CA1296592C - Flexible composite intubation tube - Google Patents
Flexible composite intubation tubeInfo
- Publication number
- CA1296592C CA1296592C CA000565275A CA565275A CA1296592C CA 1296592 C CA1296592 C CA 1296592C CA 000565275 A CA000565275 A CA 000565275A CA 565275 A CA565275 A CA 565275A CA 1296592 C CA1296592 C CA 1296592C
- Authority
- CA
- Canada
- Prior art keywords
- tube
- set forth
- outer layer
- layer
- inches
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Expired - Lifetime
Links
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61J—CONTAINERS SPECIALLY ADAPTED FOR MEDICAL OR PHARMACEUTICAL PURPOSES; DEVICES OR METHODS SPECIALLY ADAPTED FOR BRINGING PHARMACEUTICAL PRODUCTS INTO PARTICULAR PHYSICAL OR ADMINISTERING FORMS; DEVICES FOR ADMINISTERING FOOD OR MEDICINES ORALLY; BABY COMFORTERS; DEVICES FOR RECEIVING SPITTLE
- A61J15/00—Feeding-tubes for therapeutic purposes
- A61J15/0003—Nasal or oral feeding-tubes, e.g. tube entering body through nose or mouth
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61J—CONTAINERS SPECIALLY ADAPTED FOR MEDICAL OR PHARMACEUTICAL PURPOSES; DEVICES OR METHODS SPECIALLY ADAPTED FOR BRINGING PHARMACEUTICAL PRODUCTS INTO PARTICULAR PHYSICAL OR ADMINISTERING FORMS; DEVICES FOR ADMINISTERING FOOD OR MEDICINES ORALLY; BABY COMFORTERS; DEVICES FOR RECEIVING SPITTLE
- A61J15/00—Feeding-tubes for therapeutic purposes
- A61J15/0026—Parts, details or accessories for feeding-tubes
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M25/00—Catheters; Hollow probes
- A61M25/0043—Catheters; Hollow probes characterised by structural features
- A61M2025/0063—Catheters; Hollow probes characterised by structural features having means, e.g. stylets, mandrils, rods or wires to reinforce or adjust temporarily the stiffness, column strength or pushability of catheters which are already inserted into the human body
- A61M2025/0065—Catheters; Hollow probes characterised by structural features having means, e.g. stylets, mandrils, rods or wires to reinforce or adjust temporarily the stiffness, column strength or pushability of catheters which are already inserted into the human body which become stiffer or softer when becoming wet or humid, e.g. immersed within a liquid
Abstract
ABSTRACT OF THE DISCLOSURE
The composite intubation tube has an outer pliable outer layer of plastic material and an inner concentric layer made of a hydrophilic polymer which becomes very soft and flexible in a wetted state. After intubation in a patient, a flow of gastric fluids or an inflow of nutrient solution wets the inner layer so the tube becomes very soft so that pressure points on the tissue of the patient are eliminated.
The composite intubation tube has an outer pliable outer layer of plastic material and an inner concentric layer made of a hydrophilic polymer which becomes very soft and flexible in a wetted state. After intubation in a patient, a flow of gastric fluids or an inflow of nutrient solution wets the inner layer so the tube becomes very soft so that pressure points on the tissue of the patient are eliminated.
Description
~ ~Z965~1~
A FLEXIBLE COMPOSITE INTUBATION TUBE
This invention relates to a flexible composite intubation tube.
Heretofore, various types of intubation tubes have been known for introducing or removing fluid materials from a medical patient. For example, in the case of a gastric feeding tube, the tube is usually inserted through the nose and esophagus into the stomach of the patient and left in place for sub6equent feeding of nutrients into the patient. Examples of such tubes are described in U.S. Patents 4,249,535; 4,410,320; 4,547,192 and 4,610,673.
Generally, the tubes must have sufficient rigidity in order to be inserted into the patient while at the same time not causing damage to the internal passages within the patient. In order to achieve these purposes, it has been known to use a stylet with a collapsible tube so that the stylet can be used to introduce the tube and thereafter removed in order to leave the tube in place.
However, in such cases, the use of a stylet has raised the risk of damaging the internal passages and/or organs, such as a lung of a patient, particularly where the internal passages have bends. Further, the use of a stylet normally requires the attendance of a physician lZ96S92 in order to ensure that the tube is properly intubated.
In other cases, it has been proposed to eliminate the need for a stylet so as to avoid the attendant risks.
For example, as suggested in U.S. Patent 4,610,673, it is proposed to provide a feeding tube which is comprised of an elongated shaft portion and an intermediate portion which extends from a distal end to the shaft as well as a weighted bolus at the distal end. The shaft is to be constructed to have sufficient flexibility to pass the nostril of a patient but with sufficient rigidity to permit intubation without the use of a stylet. The intermediate portion is to be constructed with an enlarged dimension relative to the shaft while being provided with a transverse slot to define an inner passage and a pair of side apertures for passing feeding formula to the exterior. The intermediate portion is also to be constructed to be at least as rigid as the shaft and sufficiently flexible to permit passage through a nostril of a patient during installation but nevertheless 6ufficiently rigid to permit installation without the use of a stylet.
