RU2805545C1 - Endotracheal device for mechanical ventilation of patient's lungs - Google Patents

Abstract

FIELD: medical technology.

SUBSTANCE: invention is related to instruments and devices for surgical use and, in particular, to an endotracheal device used in mechanical ventilation of patients as an interface between the patient and the ventilation apparatus. An endotracheal device for mechanical ventilation of the patient's lungs (3) contains a ventilation tube (10) containing a distal part with a distal end (11) intended for insertion into the patient's respiratory tract (3), a proximal part with a proximal end (12) intended for connection with a ventilation device; and a barrier (13) covering the ventilation tube (10) in the distal region and, when inserted, configured to be located in the subglottic cavity (14), as well as in the vocal cavity (15) and also in the supraglottic cavity (16) of the larynx (5) of the patient (3) and with the ability to adapt to their morphology, for which the barrier (13) has a variable cross-section along its length. The endotracheal device further comprises pressure application means configured to connect to the barrier (13) to deform the barrier (13). The barrier (13) is made of a hard viscoelastic material and contains, in a more distal location, a first part (17) with a cross-section increasing from the distal end (11), to adapt to the subglottic region (14), and in a more proximal location, a second part (18), opposite the first part (17), with a cross-section increasing from the first part (17), to adapt to the supraglottic cavity (16). The pressure application means comprise a flexible conduit (22) connected to the barrier (13) and to an air shut-off valve (23) to apply negative pressure to compress the barrier (13) before insertion into the patient (3) and release said compression after insertion.

EFFECT: invention provides increased safety and lesser likelihood of complications during mechanical ventilation of patients.

15 cl, 4 dwg

Description

TECHNICAL FIELD

The present invention relates to the field of instruments and devices for surgical use. In particular, the invention relates to an endotracheal device used in mechanical ventilation of patients as an interface between the patient and the ventilator.

BACKGROUND OF THE ART

Mechanical ventilation of patients (3) under anesthesia (for surgical or diagnostic procedures) or in critical situations (emergency situations or intensive care) requires an interface between the patient (3) and the ventilator, which is currently implemented in the form of masks of various designs and in the form of endotracheal tubes (1), which have been in use for over 100 years and whose design has undergone only minor changes, but has not been significantly changed. Accordingly, the risks and complications associated with their use remained unchanged over the specified long period of time.

In FIG. 1 illustrates the use of one of these endotracheal tubes (1) known in the prior art. Said endotracheal tube (1) contains a channel (2), which, under general anesthesia and during the patient's sleep (3), is inserted through the patient's mouth or nose (3) until it reaches the trachea (4) in the subglottic cavity. Said endotracheal tube (1) is connected to a ventilator, also called a respirator, or the like. (not shown in FIG. 1), the function of which is to maintain the patient's breathing (3). Even if the channel (2) is properly positioned, some of the stomach contents can sometimes pass into the patient's lungs (3) and cause serious breathing problems. Likewise, in surgical procedures performed in the pharynx and the oral or nasal cavities, there is a risk that secretions or blood formed in the upper respiratory tract (above the glottis) will pass into the lower respiratory tract. To minimize this risk, the use of gauze tamponade as a barrier is indicated.

Damage to the respiratory tract occurs during anesthesia, which is performed daily in any hospital. Damage to the vocal cords or larynx is reflected in the postoperative period: sore throat (odynophagia), voice changes (dysphonia due to irritation of the vocal tract) or loss of voice (aphonia). Injuries that affect certain parts of the vocal folds, such as the arytenoids, cause the voice to become weak throughout the day.

The introduction of videolaryngoscopy, coupled with improved muscle relaxant reversal, has led to increased indications for intubation, resulting in improved patient safety (3). That is why there is a need to develop new devices that, while maintaining ventilation and anesthesia, provide greater safety and less risk of complications and thus significantly improve the current situation.

The possibility of an epidemic in which microbes are present in the pulmonary tract indicates the need for increased respiratory tract protection, preferably avoiding the future use of devices that do not provide adequate containment.

