JP2010220711A - Medicinal gas administration device - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To provide a medicinal gas administration device reducing the useless consumption of a medicinal gas and considering safety and environments. <P>SOLUTION: The medicinal gas administration device is for introducing the medicinal gas to a gas flowing through a respiratory line of an artificial respirator 2. By intermittently introducing the medicinal gas in linkage with switch of the inspiratory phase and expiratory phase of artificial respiration in the artificial respirator 2, the medicinal gas is introduced matched with the expiratory phase of the artificial respiration. Consequently, the medicinal gas uselessly discharged conventionally is saved, the consumption of the medicinal gas is substantially reduced, a medicinal gas amount to be discharged to a treatment environment is substantially reduced, and the health damage to a medical staff and environmental destruction such as global warming are prevented. <P>COPYRIGHT: (C)2011,JPO&INPIT

Description

  The present invention relates to a pharmaceutical gas administration device for administering a pharmaceutical gas to a human body for the purpose of treating a human body or an animal.

  Gases that have physiological effects on the human body and animals are sometimes used in clinical medicine as pharmaceutical gases. As such a medicinal gas, for example, the following gas is expected to be used clinically (see Non-Patent Documents 1 to 6 below).

Nitric oxide has a vasodilatory effect and has already been approved as a pharmaceutical in various countries for the purpose of improving hypoxia due to pulmonary hypertension in newborns, and is expected to be used clinically.
Helium is expected to act as a respiratory aid when oxygen is delivered to the constricted bronchi of asthmatic patients, and has already been used in clinical practice overseas, and research is being promoted for practical application in Japan.
Xenon is approved as an anesthetic in Germany, and it is approved as a diagnostic agent for cerebral blood flow distribution in Japan.
Carbon monoxide, like nitric oxide, has a research result that activates guanyl cyclase, which is involved in the relaxation (dilation) of blood vessels, and research for practical use is being conducted.
Carbon dioxide is effective as an awakening action during altitude sickness and anesthesia, and as a preventive action for pulmonary diastolic dysfunction after surgery. In addition, premature infants are expected to have the effect of shortening artificial ventilation as a result, and research for practical application is being conducted.

  In this way, research and development for various types of gas other than those already in practical use has been actively conducted, and their clinical use is expected to expand in the future. Yes.

  Since medicinal gases can be handled as gases, they are introduced into the body through breathing, but these gases always maintain an effective concentration range in the patient's lungs, and are adjusted to the condition. It is necessary to change the concentration. In addition, a large amount of gas is required for continuous administration according to the patient's breathing. Therefore, in clinical use, it is difficult to directly administer medicinal gas adjusted to a certain concentration in advance from a cylinder or the like without adjusting the concentration.

  For this reason, medicinal gas adjusted to be higher than the effective concentration is filled in a cylinder etc. at high pressure and used as a supply source, and the flow rate is adjusted and added to the gas supplied from the ventilator and diluted. Thus, a method for causing a patient to breathe an effective concentration of medicinal gas is efficient and practical. That is, when using medicinal gas, an administration method using a precise gas concentration or flow rate control mechanism linked with a ventilator or the like is considered to be appropriate.

  As an example of the prior art that has been put to practical use using such a method, there is a nitrogen oxide delivery device disclosed in Patent Document 1. This device is used in combination with a ventilator, controls the necessary flow rate of a medicinal gas of known concentration according to the inspiratory flow rate in the breathing circuit discharged from the ventilator, introduces it into the patient circuit, and keeps constant for the patient A device that achieves dosing at a concentration.

JP 7-194705 A

Reiko Hirose, Neonatal Respiratory Therapy Monitoring Forum Proceedings, (2007) Gas Medina 2006, Gas Review Co., Ltd., p. 27-30, (2007) G. S. Marks, et al. , Trends Pharmacol Sci, 12, p. 185-188, (1991) Gonzalo Mariani, et al. , PEDIATRICS Vol. 104 No. 5, p. 1082-1088, (1999) Emergency / Intensive Care, Kazufumi Okamoto, General Medical Co., Ltd., Vol. 17, no. 11, 12, p. 1252, (2005) Respiratory therapy revised 3rd edition, supervised by Katsuo Numata, Shujunsha, p. 42, (2001)

