Device for intratracheal ventilation and intratracheal pulmonary ventilation including reverse venturi

Abstract: A device (10, 80 or 120) for creating a sub-atmospheric pressure near the carina (12) of a human or veterinary patient (48) includes a channel (28) or perforation (92 or 132) for the passage of an oxygen-containing gas therethrough, the channel (28) or perforation (92 or 132) being open in a direction distal of the patient, so as to establish a zone (30, 94 or 142) of sub-atmospheric pressure by reverse venturi effect during patient exhalation. The sub-atmospheric pressure in the zone (30, 94 or 142) facilitates removal of carbon dioxide from the lungs (54) of the patient and permits intratracheal and/or intratracheal pulmonary ventilation to be performed at pressures less than those conventionally required for such ventilation. The device (10, 80 or 120) of the present invention is also advantageous in obviating the risks inherent in prior reverse venturi devices, specifically, the possibility of detachment of a tubular member in those devices, and the possible complications of surgical recovery of the tubular member from the bronchi (52) or lungs (54) of the patient (48). The device (10, 80 or 120) of the present invention achieves this latter advantage either by eliminating the tubular member of prior reverse venturi devices, or by providing a shoulder (130) affirmatively preventing distal movement and loss of it.

Description: Technical Field This invention relates generally to medical devices, and more particularly to devices for delivering fresh air, oxygen or an oxygen-containing gas to the trachea and lungs of a human or veterinary patient. Background of the Invention Mechanical ventilation has long been used to support lung function in a patient, and entails the use of warmed and moistened fresh air, oxygen, or an oxygen-containing gas (such as an anesthetic gas) supplied to the patient under pressure for oxygenating the patient's lungs. One known method of mechanical ventilation is intratracheal ventilation (ITV). ITV involves the delivery of a warmed and well-humidified gas at or near the patient's carina (the fork of the trachea leading to the bronchial tubes). The gas is delivered through a ventilator tube positioned in the trachea. The ventilator tube can be a catheter, a tracheal tube, an endotracheal tube or the like, and the oxygen-containing gas can be supplied through it on either a continuous or periodic basis. In the former case, the ventilator tube can be supplied with a positive end expiratory pressure (PEEP) valve, whose periodic activation allows air from the lungs (enriched in carbon dioxide) to exit the patient's body. While they do provide some degree of oxygenation when initially employed, the continued use of mechanical ventilators for ITV is subject to significant drawbacks. For example, mechanical ventilators have traditionally been required to deliver high gas pressures, in order to achieve adequate oxygenation. There are several reasons for this. When a mechanical ventilator is first installed, the interior of the ventilator tube usually contains just air, rather than an oxygen-enriched gas; when activated, this air is pushed into the lungs, while the oxygen-enriched gas remains outside the lungs. The alveoli in the patient's lungs expire carbon dioxide, and the expired carbon dioxide builds up in the lungs after several ventilation cycles, because the high pressure of the oxygen-enriched gas -- and any straight air between the gas and the carbon dioxide in the lungs -- prevents at least some of the carbon dioxide from escaping the lungs. The elevated level of carbon dioxide leads the health practitioner to supply even higher pressures of the oxygen-enriched gas to the ventilator tube. After a time as short as only a few hours, the patient's lungs may suffer damage from two sources, specifically, the elevated ventilator pressure, and the build-up of carbon dioxide. The result can be hypoxia, respiratory acidosis, hypercarbia, iatrogenic lung damage, pulmonary hypertension, overinflation, and/or pulmonary parenchymal injury. These problems can even be severe enough to result in the death of the patient. Further, while these problems are more likely to occur and to be more severe in patients with significantly impaired lung function (such as pediatric patients and patients who have undergone a partial lung removal), these problems can even occur in patients with healthy lungs. Another known method of mechanical ventilation is intratracheal pulmonary ventilation (ITPV) . ITPV similarly involves the delivery of an oxygen-containing gas at or near the patient's carina. The gas