Likewise, the present device allows patients to be ventilated more safely, reducing the likelihood of infection to the patient and involved medical personnel should ventilation be required during an epidemic.

In documents US6745773B1 (GOBEL), US2010/051035A1 (JENKINS), US2013/146062A1 (SCHUMACHER), WO2010/091440A2 (BHATT), US2020/030560A1 (JENKINS), US2017/281966A1 (BASIONY) and WO2006/125986A1 (LARYNGEAL MASK) disclosed several models of tracheal cuffs.

DISCLOSURE OF THE INVENTION

The present invention solves the above-mentioned problems by providing an endotracheal device for mechanically ventilating a patient, providing increased safety and less likelihood of complications when mechanically ventilating patients.

The endotracheal device of the present invention includes a vent tube and a barrier, the vent tube including: a distal portion with a distal end for insertion into the airway of a patient, and a proximal portion with a proximal end for connection to a ventilator.

In addition, the barrier is made of a solid viscoelastic material, covers the ventilation tube in the distal region and is designed to be inserted into the subglottic cavity, as well as in the vocal cavity and also in the supraglottic cavity of the patient's larynx, as a result of which the barrier has a variable cross-section along its length. As will be explained below, the barrier provides a triple effect, since it affects three specified cavities: the subglottic, glottal and supraglottic cavities.

In a more preferred example, the barrier comprises two frusto-conical portions meeting at a cylindrical junction to accommodate different diameters at the level of the trachea, vocal cords and supraglottic cavity in such a way that it can adapt to provide better treatment to adjacent structures, as well as damping any movement performed by the patient such as change of position, convulsions, etc. In accordance with the above, the use of a barrier provides triple protection: in the vocal cords, in the trachea and in the supraglottic cavity.

BRIEF DESCRIPTION OF THE DRAWINGS

As a supplement to the description and in order to facilitate easier understanding of the features of the invention, in accordance with a practical preferred embodiment thereof, the said description is accompanied by a set of drawings which, by way of illustration and not limitation, show the following:

In FIG. 1 shows a schematic view of a patient intubated by means of an endotracheal tube known in the art.

In FIG. 2 is a life-size perspective view of an exemplary embodiment of an endotracheal device according to the present invention.

In FIG. 3 is a schematic view of a patient intubated with a device according to the present invention.

In FIG. 4 shows a view of a triple effect barrier in an exemplary embodiment of the invention for a specific case of a pediatric patient.

IMPLEMENTATION OF THE INVENTION

A detailed description of a preferred embodiment of an endotracheal device for mechanical ventilation of a patient (3) in accordance with the present invention is given below with reference to FIG. 1-4 described above.

The endotracheal device of the present invention is a three-barrier transglottic device, as explained below, the name of which may be abbreviated as ETT.

In FIG. 2 and 3 are perspective views of a preferred life-size embodiment of the endotracheal device. The endotracheal device includes a ventilation tube (10) with a distal portion provided with a distal end (11), and a proximal portion provided with a proximal end (12), wherein the distal portion is intended for insertion into the patient's airway (3), and the proximal portion is intended for connection with a ventilation device (not shown).

In FIG. 1 and 3 show that the ventilation tube (10) is covered with a barrier (13) made of a deformable solid material with viscoelastic characteristics, located in the distal part of the ventilation tube (10) and designed to be inserted into the subglottic cavity (14), and also in the vocal cavity (15) and also in the supraglottic cavity (16) of the larynx (5) of the patient (3). In the illustrated example, the barrier (13) occupies approximately the most distal third of the vent tube (10). The barrier (13) has dimensions, in length and cross-section, suitable to adapt to the morphological structure of the above-mentioned subglottic cavity (14), vocal cavity (15) and supraglottic cavity (16). In particular, the barrier (13) has a variable cross-section along its length. The barrier (13) preferably has rotational symmetry, as a result of which the cross sections of the barrier (13) are defined at each point by the value of the corresponding diameter.

