WO2010134894A1

WO2010134894A1 - Portable pneumothorax device

Info

Publication number: WO2010134894A1
Application number: PCT/TR2010/000098
Authority: WO
Inventors: Volkan Bayraktar
Original assignee: Volkan Bayraktar
Priority date: 2009-05-20
Filing date: 2010-05-18
Publication date: 2010-11-25
Also published as: TR200903881A2

Abstract

Pneumothorax is filling of the pleural cavity of the lungs with air and the occurrence of lung collapse. It may arise from various factors like traffic accidents, wounding from firearms, athletic injuries. Portable pneumothorax device provides many conveniences in pneumothorax treatment. The pressure sensor (10 or 16) and the vacuum motor constitute the main features of the present invention. System depends simply on discharging of the air from the intrapleural cavity by detection of the pressure in the pleural cavity with the pressure sensors (10 or 16) and evaluation thereof at the microprocessor and providing turning back of the intrapleural pressure to the normal values. The invention which decreases the treatment period to considerably low degrees (from days, weeks to hours and even minutes), the sensation of pain of the patient and reduces the cost of the treatment to very low degrees, enables overcoming of the serious difficulties faced in pneumothorax treatment.

Description

DESCRIPTION

PORTABLE PNEUMOTHORAX DEVICE

Technical Field

Present invention relates to the systems used in the treatment of pneumothorax. Said invention enables the treatment of pneumothorax to be completed in very short time and also is designed for the purpose of enhancing the comfort of the patient as far as possible.

Background of the Invention

Pneumothorax, in the simplest term, is filling of the pleural cavity of the lungs with air and the occurrence of lung collapse accordingly. Pneumothorax is divided into two groups as spontaneous and traumatic. Spontaneous pneumothorax occurs by the rupture of the lung tissue and bleeding of the air into the pleural cavity from the respiratory track. Spontaneous pneumothorax may appear sometimes as a result of the destruction and rupture of the pleural tissue depending on the disease like KOAH, pulmonary tuberculosis, asthma, lung cancer, bronchiectasis and pulmonary abscess; and sometimes in the healthy persons who do not suffer from any pulmonary disease. Traumatic pneumothorax on the other hand is the opening of the pleural cavity to the atmosphere from the chest wall in consequence of the trauma. Leading causes of the pneumothorax which constitutes the penetran and obtuse traumas and which may arise from several factors are, traffic accidents, athletic injuries, falling down from high, wounding from firearms, wounding from cutter tools, pounding and injuries from certain accidents.

From a physiological point of view, the pleural pressure is 756 mm Hg in average whereas the atmospheric pressure is 760 mm Hg. The pressure in the lung is calculated over water (H₂O). The reason is that the changes in the pressure can be traced easier in water since the pressure difference changes in wider ranges in the water owing to the fact that the pressure of the water is low. The atmospheric pressure (760 mmHg) is assumed to be the limit (0 cm H₂O). A simple comparison is made here since the density of 1 cm H₂O is 1 , whereas that of 1 mm Hg is 1.3. 4 mm Hg » 5 cm H₂O. By this way the pleural pressure is assumed as -5 cm H₂O. Certainly, as this value may show little fluctuations from person to person (like infant-old), it may also show changes in the pleural cavity (in the apex, medial, in the region close to the diaphragm).

In case of pneumothorax, this pressure is 0 (zero) cm H₂O or in the higher positive values and the lung collapses, respiration drops off to minimal levels. What needs to be done is to restore this negative pressure to the required value. In pneumothorax, the amount of air in the pleural cavity changes between 1-3 liters in average.