is continuously supplied either at a constant pressure, or by pressure pulses at a frequency of about 1 to 50 cycles per second. EP 0180038 discloses an apparatus for high-frequency artificial respiration of patients comprising a flexible endotracheal tube having a mechanism comprising a mobile valve adjacent to the distal end of the tube. The valve is either rotating or moving in an axial direction with respect to the remainder of the device, with the purpose of supplying respiratory air pulses in a forward direction through forward facing discharge ports for inhalation by patients, and in a reverse direction through separate reverse blast discharge ports for facilitating exhalation by patients. One drawback to this method is that carbon dioxide outflow is periodic or intermittent, controlled by relatively complex valve and timer mechanisms. As a result, the potential remains for an inadequate expiration of carbon dioxide and a resultant progressive build up of the dioxide level in the patient. Additionally, the cyclical peak pressures typically employed in this method are high, often significantly higher than the pressures employed in ITV. Accordingly, all of the problems, which may be encountered in the use of ITV, may also be faced during the use of ITPV. One solution to these and other problems has been the Kolobow reverse thrust catheter, such as disclosed in U.S. Patent No. 5,186,167 (Feb. 16, 1993). It describes a catheter contained in a trachea and deliberately avoids the use of a tracheal or endotracheal tube. In FIG. 30 in the patent the flow of air and oxygen is in a direction opposite the distal end of the catheter. Kolobow presents a risk to the patient, in that the catheter tip 16 causing the venturi effect is generally of solid material and is pressed over and attached to the distal end of a hollow and flexible catheter. As a practical matter, such attachment is problematic, due to the nature of the materials used and the small dimensions encountered. The result is that the catheter tip 16 can become loose and separate from the distal end of the catheter, and be deposited in one of the bronchi or lungs of the patient. As a result, the catheter tip 16 may damage the tissue of the lung and create complications such as fluid pockets, infections and patient discomfort. Furthermore, the separated catheter tip 16 may require surgical removal, and the complications attendant to lung surgery. Kolobow assists in the removal of carbon dioxide-laden air out of the patient's lungs, but in accordance with the present invention it has been discovered that when the arrangement is used in the presence of a tracheal or endotracheal tube, the improvement in that removal is remarkably enhanced. Oxygenation can be achieved at pressure levels significantly lower than the pressures employed in Kolobow, thereby substantially reducing the risk of trauma to the patient from elevated ventilation pressures. Another solution to the problems has been provided by Makhoul as disclosed in U.S. Patent No. 5,291,882 (Mar. 8, 1984). It is based on the same principle of redirection of flow within the trachea as the Kolobow device, except that the redirection is caused by the intratracheal tube rather than a catheter tip. In Makhoul's ventilation system, the direction of flow through the intratracheal pulmonary ventilation tube is directed away from the distal end of the tube towards the proximal end in order to reduce the amount of carbon dioxide within the trachea of a patient. The redirection of flow is made possible by the configuration of the distal end of the intratracheal tube comprising a curved section leading to a tab near the distal end of the tube. According to the present invention, there is provided a device as defined in claim 1. The foregoing problems are solved and a technical advance is achieved in an illustrative reverse venturi device for creating a sub-atmospheric pressure near the carina of a human or veterinary patient, employed for intratracheal and/or intratracheal pulmonary ventilation. More particularly, the present invention is directed to a device for creating a sub-atmospheric pressure near the carina of a human or veterinary patient, which includes a channel or perforation for the passage of an oxygen-containing gas therethrough, the channel or perforation being open in a direction distal of the patient, so as to establish a zone of sub-atmospheric pressure by reverse venturi effect during patient exhalation. "Sub-atmospheric pressure" means a pressure below at least the air pressure within the lungs and bronchi at the start of patient exhalation, and is preferably a pressure below the ambient atmospheric