Various barrier cross-section/diameter values (13) are derived from anatomical studies of the trachea in patients (3) and/or cadavers.

At a more distal location, the barrier (13) contains a first part (17), preferably with a straight or convex (not concave) longitudinal section, whereby, for example, the first part (17) has a conical shape to adapt to the subglottic space (14). The configuration of the first part (17) may vary for pediatric patients (3) compared to adult patients (3). For adult patients, according to an example implementation, see FIG. 2 and 3, the first portion (17) has an increasing cross-section (or diameter) from the distal end (11), and preferably larger and smaller end diameters of 29 mm and 19 mm, respectively, to properly adapt to the morphology of the subglottic cavity (14 ), usually having an anteroposterior diameter of 14 to 18 mm and a transverse diameter of 18 to 22 mm (internal distances; external distances are larger). The difference in diameters between the first part (17) of the barrier (13) and the subglottic cavity (14) of the larynx (5) of the patient (3) is set in such a way that a pressure sufficient to isolate and protect the airways at atmospheric pressure is created. On the other hand, for pediatric patients (3), in particular those under nine years of age, see FIG. 4, the first portion (17) may have an increasing cross-section (or diameter) from the distal end (11), with the larger and smaller end diameters being smaller compared to the adult device. In any case, the ventilation tube (10), as well as the barrier (13), in particular the first part (17) of the barrier (13), can be manufactured in different sizes without loss of versatility or performance based on the morphology of different pediatric patients (3). and adult ages.

In FIG. 2 and 3 also show that the barrier (13) at a more proximal location comprises a second part (18) opposite the first part (17), with a cross-section (or diameter) increasing from the first part (17), preferably straight or convex (not concave) longitudinal section, such that, for example, the second part (18) has a conical shape to adapt to the supraglottic cavity (16). According to an example implementation, the second part (18) has smaller and larger end diameters of 19 mm and 34 mm, respectively, for reasons similar to those disclosed for the first part (17) of the barrier (13).

In FIG. 2 and 3 also show the joint (19) of the first part (17) with the second part (18) of the barrier (13), intended to be located in the vocal cavity (15) at the level of the vocal cords and, according to the described preferred example, the joint has a known diameter of 19 mm, since the maximum opening of the vocal cords is usually from 10 to 15 mm (at rest - 6-7 mm in men, 1-2 mm in women). In general, the joint (19) has a preferred length of from 4 mm to 15 mm, and a preferred diameter of from 3 mm to 24 mm.

Preferably, as shown in FIG. 1 and 3, a placement mark (20) is provided, preferably opaque and more preferably black, located at the junction (19) of the first part (17) with the second part (18) and intended to be positioned at the level of the patient's vocal cords (3) and, hence the vocal cavity (15).

As an example, in the described preferred embodiment, the barrier (13) has a total length of 10.5 cm, of which 5.5 cm corresponds to the first part (17) and 5 cm corresponds to the second part (18). In general, the first part (17) may have a preferred length of from 10 mm to 65 mm. Likewise, the second part (18) may preferably have a length of from 10 mm to 75 mm.

In FIG. 2 and 3 show the location of each part (17, 18) of the barrier (13) in the respiratory tract after inserting the device into the patient's body (3), with the subglottic cavity (14) located below the vocal cords, the vocal cavity (15) located at the level of the vocal cords , and the supraglottic cavity (16) is located above the vocal cords and extends to the base of the epiglottis.

In FIG. 2 and 3 show that the distal end (11) preferably lacks a Murphy eye (6), see FIG. 2, and a control mark (21) with radiopaque characteristics is provided, allowing, after insertion of the device into the patient's body (3), to check the correct positioning of the distal part of the endotracheal device and, therefore, the endotracheal device as a whole, by radiography.

The configuration of the device in shape and size is determined by the anatomical ranges characteristic of the larynx (5), i.e. epiglottis, ligaments, arytenoids, etc., trachea (4) and pharynx of patients (3).