  However, the timing at which the medicinal gas administered to the patient can be effectively introduced into the patient is during the patient's inspiration (inhalation phase), and otherwise (the expiratory phase), the medicinal gas is introduced into the patient. There is nothing. Therefore, since the device of Patent Document 1 controls the dosage of the medicinal gas based on the flow rate of the circuit gas, as long as the circuit gas supplied from the ventilator is flowing, it is also in the expiratory phase. Regardless, the medicinal gas will continue to be administered, and the medicinal gas administered to the expiration phase is exhausted wastefully without being introduced into the patient's body. Moreover, in general, the time ratio (I: E ratio) between the inspiratory phase and the expiratory phase in artificial respiration therapy is 1: 2 (see Non-Patent Document 5 above), and the time spent for exhalation is twice that of inhalation. Therefore, the gas waste during this period cannot be ignored.

  As described above, in the apparatus of Patent Document 1, the consumption amount of the pharmaceutical gas is much larger than the actual required amount, and there are many gases that are exhausted without being introduced into the patient. It is. In addition, depending on the type of gas used as a medicinal gas, it may cause toxicity to the human body when it exceeds the amount required by the human body, or may adversely affect the environment. There is also concern that it may lead to environmental damage such as health damage and global warming.

  The present invention has been made to solve such a problem, and an object of the present invention is to provide a medicinal gas administration device capable of reducing wasteful consumption of medicinal gas and taking safety and environment into consideration. And

To achieve the above object, the medicinal gas administration device of the present invention is a medicinal gas administration device that introduces medicinal gas into the gas flowing through the breathing line of the artificial respiration means,
The gist of the present invention is that the introduction of the medicinal gas is intermittently performed in conjunction with the exchange of the expiration phase and the inspiration phase of the artificial respiration in the artificial respiration means.

  In the present invention, since the introduction of the medicinal gas is intermittently performed in conjunction with the change of the exhalation phase and the inspiration phase of the artificial respiration in the artificial respiration means, the introduction of the medicinal gas in accordance with the inspiration phase of the artificial respiration can be performed. It becomes possible, and the consumption of the medicinal gas can be greatly reduced by reducing the medicinal gas that has been conventionally exhausted. In addition, the amount of medicinal gas discharged into the treatment environment can be greatly reduced, and health damage to medical personnel and environmental destruction such as global warming can be prevented. Furthermore, by suppressing the consumption of the medicinal gas, it is possible to contribute to the reduction of medical costs due to the reduction of medical costs and the frequency of exchanging the medicinal gas cylinders.

  In the present invention, when the timing of introduction of the medicinal gas is controlled by using a flow rate change in the breathing line of the artificial respiration means as a trigger, the medicinal gas introduction timing can be surely matched to the inspiratory phase of the artificial respiration. It is possible to reduce wasteful consumption of medicinal gas and prevent health damage and environmental destruction. Furthermore, by suppressing the consumption of the medicinal gas, it is possible to contribute to the reduction of medical costs due to the reduction of medical costs and the frequency of exchanging the medicinal gas cylinders.

  In the present invention, when the timing of introduction of the medicinal gas is controlled using a pressure change in the breathing line of the artificial respiration means as a trigger, the medicinal gas introduction timing can be surely matched to the inspiratory phase of the artificial respiration. It is possible to reduce wasteful consumption of medicinal gas and prevent health damage and environmental destruction. Furthermore, by suppressing the consumption of the medicinal gas, it is possible to contribute to the reduction of medical costs due to the reduction of medical costs and the frequency of exchanging the medicinal gas cylinders.

  In the present invention, when the timing of introducing the medicinal gas is controlled by using the operation of the pressure fluctuation means and / or the flow rate fluctuation means in the artificial respiration means as a trigger, the introduction timing of the medicinal gas is set to the inspiration phase of the artificial respiration. It is possible to reduce the wasteful consumption of medicinal gas and prevent health damage and environmental destruction. Furthermore, by suppressing the consumption of the medicinal gas, it is possible to contribute to the reduction of medical costs due to the reduction of medical costs and the frequency of exchanging the medicinal gas cylinders.

  In the present invention, when detecting the concentration of the medicinal gas in the breathing line of the artificial respiration means and controlling the medicinal gas concentration when introducing the medicinal gas based on the detected concentration, the medicinal property The gas administration concentration is always properly controlled to enable appropriate treatment.