pressure. The sub-atmospheric pressure created in the present invention is advantageous in that it facilitates removal of carbon dioxide from the lungs of the patient and permits intratracheal and/or intratracheal pulmonary ventilation to be performed at pressures less than those conventionally required for such ventilation. A first embodiment of the present invention is directed to a device for creating a sub-atmospheric pressure near the carina of a human or veterinary patient, which comprises a tracheal or endotracheal tube having proximal and distal ends, a wall connecting them, and a passageway for the flow of an oxygen-containing gas; and which also comprises an insert received in and circumferentially abutted by the distal end of the tracheal or endotracheal tube, the insert having a surface defining at least one channel in communication with the passageway of the tube, the channel being open towards the proximal end of the tube; such that a zone of sub-atmospheric pressure is established, inside the tube and adjacent the distal end of the tube during exhalation of the patient, upon passage of an oxygen-containing gas through the tube passageway and the at least one channel of the insert. Preferably, the tracheal or endotracheal tube is a multiple lumen tube, in which the passageway is formed in the wall of the tube and includes an outlet adjacent the distal end of the tube. Also preferably, the insert is shaped as a hollow cylinder having a plurality of axial channels and a circumferential channel connecting the axial channels to the passageway outlet at the distal end of the tube. Advantageously, the inner surface of the wall of the tube and the outer surface of the insert together define the at least one channel. The device comprises means for connection to a source of an oxygen-containing gas, preferably a continuous source of such a gas, connected to the passageway of the tube. This embodiment of the invention is particularly advantageous over the device disclosed by Kolobow in that it renders the tubular portion 19 of Kolobow unnecessary, thereby affirmatively preventing any risk of separation of that portion from the catheter and its loss inside the patient, thus avoiding any potential trauma or complications from procedures needed to recover it. Furthermore, the tracheal or endotracheal tube advantageously includes a second passageway in the wall of the tube, which has an outlet distal of the insert. This second passageway is utilized for infusing drugs, but more importantly, monitoring the pressure at the distal end of the tube and/or near the carina of the patient. In Kolobow the catheters described in Figs. 3A,3B and 3C are positioned directly within the trachea of a patient without the presence of a tracheal or endotracheal tube. It has now been discovered that by intentionally locating such a tube around the particular catheters of this invention, that the reverse venturi effect has been surprisingly enhanced. No theory is postulated at this time to explain the degree of enhancement achieved. Brief Description of the Drawing A better understanding of the present invention will now be had upon reference to the following detailed description, when read in conjunction with the accompanying drawing, wherein like reference characters refer to like parts throughout the several views, and in which: FIG. 1 is a perspective view of a preferred embodiment of the present invention positioned in the trachea of a patient; FIG. 2 is a side exploded view of the embodiment shown in FIG. 1; FIG. 3 is a cross-sectional view taken along line 3-3 of FIG. 2; FIG. 4 is an end view of the preferred embodiment of the present invention; FIG. 5 is a partial view of a portion of the preferred embodiment of the present invention; FIG. 6 is an end view taken from line 6-6 of FIG. 5; FIG. 7 is an end view taken from line 7-7 of FIG. 5; FIG. 8 is a cross-sectional view taken along line 8-8 of FIG. 5; FIGs. 9 and 10 are schematic views of the use of the preferred embodiment of the present invention; Detailed Description With reference first to FIGs. 1 and 2, the first preferred embodiment of the present invention for creating a sub-atmospheric pressure near the carina 12 of a human or veterinary patient 48 is thereshown as a device 10, extending from outside the patient 48 to a location within the trachea 50 of the patient 48. The carina 12 is, of course, the location at which the bronchi 52 split from the trachea 50, and lead towards the lungs 54 of the patient 48. More particularly, the device 10 first comprises a tracheal or endotracheal tube 14 having a proximal tube end 16 positioned outside the trachea 50 of the patient 48, and