , 50 ′. the second transition period uz 2 starts with the end of the nominal breathing exercise t 3 . the drug dose is raised again at this time , so that the drug dosing curve md rises again . the percentage of the lung function that is assumed by the ventilator 30 is also increased again until the end time t 4 , so that the ventilator work of breathing curve v - wob also rises again during the transition period uz 2 . examples of respiration parameters that may be stored in the device 10 according to the present invention , in particular in the control device 30 according to the above - described exemplary embodiments are , e . g ., these respiration parameters include corresponding tolerance ranges , which are taken into account when generating control commands . a respiration rate in the range of 15 - 30 per minute is usually considered to be normal , and a respiration rate of , e . g ., 35 per minute is usually considered to be tachypnea requiring treatment in adults . for example , the following exemplary values listed in table 1 , which are considered to be normal ventilation under certain marginal conditions , may be stored as benchmark data for respiration parameters in the device . tolerance fields are set in the multidimensional respiration parameter space to determine decision values . this means that the control device has means that are designed to associate the measured values determined by the measuring device on the basis of stored data . for example , values for the end - tidal co 2 partial pressure ( etco 2 ) and for the spontaneous respiration rate f , may be stored in the control device . it can be set , for example , for the end - tidal co 2 partial pressure that the control device selects a first decision value el when the actual value drops below a value of 20 mmhg , but it selects a decision value e2 when the actual value drops below a value of 55 mmhg but there is a value of 20 mmhg or higher , and a decision value e3 when the actual value exceeds a value of 55 mmhg . corresponding decision values can also be assigned to other respiration parameters in the same manner . for example , a decision value e4 may be assigned to a value of 35 bpm or higher for the spontaneous respiration rate f spn , but a decision value e5 may be assigned to an f , value of less than 35 bpm but at least 30 bpm , a decision value e6 may be assigned to an f spn value of less than 30 bpm but at least 15 bpm , and a decision value e7 may be assigned to an f spn value of less than 15 bpm . it is apparent that this example is only an example and completely different values may , of course , also be stored in the control device . the selection of the control commands is then performed on the basis of the decision values determined . both individual decision values and combinations of decision values may be decisive . if , for example , the combination of decision value e5 and decision value e2 was determined in the control device , the corresponding control command may be a command that instructs the ventilator to raise the pressure by a preset value , e . g ., 2 mbar or less . another example would be the determination of the decision values e6 and e2 . the corresponding control command may now be a command that instructs the ventilator to lower the pressure by , e . g ., 4 mbar or less . the time - dependent courses of the effective drug concentration can be calculated in advance for many relevant drugs by means of models from medical research . for example , an adequate value for the transition time uz 1 can be determined on the basis of the time in which the effective concentration of opioids drops to half the value when the supply is stopped . for example , concentration limits can be assigned in the control device for certain opioids to certain time values . the time values may indicate here the duration of the transition period uz 1 . these values may be assigned to a certain body weight or other data of the patient . when using the device , the operator may , for example , program this assignment freely or even select from different suggestions stored in the control device . the duration of the period uz 2 can be determined in the same manner on the basis of stored data . the duration of time during which the full effect of the drug is reached after administration of a certain dose of a drug is important for the control of the device during the period uz 2 . these times of some important drugs used in analgosedation are listed as examples in the table below . the onset time designates the start of the effect after administration of the active ingredient . one example of stored pharmacodynamic data is the interaction that , for example , propofol and remifentanil may have when they are administered together . the risk for the development of respiratory depression can be estimated on the basis of the known administered doses of the drugs . respiratory depression reaches its maximum within 5 minutes following the single - time bolus injection of 1 μg / kg of remifentanil and persists for about 10 minutes , and it persists for about 20 minutes following administration of 2 μg / kg . the blood gases return to normal within 5 - 15 minutes , regardless of the rate of infusion , after a continuous infusion had been stopped . infusion rates targeting an effective concentration of 2 . 0 ng / ml are not unusual in case of intense pain . these relationships can be used to determine the degree of respiratory depression as a function of time from measured effective quantities or effective quantities determined in another manner , which are consequently known quantities . this can be done by means of pharmacological models ; as an alternative , an operator of the device according to the present invention may preset a variation range of the dosage based on his experience . the control of the device according to the present invention uses these data . all the features and advantages appearing from the claims , the specification , including the following examples and the drawings , including design details , arrangements in space and process steps , may be essential for the present invention both in themselves and in the many different combinations . while specific embodiments of the invention have been shown and described in detail to illustrate the application of the principles of the invention , it will be understood that the invention may be embodied otherwise without departing from such principles .
a respiratory support device includes a ventilator which allows spontaneous breathing , a control device , a dosing device for pharmaceutically active substances , and at least one first measuring device . pharmacodynamic and / or pharmacokinetic data of pharmaceutically active substances and / or compositions as well as comparison data for different respiration parameters are stored in the control device . the measuring device is configured to detect one or more respiration parameters . the measuring device or another measuring device is additionally configured such that the effective active ingredient quantity of one or more pharmaceutical substances dispensed by the dosing device can be detected using the measuring device . a device for exchanging data in a bidirectional manner is arranged at least between the control device and the measuring device and / or the dosing device .