It is a block diagram which shows one Embodiment of the pharmaceutical gas administration apparatus of this invention. It is a diagram which shows the result of Example 1. FIG. 6 is a diagram showing the results of Example 2. FIG. It is a diagram which shows the result of a comparative example.

  Next, the best mode for carrying out the present invention will be described.

  FIG. 1 is a diagram showing a pharmaceutical gas administration device 1 to which the present invention is applied. This medicinal gas administration device 1 uses an artificial respirator 2 as an artificial respiration means, introduces medicinal gas into the gas flowing through the breathing line 3 of the ventilator 2, and converts it into the circuit gas flowing through the breathing line 3. On the other hand, medicinal gas is administered to the patient 4 by mixing medicinal gas so as to have a predetermined concentration and artificially breathing the patient 4 through the mask 7 attached to the breathing line 3. is there. As the circuit gas for artificial respiration, for example, air with increased oxygen concentration, oxygen, air, or the like can be used.

  More specifically, in this example, the breathing line 3 of the ventilator 2 is an inhalation line 12 that sends circuit gas supplied from the ventilator as inhalation to the patient 4 via the mask 7 from the ventilator 2. And an exhalation line 11 for sending circuit gas as exhalation from the patient 4 to the ventilator 2 through the mask 7.

  In this example, an introduction adapter 8 for introducing a medicinal gas to the circuit gas supplied from the ventilator flowing through the inspiratory line 12 is provided in the inspiratory line 12. The introduction adapter 8 reduces the time loss from the introduction and mixing of the medicinal gas to the circuit gas supplied from the ventilator until it reaches the mask 7 that is the mouth of the patient 4. 12 is arranged in the immediate vicinity of the mask 7.

  The inspiratory line 12 is provided with a detector 9 that detects at least one of the flow rate and pressure of circuit gas supplied from a ventilator that flows through the inspiratory line 12. In this example, the detector 9 detects both the flow rate and pressure of the circuit gas supplied from the ventilator flowing through the inhalation line 12.

  Further, the ventilator 2 is provided with an exhalation valve 10 at the end of the exhalation line 11, that is, in the vicinity of the connection portion between the exhalation line 11 and the ventilator 2. The ventilator 2 intermittently varies the pressure of the circuit gas supplied from the ventilator flowing through the breathing line 3 by performing an opening / closing operation or an opening degree adjusting operation of the exhalation valve 10.

  That is, by closing the exhalation valve 10 or reducing the opening, the pressure of the circuit gas supplied from the ventilator flowing through the breathing line 3 increases, and at the same time the flow rate temporarily decreases. The circuit gas supplied from the ventilator is forcibly introduced into the lungs of the patient 4 due to the pressure increase at this time, and an inspiration phase is formed. On the other hand, by opening the exhalation valve 10 or increasing the opening degree, the pressure of the circuit gas supplied from the ventilator flowing through the breathing line 3 decreases, and at the same time the flow rate temporarily increases. Due to the pressure drop at this time, the circuit gas supplied from the ventilator is forcibly discharged from the lungs of the patient 4 to form an expiration phase.

  Thus, the exhalation-valve 10 functions as pressure fluctuation means and flow rate fluctuation means in the ventilator 2, and functions as means for forming the expiration phase and the inspiration phase of the artificial respiration and their interchange.

  On the other hand, in this example, the medicinal gas administration device 1 of the present embodiment includes a supply line 23 that receives a medicinal gas supply from the medicinal gas cylinder 5 filled with medicinal gas via the pressure regulating valve 6, and the above An introduction line 21 is provided in communication with the introduction adapter 8 to introduce the medicinal gas into the breathing line 3.

  In addition, the medicinal gas administration device 1 is connected to the gas line 24 connected from the supply line 23 to the introduction line 21 from the supply line 23 side to the shutoff valve 16, the check valve 17, the three-way switching valve 18, the flow control valve 19, An on-off valve 20 is provided.

  The shutoff valve 16 shuts off the supply of the pharmaceutical gas from the supply line 23 when the apparatus is stopped. The check valve 17 prevents the backflow of the pharmaceutical gas flowing through the gas line 24. The three-way switching valve 18 enables the purging by switching the medicinal gas flowing through the gas line 24 to the purge line 22.