The most commonly used treatment system in this sector is water drainage system. The water drainage system is composed of a lantern like structure which has connection to outside and in which 300 ml normal saline in average is found; and a catheter, one end of which is connected to this normal saline and the other end of which is connected to the intrapleural cavity. In the treatment with water drainage system, the patient, off his own bat, assures increase in the intrapleural pressure by narrowing the intrapleural cavity by practicing stiff expiration or respiration exercises. Increased pressure in the pleural cavity overcomes that of the normal saline inside the catheter and is discharged almost effervescing from the normal saline inside the lantern like structure. On the other hand, when the patent makes inspiration, i.e. reduces the pressure in the pleural cavity; depending also on the gravity, the normal saline inside the catheter can not reach to the pleural cavity. By this way, the air in the pleural cavity is discharged in a way similar to a non return (one way) valve system. Certainly, because of the expiration and respiration exercises in the course of this process, depending on the patients attempt for discharging of the air off his own bat, the treatment may last for days, weeks, even for months in the serious cases. Moreover, in the course of stiff expiration and respiration exercises, the catheter placed inside the pleural cavity of the patient, by contacting with the pleuras at once, causes considerable pains to arise.

The other systems used in the treatment, operates directly in the non return valve system. Among these valve systems, Heimlich valve and tru close troracic vent systems are found.

In the Heimlich valve system, when the pleural pressure increases, air is discharged from the central valve. And when the pleural pressure decreases, the structure of the central valve is collapsed and air entrance into the pleural cavity is blocked. By this way, discharging of air inside the pleural cavity is enabled. However as there is no opportunity to trace the pressure in the pleural cavity, treatment is not achieved completely and a portion of the air may rest in the pleural cavity. Besides being rarely used, this system is generally applied in urgent pneumopthorax cases. For the complete treatment, once more, water drainage is preferred.

The other, the tru close troracic vent system is a treatment system which is recently introduced to the market. Yet again, it comprises a non return valve system in the structure. A cap structure found in the system, functions as a valve and enables the discharge of the air in the pleural cavity. Its only advantage against the water drainage is that it is portable. But again, the drawbacks seen in the water drainage come out like the treatment period being long and sensation of pain being acute.

The systems disclosed in US Patent No. 5419776 and US Patent No. 4813941 as well operates in the non return valve system. Besides having fine security features and being applicable in urgent cases, again these systems show the drawbacks in the systems like tru close troracic vent system.

Drawings Which Will Be Helpful in Understanding The Invention The figures relating to the invention which is designed to be able to overcome the aforementioned disadvantages are:

Figure 1. is the top view of the invention.

Figure 2. is the bottom view of the invention. Figure 3. is the side view of the invention.

Figure 4. shows the localization of the pressure sensor in the air channel.

Figure 5. shows another pressure detection system which may be used in the invention.

Figure 6. shows the localization of the liquid bag, which will enable the discharge of the liquid that may come from the pleura, in the air channel.

Figures 1 , 2, 3 according to the invention are the external views of the system in design state. For this reason these figures are not stable and may be realized in different designs in the future. The parts in the drawings are enumerated and the correspondences of which are shown in below.

1) Screen in which the pressure difference and the applied operations may be monitored I

2) On button and automatic operation button

3) Manual operation button

4) Aspiration speed increasing button

5) Aspiration speed decreasing button

6) Channel on/off button (from the main cap)

7) Aspiration button

8) Entrance part of the channel (the part where also the catheter is integrated)

9) Exit part of the channel

10) Mini differential pressure sensor

11) The stand in the atmosphere connected channel part of the pressure sensor

12) The stand in the pleural cavity connected channel part of the pressure sensor

13) Atmosphere connected part of the channel (is a part of 17 at the same time)

14) Pleura connected part of the channel (is a part of 17 at the same time)

15) Main cap

16) Normal pressure sensor

17) Channel (contains also 13 and 14)