Since the barrier (13) is made of a deformable solid material with viscoelastic characteristics, the barrier (13) can be inserted into the patient's body (3) in a folded state, i.e., in a compressed state, by applying negative pressure to the barrier (13) and stopping said compression after insertion or even application of positive pressure. Briefly, the device of the present invention may include pressure application means that can be coupled to the barrier (13) to deform the barrier (13) due to the effects of fluid pressure and compressive force. This can be accomplished, for example, by connecting to the barrier (13) a flexible conduit (22), in turn connected to a stop valve (23), such as, for example, a three-way stop valve (23), and aspiration using a syringe (30). from the three-way shut-off valve (23). After placing the device in the patient's body (3) and through the use of the specified three-way shut-off valve (23), it is possible to freely pass atmospheric air to the barrier (13) with filling at atmospheric pressure or applying positive pressure by pumping air through a syringe (30). The barrier (13) can be adapted to tracheostomy cannulas.

In FIG. 2 and 3 show the arrangement of reinforced sections and non-reinforced sections in the vent tube (10), as explained below. In the prior art, reinforced, also referred to as reinforced, endotracheal tubes (1) are known, characterized by having internal reinforcement of an exhalation spring mold placed within the tube to prevent the transmission of stress caused by any connection or movement along the entire length of the device, as well as to prevent easy bending tubes. However, if the patient (3) bites down on one of these reinforced tubes upon awakening from anesthesia or when mechanical ventilation is required, the reinforced tube will be deformed and make ventilation difficult due to the increased resistance caused by the reduction in size. Sometimes the wrinkling is so significant that it prevents the secretion from draining down the tube. These disadvantages can be eliminated by using an unstrengthened tube. To provide the benefits of reinforced tubes and non-reinforced tubes in a single tube, the device of the present invention includes alternating reinforced segments (24, 26) and non-reinforced segments (25, 27) in the vent tube (10). In general, the ventilation tube (10) is for the most part reinforced to provide the above-mentioned advantages, and is non-reinforced in the area in which the patient (3) can bite the ventilation tube (10). In particular, the ventilation tube (10) contains a first reinforced segment (24) located in the distal part, followed by a first non-reinforced segment (25) located in the area that the patient (3) can bite, which in turn is followed by a second reinforced segment (26), already located in the proximal part. Preferably, it is followed by a second non-reinforced segment (27) extending to a proximal end (12) following it. The described combination of reinforced segments (24, 26) and non-reinforced segments (25, 27) is a significant novelty of the present invention.

The ventilation tube (10) preferably contains in its distal part, at least in part of the area covered by the barrier (13), a disinfectant radiation emitter (28), emitting, for example, ultraviolet (UV) radiation, for example type C, in the range of 200- 280 nm. Preferably, the disinfectant radiation emitter (28) comprises an optical fiber extending internally through a vent tube (10) and coated with an opaque material, wherein it is devoid of opaque material in a region corresponding to the barrier (13) to generate radiation, for example UV radiation, in the specified area. The disinfectant radiation emitter (28), in particular an optical fiber, can, if necessary, reach the radiopaque control mark (21).

At the proximal end (12), the vent tube (10) may include an indicator (29) providing information about the diameter of the vent tube (10) to facilitate safe and rapid connection to the ventilator. Preferably, the indicator (29) may be a cap. Even more preferably, the indicator (29), in particular the cap, has a color indicating the diameter value, in accordance with a predetermined color classification. Color classification allows for safer and faster availability of these devices, especially in emergency situations where time is of the essence. This simple classification allows you to quickly find the required tube, which is currently impossible. According to the illustrative example, the colors pink, blue, red, green and yellow are used for diameters of 6.0, 6.5, 7.0, 7.5 and 8.0 mm, respectively.

Preferably, the barrier (13) at least in the outermost layer is made of a partially permeable polymer (for example, nylon 6) for impregnation with medical substances such as antiseptics, local anesthetics, etc.

Likewise, the vent tube (10), internally and/or externally, and the barrier (13) are preferably impregnated with nanoparticles (such as silver nanoparticles AgNPs and zinc oxide nanoparticles ZnONPs) to protect against bacteria.