  The flow rate control valve 19 controls the flow rate of the medicinal gas flowing through the gas line 24 and controls the flow rate of the medicinal gas introduced from the introduction line 21 to the breathing line 3, that is, the introduction amount, thereby feeding the mask 7 into the mask 7. The concentration of the pharmaceutical gas with respect to the gas is adjusted, and the dosage of the pharmaceutical gas to the patient 4 is adjusted. The on-off valve 20 controls the introduction start timing and the introduction time for introducing the medicinal gas into the breathing line 3 by intermittently opening and closing.

  The medicinal gas administration device 1 includes a central processing unit 13. As will be described later, the central processing unit 13 controls the opening of the on-off valve 20 by using a pressure change of the breathing line 3, a change in the flow rate of the breathing line 3, and an operation of the exhalation valve 10 as a trigger. The introduction of gas is controlled to be intermittently performed in conjunction with the exchange of the expiration phase and the inspiration phase of the artificial respiration in the ventilator 2.

  The central processing unit 13 receives the pressure of the circuit gas flowing in the breathing line 3 detected by the detector 9 and opens the on-off valve 20 using a pressure change in the breathing line 3 (in this example, the intake line 12) as a trigger. Valve control can be performed to control the start timing of introduction of the medicinal gas. That is, as described above, the pressure of the circuit gas flowing through the breathing line 3 is relatively high in the inspiratory phase of artificial respiration, and the pressure of the circuit gas flowing through the breathing line 3 is relatively low in the expiratory phase of artificial respiration. Be controlled. Therefore, the pressure of the circuit gas in the breathing line 3 is detected by the detector 9, a pressure change from the low pressure phase to the high pressure phase is detected, and the opening / closing valve 20 is opened using this pressure change as a trigger to start introduction of medical gas. Timing can be controlled.

  The central processing unit 13 receives the flow rate of the circuit gas flowing through the breathing line 3 detected by the detector 9, and the opening / closing valve 20 is triggered by the flow rate change in the breathing line 3 (inhalation line 12 in this example). The opening timing of the medicinal gas can be controlled by performing the valve opening control. As described above, when the artificial breath is switched from the expiratory phase to the inspiratory phase, the flow rate of the circuit gas flowing through the respiratory line 3 temporarily decreases. Therefore, the flow rate of the circuit gas in the breathing line 3 is detected by the detector 9, a change in the flow rate that temporarily decreases is detected, and the on-off valve 20 is opened using this flow rate change as a trigger to start introduction of medical gas. Timing can be controlled.

  The central processing unit 13 receives the operation of the exhalation valve 10 (functioning as a pressure variation unit and / or a flow rate variation unit), and controls the opening and closing of the on-off valve 20 using the operation of the exhalation valve 10 as a trigger. It is possible to control the start timing of introduction of the pharmaceutical gas. That is, as described above, the expiratory phase and the inspiratory phase of artificial respiration are an exhalation valve that functions as pressure fluctuation means and / or flow fluctuation means for controlling pressure fluctuation and flow fluctuation of circuit gas in the breathing line 3 in the ventilator. The operation is switched by opening and closing 10. Accordingly, an operation for closing the exhalation valve 10 or reducing the opening degree is detected by a detection means (not shown), an operation for switching from the expiration phase to the inspiration phase in the expiration valve 10 is detected, and the opening / closing valve 20 is triggered by this operation. It is possible to open and control the introduction start timing of the medical gas.

  The central processing unit 13 controls the closing timing of the on-off valve 20, that is, the introduction / stop timing of the medical gas, and is linked to the breathing line 3 in conjunction with the change of the expiration phase and the inspiration phase of the artificial respiration in the ventilator. Introduce medical gas intermittently.

  The closing timing of the on-off valve 20 is that the pressure change from the high pressure phase to the low pressure phase of the breathing line 3 is detected, and the on / off valve 20 is closed using this pressure change as a trigger to control the introduction stop timing of the medical gas. it can.

  Further, when the switching timing of the on-off valve 20 is switched from the inspiratory phase to the expiratory phase of artificial respiration, the flow rate of the circuit gas flowing through the respiratory line 3 temporarily increases. Therefore, the flow rate of the circuit gas in the breathing line 3 is detected by the detector 9, a flow rate change that temporarily increases the flow rate is detected, and the on / off valve 20 is closed using this flow rate change as a trigger to stop the introduction of medical gas. Timing can be controlled.

