JPS6223496Y2 - - Google Patents

Description

[Detailed Description of the Invention] The present invention relates to an independent lung ventilation device used to forcefully ventilate the left and right lungs independently during artificial respiration or open-heart surgery.

The above-mentioned independent ventilation has been practiced since it was reported to be useful in open-heart surgery, and a ventilator as shown in FIG. 1 has already been used as a ventilator for the surgery.

In other words, with this type of device, the ventilation volume of the lung on the side with a lung disease or the lower lung when surgery is performed in the lateral position is lower than that of the other lung. Forced ventilation must be performed by setting a ventilation flow rate commensurate with the ventilation volume of each lung.

Therefore _, in the conventional device shown _in FIG.
A first branch D 1 and a second branch D ₂ are connected in series to the first and second ventilators B _{1 and} B ₂ and the first and second ventilation monitors C ₁ and C ₂ , respectively. The first and second tubes E 1 and E ₂ of the double lumen endotracheal tube E are connected to the distal ends of the respective shunts D _{1 and} D ₂ , respectively, and the endotracheal tube E is connected to each lung as shown in the figure.
It is configured to be used by being set in the trachea G so as to communicate with F ₁ and F ₂ .

For this reason, the conventional device requires two sets (A ₁ , A ₂ , B ₁ , B ₂ ) of an anesthesia machine and a ventilator, which not only increases the cost, but also In order to set ventilation volumes corresponding to the left and right lungs, separate anesthesia machines, ventilators, and ventilation monitors must be adjusted, and as a result, the adjustment takes time, especially during anesthesia. The complicated flow control of ventilators and ventilators is performed on the first and second branches.
Since this is required for D ₁ and D ₂ respectively, the operability is poor.

In view of the above-mentioned drawbacks of the conventional example, the present invention enables independent ventilation with only one set of artificial respirators by installing a new intake resistance valve with unique performance in the appropriate location, thereby reducing the cost. The purpose is not only to make the device available, but also to eliminate the need for complicated flow control in ventilators, etc., and to significantly improve the operability of this type of device.

To describe the present invention in detail with reference to the illustrated embodiment, the ventilation source 1 shown in FIG.
It consists of an anesthesia machine A and a ventilator B connected in sequence, and in this case it is used for open-heart surgery, but if you are just performing artificial respiration, of course the anesthesia machine A is not necessary. The ventilation source 1 is constituted only by the artificial breather B.

The outlet path 2 of the ventilation source 1 branches into a first ventilation shunt 3 ₁ and a second ventilation shunt 3 ₂ , and the tips of the shunts 3 ₁ and 3 ₂ are connected to the known The first tube E ₁ of the double lumen endotracheal tube E of
Second tubes _E2 are connected to each other.

Here, while a first ventilation monitor _C1 is interposed in the first ventilation shunt ₃₁ , the second ventilation shunt ₃₂ has an inspiratory resistance that will be described in detail later. A valve 4 and a second ventilation monitor C ₂ are interposed in series, and H in the figure indicates the diseased area in one lung F _2. When using this device, as shown in the figure, By setting the double-lumen endotracheal tube E in the trachea G, the second tube E2, which communicates with the second ventilation branch ₃₂ provided with the inspiratory resistance valve ₄ , is connected to the area where the diseased area H is located. In lung F ₂ (or lower lung in lateral position), first tube E ₁
will open into the other healthy lung F ₂ (or upper lung), respectively.

Now, regarding the above-mentioned intake resistance valve 4, specific examples are shown in FIGS. 3 and 4, but the invention is not limited to this, and the following conditions are met: The flow rate is controlled for the inhaled air I in the lungs, but the above control is canceled for the exhaled air J in the same lungs.

(b) Second, the above-mentioned control flow rate is adjustable.

A different structure may be adopted as long as it satisfies the following.

The inspiratory resistance valve 4 in FIG. 3 connects an inspiratory side pipe 5 on the ventilation source 1 side and an expiratory side pipe 6 on the lung side through a connecting pipe 7 to form a communicating large-diameter space 8. At the end of the intake side pipe 5, a through-hole bearing plate 9 is provided in the same space 8.
The slide tube 10, which is fixedly installed and slidably fitted to the exhalation side tube 6, has an adjustment port 11 formed by a large number of cut grooves at its distal end protruding toward the communicating large-diameter space 8. 11... are provided.

Further, a peripheral wall 10' near the base end of the cylinder 10
Adjustment pins 12, 12 protruding radially outward from
The adjustment pins 12, 12 are loosely fitted into adjustment slots 13, 13 drilled in the expiration side tube 6, and by screwing the adjustment ring 15 screwed onto the outer peripheral spiral portion 14 of the expiration side tube 6, the adjustment pins 12, 12 can be adjusted. By varying the position of the slide tube 10, the extent to which the slide tube 10 extends from the exhalation side pipe 6 to the communicating large-diameter space 8 can be adjusted, and the size of the adjustment ports 11, 11... can be freely adjusted. It is made so that it can be adjusted.