a distal tube end 18 spaced from the proximal tube end 16 and positioned at or near the carina 12 of the patient 48. The tube 14 includes a tube wall 20 connected to and extending between the proximal tube end 16 and the distal tube end 18, as well as a tube passageway 22 for the flow of an oxygen-containing gas therethrough. The tube 14 is preferably a conventional multiple lumen tracheal or endotracheal tube 32, in which the tube passageway 22 (normally used for the application of suction to remove fluids) is preferably embedded in the tube wall 20 and is connected by an appropriate valve and/or monitoring mechanism 60 to a source 46 of the oxygen-containing gas, such as warmed and moistened air, oxygen, gaseous anaesthetic, or the like. The proximal tube end 16 is attached to a fitting or connector 62, and thence to valves, regulators, monitors or controls (not shown) suitable to the particular ventilation method to be employed. It is preferable that tube 14 include a second passageway 64 in the wall thereof, which has an outlet 66 distal of insert 24 for infusing drugs and/or monitoring pressure near the carina of the patient. A side arm 68 with a well-known Luer lock connector communicates with second passageway 64 near the proximal end 16 of the tube 14. of course, it is highly desirable that the tube 14 also include a line of radiopaque material 58 in the tube wall 20 and running the entire length of the tube wall 20, to facilitate monitoring of the position of the tube 14 in the trachea 50 of the patient 48. The positions of the second passageway 64, the line of radiopaque material 58, and the tube passageway 22 are more clearly shown in FIG. 3. With continued reference to FIG. 2, but especially with further reference to FIGs. 4 through 8, the device 10 also comprises an insert 24 received in and circumferentially abutted by the distal tube end 18, for providing the reverse venturi flow of the oxygen-containing gas through the tube 14. More particularly, the insert 24 has a surface 26 defining at least one insert channel 28 in fluid communication with the tube passageway 22, the at least one insert channel 28 being open towards the proximal tube end 16. Preferably, when the tube passageway is formed in the tube wall 20, the tube passageway 22 includes a passageway outlet 34 located adjacent the distal tube end 18, and the at least one insert channel 28 is in fluid communication with the passageway outlet 34. Also preferably, the at least one insert channel 28 comprises a plurality of channels, and more particularly, at least one circumferential channel 36 in fluid communication with the passageway outlet 34, and a plurality of axial channels 38 connected to the tube passageway 22 by the at least one circumferential channel 36. The insert 24 is most preferably configured as a hollow cylinder 40 having a central throughbore 56, although any of a variety of other shapes for the insert 24 might be suitable, if the material of the tube 14 is sufficiently flexible to ensure an adequate seal to the insert 24, and if a central passage is provided to allow the exit of carbon-dioxide enriched air from the lungs 54, and out through the bronchi 52 and trachea 50. Also preferably, it is the outer surface 42 of the cylinder 40 that is the insert surface 26 on which the at least one insert channel 28 is formed. In such a case, the at least one insert channel 28 is further defined by the inner surface 44 of the tube wall 20, at the distal tube end 18. The insert 24 may be composed of any suitable medical grade material, such as a sterilizeable synthetic. However, as the tube 14 will typically be composed of a material which is somewhat flexible, it is highly desirable that the insert 24 be composed of a material which is more rigid than the material making up the tube 14; this ensures that the inner surface 44 of the tube wall 20 does not collapse into the at least one insert channel 28, and prevent the flow of the oxygen-containing gas through the at least one insert channel 28. It is therefore advantageous to construct the insert 24 from a suitable rigid material, such as Deltrin™ nylon material, into whose surface 26 the at least one insert channel 28 can be machined. The number of insert channels 28 is not believed to be critical, so long as one or more of them are open in the direction of the proximal tube end 16, and can establish in the tracheal or endotracheal tube 14 a reverse venturi flow of the oxygen-containing gas away from the lungs 54 and bronchi 52 of the patient 48. Use of the present invention in ventilation procedures such as ITV and ITPV can now be easily understood. The passage of an oxygen containing gas