  The closing timing of the on-off valve 20 can be controlled by receiving the operation of the exhalation valve 10 (functioning as a pressure variation unit and / or a flow rate variation unit) and using the operation of the exhalation valve 10 as a trigger. That is, as described above, the expiratory phase and the inspiratory phase of artificial respiration are an exhalation valve that functions as pressure fluctuation means and / or flow fluctuation means for controlling pressure fluctuation and flow fluctuation of circuit gas in the breathing line 3 in the ventilator. The operation is switched by opening and closing 10. Therefore, an operation for opening the expiratory valve 10 or increasing the opening degree is detected by a detection means (not shown), an operation for switching from the inspiratory phase to the expiratory phase in the expiratory valve 10 is detected, and the opening / closing valve 20 is triggered by this operation. The medical gas introduction stop timing can be controlled by closing.

  Here, the closing timing of the on-off valve 20 is, for example, the time since the opening of the on-off valve 20, the time after detecting the pressure change from the high pressure phase to the low pressure phase of the respiration line 3, The time after detecting the flow rate change in which the flow rate of the circuit gas temporarily increases, the time after detecting the operation of opening the exhalation valve 10 or increasing the opening, are measured with a timer (not shown), and the predetermined time It is also possible to control the progress of this as a trigger.

  Here, the valve opening control and / or valve closing control of the on-off valve 20 is controlled by using a flow rate change, a pressure change, and an operation of the exhalation valve 10 in the breathing line of the ventilator as a trigger. After the operation of the exhalation valve 10 is detected, the timing can be corrected by executing it after a predetermined time measured by a timer (not shown).

  At this time, the introduction stop timing of the medical gas may be controlled so that the administration flow rate of the pharmaceutical gas and the concentration of the pharmaceutical gas in the circuit are increased in the first half of the inhalation phase. That is, in the artificial respiration, the circuit gas is introduced into the intrapulmonary space in the body of the patient 4 during the second third of the inhalation phase, but only within the space from the upper and lower airways to the alveoli. It does not reach and the gas is not taken into the blood and does not substantially contribute to artificial respiration. In terms of time, it is said that the time required to absorb the effective gas amount in the first half of the intake phase is up to the first third of the intake phase.

  Therefore, introduction of medical gas in the first half of the inhalation phase (at least the first half 2/3, preferably the first half 1/2, more preferably the first half 1/3) so that the flow rate of the medicinal gas and the concentration of the medicinal gas are increased. By controlling the stop timing, the introduction of the medicinal gas can be matched with the actually effective artificial respiration, the medicinal gas can be further reduced, and the health damage and the environmental destruction can be surely prevented. For the valve closing timing of the on-off valve 20 at this time, for example, it is preferable to perform time control by the above-described timer because it is easy to control.

  In this embodiment, the medicinal gas is depressurized by the pressure regulating valve 6 from the medicinal gas cylinder 5 which is a supply source, and is predetermined by the flow control valve 19 via the shutoff valve 16, the check valve 17 and the three-way switching valve 18. It is controlled by the flow rate and guided to the introduction line 21. At this time, the introduction start timing and the introduction stop timing are controlled by opening and closing the on-off valve 20, and the medicinal gas is intermittently introduced into the intake line 12 through the introduction adapter 8, and the circuit gas is introduced into the introduction adapter 8. Mixed and administered to patient 4 at a predetermined concentration.

  Further, the medicinal gas administration device 1 uses, for example, a sensor (not shown) for detecting the medicinal gas concentration provided in the introduction adapter 8 to measure the medicinal gas concentration in the breathing line 3. 14 is provided. The pharmaceutical gas administration device 1 includes a concentration input unit 15 for setting and inputting the concentration of the pharmaceutical gas with respect to the circuit gas in the breathing line 3.

  Then, the concentration of the medicinal gas in the breathing line 3 of the ventilator 2 is detected by the sensor (not shown) and the concentration measuring device 14, and the central processing unit 13 generates the medicinal gas based on the detected concentration. Control the concentration of medicinal gas during introduction.