Thus, the more rigid parts of the device never come into contact with the most delicate structures of the patient's airway (3): the larynx (5) and trachea (4), which significantly reduces the likelihood of damage to these important structures. Likewise, this design facilitates adaptation of the patient (3) to the device during periods of awakening from anesthesia or weaning from mechanical ventilation. All of these factors prevent (or at least minimize) the occurrence of typical airway injuries during anesthesia (leading to sore throat or voice disorders such as odynophagia, dysphonia and aphonia).

On the other hand, the length and extension of the barrier (13) provide better protection against contamination of the patient's airway (3) along the outside of the device. The long length makes it difficult for any contaminant or secretion to reach the interior due to the fact that the distance that the contaminant must travel is much greater compared to the balloons (7) of known endotracheal tubes (1), which, moreover, do not correspond to the anatomy of the physiological structures . Through an innovative re-examination of the role of the glottis and supraglottis as fundamental barriers, two other factors in preventing airway contamination may be highlighted. Anatomical adaptation allows for improved isolation.

The use of the device of the present invention avoids the need to perform the pharyngeal tamponade mentioned in the "Background of the Art" section, since the airway is already isolated from the supraglottic cavity (16). Accordingly, there is no need to perform a gauze tamponade, which not only does not provide adequate isolation, but also causes pharyngeal irritation.

In addition, the device allows the maintenance of mechanical ventilation for periods of time significantly longer than the current one, by dramatically reducing the incidence of airway stenosis and preventing or reducing the indication for tracheostomy. In the case of prolonged intubation using an endotracheal tube (1), known in the art, there is a high incidence of tracheal stenosis, which increases the severity of the disease in patients (3) and, in some cases, leads to death. This is due to the following reasons:

- The balloon (7) of the endotracheal tubes (1) on the walls of the trachea (4) is pressed against an extremely short segment of the trachea (4).

- The balloon filling pressure (7) is higher than the capillary perfusion pressure at which the trachea is perfused (4).

- The location of the trachea (4) where the endotracheal tube is located and causes stenosis is known as the pressure ulcer area (9), see FIG. 2. This often requires performing a tracheostomy, which is a surgical procedure consisting of making an artificial and invasive opening in the trachea (4) and providing a channel for communication between the trachea (4) and the environment. This procedure is necessary after 8-10 days of mechanical ventilation to avoid stenosis in the trachea (4). However, tracheostomy can also lead to complications: tracheal ulcers, false tract, hemorrhage, infections, soft tissue deformation, airway obstruction, etc. However, this technique does not prevent the high incidence of post-tracheostomy stenosis: 20-30%.

The capillary blood pressure required for normal tracheal function (4) ranges from 20 to 30 mm Hg. Art., but varies greatly and depends on the resistance and condition of the patient (3). Therefore, in order to maintain tracheal perfusion (4), it is necessary to distribute the stresses created by increasing the contact surface with which the barrier (13) of the device of the present invention effectively interacts.

Given the length of the barrier (13), there is usually no need to apply positive pressure, which could damage the trachea (4). Moreover, if positive pressure was to be applied, a significantly reduced pressure would be required, which would also exert extremely low actual pressure on the airway since the applied pressure was distributed over a barrier surface (13) that was much larger than that of the balloons (7) known endotracheal tubes (1). A comparison can be made between the contact surfaces of the endotracheal tube (1) known in the art (see FIG. 1) and the barrier (13) of the device of the present invention (FIG. 2).

The main source of tracheal stenosis is the emphasis of the cannulas or tubes on the posterior wall of the trachea, where the most vulnerable area is located, since the trachea (4) is fed through this part, which is the non-fibrous part. This nutrition is disrupted as a result of contact with the endotracheal tube (1) in the pressure ulcer area (8). When compared with FIG. 3 it is noted that in the pressure ulcer area (8) damage does not occur due to the use of the barrier (13).