18) Liquid collection bag

19) Cap of the liquid bag

Description of the invention

The pressure sensor (10 or 16) and the vacuum motor constitute the main features of the present invention. The system depends simply on measuring the intrapleural pressure and depending on this pressure, discharging the excess air via a vacuum pump system like vacuum motor, turning the intrapleural pressure back to the required value. To go into particulars; a mini differential pressure sensor (10) or two normal pressure sensors (16) which is able to reflect the difference by measuring the atmospheric pressure and pleural pressure, a vacuum motor which is able to provide discharge of the air in the pleural cavity according to the values obtained from the pressure sensor (10 or 16) and turn the pressure values of the pleural cavity back to the normal pressure values, a battery which will provide energy to the system, a channel (17) which will provide the discharging of the air from the pleural cavity, main cap (15) in this channel, which will take charge in the regulation by being closed in certain periods, an integrable liquid bag (18) for collecting the liquid when the liquid comes to the channel (blood, pleural liquid etc.) and a functionally closing cap (19) in the mouth of this bag (18) and a microprocessor which will fix the organization between these mentioned structures, constitute the main features of the invention. Being inclined towards the liquid bag (18) as shown in Figure 6, the lower part of the channel (17) enables the liquid in the channel to be transferred easily. In the channel (17), the pressure sensor (10) is on the main cap (15) as shown in Figure 4, atmosphere stand (11) will be on the atmosphere part (13) of the channel, pleura stand (12) will be on the pleural part (14) of the channel. Pressure detection system (10, 11 , 12) apart from this, may also be designed by locating the 2 different pressure sensors (16) to suitable places in the atmosphere (13) and pleura (14) related parts of the channel (13) and transferring again the difference of both parts (i.e. atmosphere and pleura) to the system. In addition to this, when looked from the outside, there will be the functional buttons (2, 3, 4, 5, 6, 7), screen (1) in the Figure 1 , an belt and adhesive tape integrable to the sides of the invention and which will be able to provide the stabilization of the body. Of course as mentioned before, there may be differences in the external structure of the invention in the design state.

Working system of the invention is as follows. First of all a catheter in integrated to the entrance part of the channel (8) of the invention as in Figure 2. Later on, the region to which invasion will be made is anaesthetized and with the aid of a lancet and a clamp the region is cut and pleura is reached, the catheter is placed into the pleura. From now on, the invention is associated with the pleural cavity. Then the regulation is started by switching the on and automatic operation button (2). The pressure sensor (10 or 16) measures the pressures and evaluates. For this, one pressure stand (11) of the mini differential pressure sensor (10) which is found localized on the main cap (15) is on the pleura connected part (13) of the channel (17), the pressure stand (12) is on the atmosphere associated part (14). Apart from this, as mentioned before, there may be used 2 different pressure sensors (16) and the pressure difference is detected and transferred to the system. In the end, the pressure difference between the two media is detected and transferred to the microprocessor. Microprocessor evaluates the pressure difference and does the regulation. It directs the vacuum motor for discharging of more air if the pleural pressure is closer to positive or in other words if there is much air in the pleura; and for discharging of less air if the value is closer to negative or in other words if there is less air. However since the air will gradually decrease in the course of this discharge, like a positive feedback mechanism, the air discharge decreases in each subsequent discharging process. Discharging periods of the air in the pleural cavity is regulated with the aid of main cap (15) in the channel. While the automatic system is working, the main cap (15) in the air channel (17) is closed in functional frequency. In each closure of the cap (15), the pressure sensor system (10 or 16) will measure the pressures again and re-regulates the system. Again similar to the positive feedback mechanism, is the air in the pleural cavity is much the closure time period of the cap (15) is wide, if it is less, the closure time period of the cap (15) is short. Similarly, since the air in the pleural cavity will gradually decrease in the course of process, the time period of the main cap (15) will gradually shorten. This gradual decrease of the time period and air discharge in every step is for ensuring the approach to the desired pleural pressure value and for gradually getting sensitive and reaching the desired pleural pressure value.

The bottom part of the channel (17) on the other hand, as in Figure 6, will be inclined towards the part to which the liquid bag (18) will be integrated. By this way the filling of the liquids, like blood that come from the pleural cavity, to the liquid bag (18), will be easier. Besides, closure of the cap of the liquid bag (19) after the closure of the main cap (15), will enable the right detection of the pressure by preventing the air leakage. This structure will be in the associated part of the channel (17) to the pleura (14).

The invention will also own a warning system. It will warn us by an audible signal when the operation is completed. Apart from this, there will also be an alarm warning system. In other words, this alarm system, which may also be named as security warning system, is to provide security in case of possible failures of the invention. The system will give warning when the pleural pressure reaches to the critical limits at which serious complications may occur because of any problem. If there is no problem in the invention; system will both give an audible warning (this audible warning will be different from the sound which warn at the end of the process) will and also try to compensate the complications by making regulation. If there is any problem occurred in the invention, the system will both give an audible warning and also the progress of the complication will be prevented by automatic closure of the main cap (15) in the channel (17).