  That is, the concentration measuring device 14 measures the concentration of the pharmaceutical gas in the circuit gas in the breathing line 3 and sends it to the central processing unit 13. The flow rate control valve 19 includes a flow rate sensor (not shown), detects the flow rate of the pharmaceutical gas that passes through the flow rate control valve 19 and is introduced into the breathing line 3, and sends it to the central processing unit 13. The detector 9 detects the flow rate of the circuit gas in the breathing line 3 and sends it to the central processing unit 13.

  The central processing unit 13 first introduces a medicinal gas into the breathing line 3 at a predetermined flow rate, and measures the medicinal gas concentration in the circuit that appears as a result. The concentration filled in the cylinder of the medicinal gas to be introduced into the circuit is the known amount c, the medicinal gas flow rate is the known amount q, the flow rate supplied from the ventilator is the unknown amount Q, and the resulting medicinal properties in the circuit. When the gas concentration is a known amount C, the relationship is generally expressed as C = c · q / (Q + c · q) (1). From this relationship, the circuit flow rate supplied from the artificial respirator, which is an unknown amount, is calculated in advance by the central processing unit 13 as Q = c · q × (1−C) / C (2). Although the circuit flow Q supplied from the ventilator varies slightly at the start of inspiration and exhalation, it can be said to be almost constant throughout a series of breathing operations unless the ventilator settings are changed. Can be handled as By setting Q as a constant, the above relationship and the calculated circuit flow rate are set so that the medicinal gas concentration C in the circuit gas supplied from the ventilator in the breathing line 3 becomes the value set by the concentration input unit 15. Q is calculated as a necessary medicinal gas flow rate q = Q × C / (1-C) · c (3), and can be controlled by adjusting the opening degree of the flow control valve 19. When the circuit flow Q supplied from the ventilator changes due to a change in the ventilator settings, the change in the concentration of the medicinal gas C in the circuit is detected, thereby supplying the ventilator from the ventilator. The circuit flow rate Q is indirectly recognized, the circuit flow rate Q is calculated again from the relational expression (2), set again, and the new necessary pharmaceutical properties with the same logic as described above using the new constant Q. The gas flow rate q is derived and the flow rate control is revised. In addition, the set circuit flow rate Q of the ventilator is separately measured separately, and compared with the calculated circuit flow rate, and monitored, it is greatly reduced due to deterioration of the medicinal gas concentration sensor in the circuit, gas leakage from the circuit, etc. Activates a safety circuit, alarm, etc. when a divergence occurs.

  Thereby, the medicinal gas from the medicinal gas cylinder 5 can be introduced into the breathing line 3 while controlling the flow rate so as to be a predetermined concentration with respect to the variable gas flow rate from the gas delivery device such as the ventilator 2. .

  In this embodiment, the introduction position of the pharmaceutical gas is set near the mask 7 in the intake line 12. This eliminates delays in the addition of the medicinal gas to the inspiratory flow as much as possible, reduces the time loss from the introduction of the medicinal gas to the patient's four mouths, and achieves the accurate dosing timing of the medical gas The clinical effect on the patient 4 can be maintained.

  A circuit gas flow rate and pressure detector 9 is arranged in the vicinity of the gas supply port of the ventilator 2. Thereby, the minute change of the gas flow in the circuit of the breathing line 3 can be quickly detected, and the medicinal gas can be administered at a precise timing. The detector can also be arranged in the vicinity of the exhalation valve 10 of the exhalation line 11, and in this case as well, a minute change in the gas flow in the circuit of the breathing line 3 can be quickly detected and the accuracy is high. The medicinal gas can be administered at the timing.

FIG. 2 shows the results of Example 1 in which the medicinal gas administration apparatus 1 uses CO ₂ as the medicinal gas and administers medicinal gas using the pressure change in the breathing line 3 as a trigger.

  The lower graph is a diagram showing temporal changes in flow rate and pressure in the circuit (in the breathing line 3). It can be seen that in the inspiratory phase, the pressure is relatively higher than in the expiratory phase, and in the expiratory phase, the pressure is relatively lower than in the inspiratory phase. It can also be seen that the flow rate temporarily decreases when switching from the expiratory phase to the inspiratory phase, and the flow rate temporarily increases when switching from the inspiratory phase to the expiratory phase.