Furthermore, the resistance valve body 16 is composed of a valve plate 17 and a shaft pin 18 fixed to the valve plate 17 in a perpendicular manner. The valve plate 17 is slidably supported through the portion 10'', so that the valve plate 17 can freely abut against the end of the slide cylinder 10 at which the adjustment ports 11, 11, . . . are opened.

Therefore, in the intake resistance valve 4, the intake side pipe 5
When more intake air I flows in, the intake air passes through the through hole 9' of the through hole bearing plate 9, and enters the adjustment ports 11, 11, . . . which are open in the communicating large diameter space 8.
... will flow into the next stage second ventilation monitor C ₂ via the slide tube 10 and the exhalation side tube 6.
Next, the exhaled air J from the lungs flows in the opposite direction, so that it flows against the valve plate 17 of the resistance valve body 16, and the shaft pin 18
slides, and as a result, the valve plate 17 moves to the right until its stopper 17' presses against the through-hole bearing plate 9. As a result, the end of the slide cylinder 10 becomes open, so that the above-mentioned intake air At the time of I, the adjustment ports 11, 11, .

At this time, by screwing the adjustment ring 15 forward or backward as described above, the slide tube 10
The degree of protrusion from the exhalation side pipe 6 can be adjusted, and thereby the size of the adjustment ports 11, 11, . . . can be adjusted to control the flow rate for inhalation.

Next, regarding the intake resistance valve 4 shown in FIG.
A flow rate adjustment valve 2 having an adjustment screw 20 is installed in a connecting pipe 7 provided between the intake side pipe 5 and the exhalation side pipe 6.
The valve plate 17 of the resistance valve body 16 is provided with communication holes 17', 17'..., and the shaft pin 18 is connected to a through-hole shaft bearing fixed to the intake side pipe 5. It is slidably fitted into the shaft opening 19 in the plate 9, and when the intake air I enters as shown in the figure,
The intake air I flowing in from the through hole 9' of the same plate 9 presses against the inflow valve port 22, the valve through hole 17' of the valve plate 17,
From 17'..., it passes through the flow rate adjustment valve 21,
It will flow into the exhalation side pipe 6.

Next, in the case of expiration J, the exhalation side pipe 6 passes through the valve 21 and is applied to the valve plate 17, which causes the resistance valve body 16 to move to the right.
7 is separated from the inflow valve port 22, thereby canceling the flow rate control for the exhalation J,
Of course, the adjustment screw 22 allows the ventilation flow rate to be adjusted to a desired degree.

The present invention, as embodied by the above embodiments,
From a ventilation source 1 comprising at least a ventilator B, a first ventilation shunt ₃₁ and a second ventilation shunt 32 are branched, each branch being connected to a second ventilation shunt ₃₂ of the double lumen endotracheal tube E. 1 tube E ₁ , 2nd tube
A first ventilation monitor C ₁ is connected to the first ventilation shunt 3 ₁ , and a first ventilation monitor C ₁ is connected to the second ventilation shunt 3 ₂ to control the flow rate of lung intake I. ,
The control is canceled for lung exhalation J, and the control flow rate is made variable by interposing the inspiratory resistance valve 4 and the second ventilation monitor _C2 , so that the ventilator B If the supply amount is determined in advance according to the patient, and the degree of flow restriction of the inspiratory resistance valve 4 is adjusted according to the diseased lung or the lower lung, it is possible to supply the right and left lungs respectively. Forced ventilation with an adapted flow rate can be performed, and therefore not only does complicated flow control by a ventilator become necessary, but the ventilation source 1 can also be replaced by a single ventilator, etc. Therefore, an inexpensive device can be provided, and of course, since there is no flow rate control for expiration of the lungs that are ventilated from the flow path on the side where the inspiratory resistance valve 4 is interposed, normal forced ventilation can be realized. .

[Brief explanation of the drawing]

Fig. 1 is an explanatory diagram of piping showing a conventional lung independent ventilation device, Fig. 2 is an explanatory diagram of piping of a ventilator according to the present invention, and Figs. 3 and 4 are different examples of inspiratory resistance valves that can be used in the device. FIG. 1...Ventilation source, 3 ₁ ...First ventilation shunt, 3
₂ ... Second ventilation shunt, 4... Intake resistance valve, B...
…Respirator, C ₁ …First ventilation monitor, C ₂ …
...Second ventilation monitor, E...Double lumen endotracheal tube, _E1 ...First tube, _E2 ...Second
Tube, F ₁ , F ₂ ... Lungs, G ... Trachea, I ...
Inhalation, J...exhalation.

Claims (1)

[Scope of utility model registration request] A first tube of a double lumen endotracheal tube is set in the trachea by branching off a first ventilation branch and a second ventilation branch from a ventilation source comprising at least a ventilator. , connected to the second tube, and connected to the first ventilation shunt.
A ventilation monitor is interposed, and the second ventilation shunt is provided with an inspiratory resistance valve that controls the flow rate for lung intake, releases the control for lung exhalation, and makes the controlled flow rate variable. and a second ventilation monitor.