from the source 46, through the device 10 and out the respective channels 28, creates during exhalation a respective zone 30 (Fig. 10) of sub-atmospheric pressure. In operation the device 10 is positioned with respect to the patient 48 so that the distal tube end 18 lies at the level of the carina 12. A moist, warmed oxygen-containing gas is then introduced into the device 10 from the source 46, through the valve 60, and allowed to flow out the insert channels 28, such as the circumferential channel 36 and the plural axial channels 38. During the inhalation phase of the respiratory cycle, as shown by the arrows in FIG. 9 the gas passes into the bronchi 52 and the lungs 54, oxygenating the lungs 54 in the desired manner. During the exhalation phase of the respiratory cycle, as shown by the arrows in FIG. 10, the oxygen-containing gas continues to flow out of the channels 36 and 38 and creates the zones 30 of sub-atmospheric pressure which aid removal of the carbon-dioxide laden air from the lungs 54 and bronchi 52. It is critical to achieving this reverse Venturi that the oxygen-containing gas flow through the device 10 at some time during the exhalation phase, preferably continuously. The use of the device 10 is not limited to constant flow methods. The present invention is expected to be useful in ventilation methods in which the flow rate or pressure varies during the ventilation cycle, so long as a sufficient flow rate through the device 10 is provided to create sub-atmospheric pressure adjacent to the devices during patient exhalation, and aid removal of carbon-dioxide enriched air from the lungs of the patient. Constant flow methods are probably preferred, however. The device 10 reduces the size of the dead space in the trachea which might trap carbon-dioxide laden air in the lungs and bronchi, or which might block the introduction of oxygen into the bronchi and lungs. It also permits ventilation procedures to be successfully carried out with lower gas flow rates and lower peak respiratory pressures, reducing the risk of trauma to the lungs, and the other problems mentioned above. The other details of the construction or composition of the various elements of the disclosed embodiment of the present invention are not believed to be critical to the achievement of the advantages of the present invention, so long as the elements possess the strength or flexibility needed for them to perform as disclosed. The selection of these and other details of construction are believed to be well within the ability of one of even rudimentary skills in this area, in view of the present disclosure.

Claims: A device (10) for ventilating a patient at a conventional ventilation rate, comprising a tracheal or endotracheal tube (14, 32) having a distal end (18); connection means (60) in the region of the proximal end (16) of the tube (14, 32) for connection to a source (46) of an oxygen-containing gas; and means (22, 34) for feeding the said gas to a region in the tube (14, 32) adjacent to the said distal end (18); characterised in that the tracheal tube comprises an insert (24) with a central throughbore (56) extending through the insert for receiving exhaled gas, and with longitudinal channels (38) circumferentially spaced around the central throughbore of the insert for redirecting the oxygen-containing gas. A device (10) according to claim 1, wherein the insert (24) is located adjacent to the distal end of the tube (14, 32), said insert (24) being in communication with the gas feeding means (22) and having a plurality of channels (28) for directing the gas towards the proximal end (16) of the tube (14, 32). A device (10) according to claim 2, wherein the insert (24) serves to distribute the said gas to the said plurality of channels, said insert comprising the central throughbore (56) to be located in the region of the carina (12) of the patient (48). A device (10) according to claim 2 or 3, wherein the insert (24) is a hollow cylinder circumferentially abutting the internal surface (44) of the distal end (18) of the tube (14, 32), with the channels (28, 36) formed between the insert (24) and the said tube (14, 32), the insert (24) having a circumferential channel (36) connected to the gas feeding means (22, 34) and to the longitudinal channels (38). A device according to claim 1, 2, 3 or 4, wherein the gas feeding means is a lumen (22) formed in the wall (20) of the said tube (14, 32), other lumen (64) in the wall of the tube (14, 32) being an optional provision.

Inventors: FISCHER FRANK J JR, FISCHER, FRANK J., JR.
Applicants: COOK INC, COOK INCORPORATED
Application year: 1996
Main classification: A61M16
IPC codes: A61M16, A61M25