The use of endotracheal tubes (1) known in the art sometimes actively or passively causes bronchoaspiration as well as intestinal reflux. This is because the airway is not completely protected or sealed. Since the supraglottic cavity (16) is not protected, and the balloons (7) of the endotracheal tubes (1) are short and, therefore, have a small surface of interaction with the walls of the trachea (4), there is a high probability of intestinal or oral microbes passing through this area, which causes contamination respiratory tract. Infections associated with mechanical ventilation currently result in increased days in intensive care units and significantly increase mortality in these patients (3). In addition, these nosocomial infections are usually caused by multidrug-resistant microbes, the eradication of which is difficult.

Typically, in patients (3) who require prolonged intubation, after 8 to 10 days, an invasive surgical procedure called tracheostomy will be indicated, which is not without complications, increases costs, and diverts resources. In addition, often the specified prophylactic tracheostomy is performed, but soon mechanical ventilation of the patient's lungs (3) is stopped, and accordingly, the specified procedure (with hindsight) could have been avoided. Although attempts have been made to develop methods to predict which patients should receive a given prophylactic intervention, these methods have been unsuccessful and tracheostomy is ultimately performed (as a "lesser evil") before damage due to tracheal stenosis can occur. The device of the present invention increases the duration of possible maintenance of orotracheal ventilation, which avoids many cases in which tracheostomy is currently performed.

There are two routes of infection leading to highly undesirable nosocomial pneumonia associated with mechanical ventilation: the external and internal surfaces of endotracheal tubes (1). As explained above, the present invention provides three solutions:

- Large length and contact surface of the barrier (13) with the respiratory tract in three cavities: subglottic (14), glottic (15) and supraglottic (16).

- The possibility of impregnating the barrier (13) with silver or zinc oxide nanoparticles, or antiseptics or other substances that prevent the formation of bacterial biofilm and create an active barrier against infectious invasion of the respiratory tract through the outer surface of the device.

- The ability to provide short-wave ultraviolet radiation (UVC, 200-280 nm) in the distal part, providing protection against respiratory contamination along the inner surface of the device.

These capabilities will be desirable in epidemic situations in the presence of microbes that have a high ability to become infected through airborne droplets, since the device protects not only the patient, but also personnel working near the patient.

In addition, these solutions reduce the likelihood of respiratory tract contamination. If the need for mechanical ventilation is short-term (less than 24 hours), the last two solutions can be omitted and thus production costs can be reduced.

Due to the configuration of the distal part, the device significantly reduces the likelihood of selective ventilation. Once the device is properly positioned, the distance between the point that should rest on the vocal cords and the most distal point of the device is 5.5 cm, according to a preferred example. In endotracheal tubes (1) known from the prior art, the specified distance is 9.0 cm; accordingly, the device can touch and damage the carina of the trachea or cause selective intubation with subsequent complications: increased pressure in the airways, bronchospasm, increased requirements for anesthetics, extrasystole, etc.

The trachea (4) varies greatly in length (and in fact does not always have the same number of rings), ranging from 7 to 15 cm. In addition, movements of the neck can cause a decrease in length by shortening 3-4 rings. Thus, by using the device of the present invention, collision with the tracheal carina or the occurrence of selective pulmonary intubation can be avoided. To improve safety, the Murphy eye (6) present in endotracheal tubes (1) is preferably not used.

The device of the present invention reduces the likelihood of hospital-acquired pneumonia and infectious diseases associated with manipulation of the respiratory tract.

The ability to impregnate the barrier (13) with oral anesthetics allows the patient (3) to better adapt to the device during and at the end of anesthetic procedures. When endotracheal tubes (1) are used, the endotracheal tube (1) often ruptures upon awakening from anesthesia (due to laryngeal reflexes). Anesthetic impregnation results in greater patient acceptance and tolerability (3).

The device of the present invention provides better patient tolerance (3) of mechanical ventilation and weaning from it during long-term ventilation procedures. Likewise, the presence of a reference mark (21) located at the distal end, which is not present in the endotracheal tubes (1), makes it easier to detect this marker in the patient's body (3) by radiography with greater clarity.