The invention will provide not only an automatic operation but also a manual operation. This is provided by the manual operation button (3) in Figure 1. After switching the manual operation switch (3) on and changing to manual; process may be carried out by tracing the values from the screen (1) with the aspiration speed increasing switch (4), aspiration speed decreasing switch (5) and the channel on/off switch (6).

It will also provide another usage opportunity as a portable aspirator device to be applied in surgical and various operations with the aspiration switch (7) found in the structure of the invention.

The advantages of the invention against the systems used in the prior art are as follows:

Depending on the active discharging of the pleural air, the invention will reduce the period of the treatment into hours or even into minutes, whereas in the other systems the treatment lasts for days, weeks.

Colliding of the catheter to the pleuras and arising of the considerable pains, depending on the sudden maneuvers like various respiration exercises and stiff expiration that the patient practice to increase the intrapleural pressure in the other systems will have also been overcome by active vacuuming of the pleural air in this invention. Because by this system, the active discharging of the air from the intrapleural cavity will be enabled without feeling the need of sudden respiration maneuvers like stiff expiration and respiration exercises, i.e. without feeling the need of increasing the intrapleural pressure difficultly. The most important benefits of the invention will be the above mentioned two advantages.

It will be in an easily portable structure.

The usage is fairly easy. After entering into the intrapleural cavity, with on and automatic operation switch, all operations will be done automatically. It will also warn as at the end of the process. It will provide a considerable reduction in the treatment cost and will provide thousands of usage opportunity.

Besides, it may also be used as an aspirator device in various medical operations as a supplementary function.

Claims

1. The invention is a device which provides pneumothorax treatment; characterized in that, it reduces the treatment period, the sensation of pain of the patient and reduces the treatment costs and it has pressure sensor (10 or 16), vacuum pump system, microprocessor, channel (17), main cap (15), battery, integrable liquid bags (18), cap of the liquid bag (19) which is found at the mouth of the said bag (18), functional buttons (2, 3, 4, 5, 6, 7) and screen (1) parts.

2. A pressure sensor (10 or 16) according to claim 1 ; characterized in that, either one differential pressure sensor (10) is localized on the main cap (15), in the channel (17) and having stands (11 and 12) in the atmosphere associated (13) and pleura associated (14) parts of the channel (17); or two different pressure sensors (16) are localized separately in the suitable regions of the atmosphere associated (13) and pleura associated (14) parts of the channel (17).

3. Vacuum pump system according to claim 1 ; characterized in that, it consists of a vacuum system structure which is able to operate at the suitable pressure range like vacuum motor.

4. Microprocessor according to claim 1 ; characterized in that, it regulates the vacuum motor and the caps (15 and 19) according to the detected pressure difference from the pressure sensor (10 or 16).

5. Channel (17) according to claim 1; characterized in that, via main cap (15) it is divided into two parts associated to atmosphere (13) and associated to pleura (14), and also the bottom part of the pleura associated part (14) is inclined towards the liquid bag (18).

6. Main cap (15) according to claim 1; characterized in that, it takes charge in the regulation by functionally being opened and closed depending on the pressure difference detected by the microprocessor.

7. Liquid bag (18) according to claim 1; characterized in that, it is in an integrable structure to the channel (17) and provides the collection of the liquids which come from the intrapleural cavity.

8. The cap of the liquid bag (19) according to claim 1 ; characterized in that, it prevents air leakage by closure of the cap of the liquid bag (19) after the closure of the main cap (15) and it provides the right detection of the pressure.

9. Functional buttons (2, 3, 4, 5, 6, 7) according to claim 1 ; characterized in that, they provide switching on and automatic operation (2), transition to manual (3), aspiration speed increasing (4) and decreasing (5) in manual, channel opening and closing (6) and only aspiration (7).

lO.Screen (1) according to claim 1 ; characterized in that, the values are traced in the course of automatic and especially manual operations.