The upper graph is a diagram showing a temporal change in the flow rate of the medicinal gas to the breathing line 3 by the medicinal gas dosing device 1 and the concentration of the medicinal gas (CO ₂ ) in the circuit (in the breathing line 3). It is. It can be seen that in the first half of the inhalation phase, the flow rate of medicinal gas and the concentration of medicinal gas (CO ₂ ) are high and reach the set value or the target value. Thus, in the first embodiment, control is performed so that the administration flow rate of the pharmaceutical gas and the concentration of the pharmaceutical gas reach the set value or the target value in the first half of the inhalation phase. Note that the set value or target value here is an example and can be set as appropriate depending on the treatment method and the like.

FIG. 3 shows the result of Example 2 in which the medicinal gas administration apparatus 1 uses CO ₂ as the medicinal gas and administers medicinal gas using the flow rate change in the breathing line 3 as a trigger.

  The lower graph is a diagram showing temporal changes in flow rate and pressure in the circuit (in the breathing line 3), and is the same as in the first embodiment.

The upper graph is a diagram showing a temporal change in the flow rate of the medicinal gas to the breathing line 3 by the medicinal gas dosing device 1 and the concentration of the medicinal gas (CO ₂ ) in the circuit (in the breathing line 3). It is. It can be seen that in the first half of the inhalation phase, the flow rate of medicinal gas and the concentration of medicinal gas (CO ₂ ) are high and reach the set value or the target value. As described above, also in the second embodiment, control is performed so that the administration flow rate of the pharmaceutical gas and the concentration of the pharmaceutical gas reach the set value or the target value in the first half of the inhalation phase. It is to be noted that the set value or the target value can be appropriately set depending on the treatment method or the like, as in the first embodiment. Further, in Example 2, there is a portion where the administration flow rate of the pharmaceutical gas and the concentration of the pharmaceutical gas increase even in the expiration phase, but the flow rate change at the time of switching from the inspiration phase to the expiration phase is detected as noise. Therefore, it is possible to control so as not to detect the noise by optimizing the control system.

FIG. 4 shows the result of a comparative example in which a pharmaceutical gas was administered using CO ₂ as a pharmaceutical gas by a conventional pharmaceutical gas administration device.

  The lower graph is a diagram showing temporal changes in flow rate and pressure in the circuit (in the breathing line 3), and is the same as in the first embodiment.

The upper graph is a diagram showing changes in the flow rate of pharmaceutical gas to the respiratory line 3 and the concentration of pharmaceutical gas (CO ₂ ) in the circuit (in the respiratory line 3) over time according to the comparative example. It can be seen that there is no difference between the flow rate of the medicinal gas and the concentration of the medicinal gas in the circuit (in the breathing line 3) between the inspiratory phase and the expiratory phase, and the medicinal gas is always consumed.

Table 1 below compares the consumption of pharmaceutical gas according to Example 1 and the comparative example. The dose of medicinal gas (CO ₂ ) per inhalation phase is 106.0 ml in the comparative example, whereas it is 8.3 ml in Example 1, and the amount of medicinal gas reduced is 97. ml. 7 ml and the reduction rate was 92.2%.

  As can be seen from Examples 1 and 2 and the comparative example, both the pressure trigger method and the flow rate trigger method start the administration of the medicinal gas at the mouth of the patient 4 almost in synchronization with the start of inspiration, and the patient is in the inspiration phase. A time-targeted administration was achieved during a period when the medicinal gas could be effectively taken up into 4 lungs. In particular, in the pressure trigger method, since the pressure fluctuation is stable, the pressure change as a trigger is accurately captured, and the trigger timing and administration time are well controlled.

  As described above, in the medicinal gas administration device 1 of the present embodiment, the introduction of the medicinal gas is intermittently performed in conjunction with the exchange of the exhalation phase and the inspiration phase of the artificial respiration in the ventilator 2, It is possible to introduce a medicinal gas in accordance with the inspiratory phase of artificial respiration, and it is possible to save medicinal gas consumption by reducing the amount of medicinal gas that was conventionally exhausted. In addition, the amount of medicinal gas discharged into the treatment environment can be greatly reduced, and health damage to medical personnel and environmental destruction such as global warming can be prevented. Furthermore, by suppressing the consumption of the medicinal gas, it is possible to contribute to the reduction of medical costs due to the reduction of medical costs and the frequency of exchanging the medicinal gas cylinders.