Claims (23)

1. An endotracheal device for mechanical ventilation of the patient's lungs (3), containing a ventilation tube (10) containing: a distal part with a distal end (11) intended for insertion into the patient's respiratory tract (3), a proximal part with a proximal end (12) intended for connection with the ventilation apparatus; And a barrier (13) covering the ventilation tube (10) in the distal region and, when inserted, configured to be located in the subglottic cavity (14), as well as in the vocal cavity (15) and also in the supraglottic cavity (16) of the larynx (5) of the patient ( 3) and with the ability to adapt to their morphology, for which the barrier (13) has a variable cross-section along its length, wherein the endotracheal device further comprises means for applying pressure configured to connect to the barrier (13) to deform the barrier (13), In this case, the endotracheal device differs in that the barrier (13) is made of solid viscoelastic material and contains: - in a more distal location, a first part (17) with a cross-section increasing from the distal end (11), to adapt to the subglottic region (14), and - in a more proximal location, a second part (18), opposite the first part (17), with a cross-section increasing from the first part (17), to adapt to the supraglottic cavity (16), wherein the pressure application means comprises a flexible conduit (22) connected to the barrier (13) and to an air shut-off valve (23) to apply negative pressure to compress the barrier (13) before insertion into the patient (3) and release said compression after insertion . 2. An endotracheal device according to claim 1, characterized in that the barrier (13) extends along the most distal third of the ventilation tube (10). 3. Endotracheal device according to any one of paragraphs. 1, 2, characterized in that the barrier (13) has rotational symmetry. 4. Endotracheal device according to claim 1, characterized in that the first part (17) of the barrier (13) has a straight or convex longitudinal section. 5. Endotracheal device according to claim 4, characterized in that the first part (17) has a conical shape. 6. Endotracheal device according to any one of paragraphs. 3-5, characterized in that the first part (17) has a cross-section increasing from the distal end (11). 7. Endotracheal device according to claim 1, characterized in that the second part (18) of the barrier (13) has a straight or convex longitudinal section. 8. Endotracheal device according to claim 7, characterized in that the second part (18) has a conical shape. 9. Endotracheal device according to any one of paragraphs. 1, 7, 8 and 9, characterized in that the first part (17) and the second part (18) converge at the junction (19) intended for placement in the vocal cavity (15) of the patient (3). 10. Endotracheal device according to any one of paragraphs. 1-9, characterized in that the barrier (13) contains a control mark (21) with radiopaque characteristics at the distal end (11) to check the location of the endotracheal device in the patient’s body (3). 11. Endotracheal device according to any one of paragraphs. 1-10, characterized in that the vent tube (10) includes reinforced segments (24, 26) containing internal spring-shaped reinforcement to prevent bending of the vent tube (10) and to prevent the transmission of stress caused by any connection or movement along the vent tube (10), wherein the ventilation tube (10) further comprises a non-reinforced segment (25) corresponding to an area that can be bitten by the patient (3), so that the reinforced segments (24, 26) and the non-reinforced segment (25) are alternating. 12. The endotracheal device according to claim 11, characterized in that the ventilation tube (10) contains a first reinforced segment (24) located in the distal part, followed by a first non-reinforced segment (25) located in the area that the patient (3) can bite, which in turn is followed by a second reinforced segment (26), already located in the proximal part. 13. Endotracheal device according to claim 12, characterized in that the second non-reinforced segment (27), extending to the proximal end (12), follows the second reinforced segment (26). 14. Endotracheal device according to any one of paragraphs. 1-13, characterized in that the ventilation tube (10) contains in its distal part, at least in part of the area covered by the barrier (13), a disinfectant radiation emitter (28). 15. Endotracheal device according to claim 14, characterized in that the disinfectant radiation emitter (28) contains an optical fiber passing inside the ventilation tube (10) and coated with an opaque material, and it is devoid of opaque material in the area corresponding to the barrier (13), to generate disinfectant radiation in the specified area.