  In addition, when the timing of introduction of the medicinal gas is controlled by using a flow rate change in the breathing line 3 of the ventilator 2 as a trigger, the medicinal gas introduction timing can be surely matched to the inspiratory phase of the artificial respiration. It is possible to reduce wasteful consumption of medicinal gas and prevent health damage and environmental destruction. Furthermore, by suppressing the consumption of the medicinal gas, it is possible to contribute to the reduction of medical costs due to the reduction of medical costs and the frequency of exchanging the medicinal gas cylinders.

  Further, when the timing of introduction of the medicinal gas is controlled by using a pressure change in the breathing line 3 of the ventilator 2 as a trigger, the medicinal gas introduction timing can be surely matched with the inspiratory phase of the artificial respiration. It is possible to reduce wasteful consumption of medicinal gas and prevent health damage and environmental destruction. Furthermore, by suppressing the consumption of the medicinal gas, it is possible to contribute to the reduction of medical costs due to the reduction of medical costs and the frequency of exchanging the medicinal gas cylinders.

  In addition, when the timing of introducing the medicinal gas is controlled using the operation of the exhalation valve 10 in the ventilator 2 as a trigger, it is possible to reliably match the timing of introducing the medicinal gas with the inspiratory phase of the artificial respiration. Thus, wasteful consumption of medicinal gas can be reduced, and health damage and environmental destruction can be prevented. Furthermore, by suppressing the consumption of the medicinal gas, it is possible to contribute to the reduction of medical costs due to the reduction of medical costs and the frequency of exchanging the medicinal gas cylinders.

  In addition, when the concentration of the medicinal gas in the breathing line 3 of the ventilator 2 is detected and the concentration of the medicinal gas when the medicinal gas is introduced is controlled based on the detected concentration, the medicinal property The gas administration concentration is always properly controlled to enable appropriate treatment.

  The medicinal gas applied to the present invention is not particularly limited as long as it is a gas showing medicinal properties, such as carbon dioxide and nitric oxide, for example, helium, carbon monoxide, and the like. It is the meaning which can apply gas.

  In the above-described embodiment, an example in which the ventilator 2 is used as the ventilator is described. However, the ventilator to which the present invention can be applied is not limited to the ventilator 2 as described above. For example, a hand ventilator that manually squeezes the bag and supplies circuit gas for artificial respiration from the breathing line to the patient, such as a bag valve mask or a Jackson lease circuit device, or a patient with only an inspiratory circuit as a breathing line The present invention can also be applied as an artificial respiration means of the present invention to an air supply device of a single breathing circuit for supplying circuit gas to the apparatus.

1: Medical gas administration device 2: Ventilator 3: Breathing line 4: Patient 5: Pharmaceutical gas cylinder 6: Pressure regulating valve 7: Mask 8: Introducing adapter 9: Detector 10: Expiratory valve 11: Expiratory line 12: Intake line 13: Central processing unit 14: Concentration measuring device 15: Concentration input unit 16: Shut-off valve 17: Check valve 18: Three-way switching valve 19: Flow control valve 20: On-off valve 21: Introduction line 22: Purge line 23: Supply line 24: gas line

Claims (5)

A medicinal gas administration device for introducing medicinal gas into a gas flowing through a breathing line of an artificial respiration means,
A medicinal gas dosing apparatus characterized in that the medicinal gas is introduced intermittently in conjunction with the exchange of the exhalation and inhalation phases of artificial respiration in the artificial respiration means.   The medicinal gas administration device according to claim 1, wherein the timing of introduction of the medicinal gas is controlled by using a flow rate change in the breathing line of the artificial respiration means as a trigger.   2. The medicinal gas administration device according to claim 1, wherein the timing of introducing the medicinal gas is controlled by using a pressure change in the breathing line of the artificial respiration means as a trigger.   2. The medicinal gas administration device according to claim 1, wherein the timing of introduction of the medicinal gas is controlled by the operation of the pressure fluctuation means and / or the flow rate fluctuation means in the artificial respiration means as a trigger.   The concentration of the medicinal gas in the breathing line of the artificial respiration means is detected, and the concentration of the medicinal gas when the medicinal gas is introduced is controlled based on the detected concentration. A pharmaceutical gas administration device according to claim 1.

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