As i8 known, the nasal passages and esophagal passages as well as the intestinal passages of a patient have numerous bends. Hence, when a feeding tube is inserted, the tube flexes around such bends and places pressure at the contact point6 with the passage walls. Over a period of time, which periods may be relatively short, the pressure points create a risk of necrosis of the pressured ti~sue. In order to avoid subsequent infection, it is necessary, from time-to-time, to remove the feeding tubes to reduce or eliminate the risk of infection.
Accordingly, it is an ob~ect of the invention to provide a feeding tube which can remain in place for relatively lZ96S92 long periods of time.
It is another object of the invention to reduce or eliminate pressure points on the passage walls of a patient by an intubated tube.
S It is another object of the invention to provide a feeding tube which can be non-rigidified after intubation.
It is another object of the invention to provide a feeding tube which is rigid when being intubated and non-rigid after being intubated.
Briefly, the invention provides a flexible composite intubation tube which is comprised of an outer layer of plastic material which is characterized in being pliable and an inner concentric layer of plastic material which defines a flow path or lumen for a fluid and which is made of a hydrophilic polymer which is characterized in being stiff in a dry state and in being very soft and flexible in a wetted state.
The tube is of a unitary construction in that the concentric layers are co-extruded. Further, the tube is of a uniform outside diameter from the proximal end to the distal end. The lumen provided by the inner layer is of standard size. For example, the inner layer may have an inner diameter of 0.08 inches in order to provide a lumen for use of the tube as a naso-gastric feeding tube.
In one embodiment, the inner layer has an inner diameter of 0.080 inches while the outer layer has an outer diameter of 0.113 inches. In addition, the inner layer is made of a thickness of 0.011 inches. In another embodiment, the inner layer may have an inner diameter of 0.080 inches and a thickness of 0.0006 inches so that the outer diameter is 0.092 inches.
The outer layer of the tube may be made of any suitable pliable plastic material to cooperate with the inner layer in order to contain the inner layer, be pliable and flexible and have sufficient body to prevent tube bursting during the normal syringe fluid injection. For example, the outer layer may be made of a polyether polyurethane resin while the inner layer is made of a polyurethane resin containing glycol chains.
The outer layer is selected to be compatible with body tissue and have softness and flexibility properties. The outer layer must not burst under normal syringe fluid injection conditions and have ~ood tensile strength. Materials which satisfy these requirements include polyurethanes and, in particular, a thermoplastic elastomer supplied by the Upjohn Co. of Kalamazoo, Michigan under the name Pellethane (Trade Mark).
The combination of a soft outer polyurethane layer or jacket made from a soft material with a Durometer of from 60A to 80A (Shore A scale) and a thickness one third (1/3) to two thirds ~2/3) that of a conventional tube coupled with a hydrophilic polyurethane inner core having extremely low stiffness when hydrated produces a composite tube which can not support itself thus virtually eliminating pressure points between the tube and the human body when in use.
The pressure of the hydrated hydrophilic polyurethane inner core causes the composite tube to behave very much like a substantially lower Durometer tube than a tube made of a Durometer of the outer layer. For the examples given, the composite hydrated ~ tube could not support its own weight and behaved very much like a "wet ~Z96S92 noodle". A more extended polyurethane material having a Durometer of 50 A exhibits apparent greater stiffness properties on a comparison basis.
When in use, the tube may be inserted through the nasal passage of a patient without a stylet and subsequently passed through the esophagal passages and intestinal passages as required for placement, for example in the stomach or in the small intestine as required. Once the tube has been put in place, any gastric fluids which move through the tube or any fluid nutrient solution passed through the tube for the feeding of the patient will wet the walls of the lumen of the inner hydrophilic layer. This causes the inner layer to swell while at the same time causing the inner layer to become very soft and flexible. However, it has been found that the swelling of the inner layer does not close the lumen so that fluid may still flow through the tube in either direction, as required. At same time, the overall tube becomes very soft and pliable so that the resistance to bending is substantially eliminated. In a sense, the "memory" of the plastic material is erased. As a result, the tube conforms to the bends and shape of the passages in which the tube is inserted so as to avoid pressing on the walls of the passages.
Because of the softened nature of the tube after intubation, the tube may be left in place for relatively long periods of time. More importantly, tube pressure against tissue is substantially eliminated thus increasing patient comfort and product acceptance.
These and other objects and advantages of the invention will become more apparent from the following detailed description taken in conjunction with the accompanying drawings wherein.
~Z96S92 Fig. 1 schematically illustrates a naso-gastric tube constructed in accordance with the invention and placed in a patient:
Fig. 2 illustrates an enlarged part-cross sectional view of a section of the tube of Fig. l;
Fig. 3 illustrates a part perspective view of several sections of a tube constructed in accordance with the invention on the edge of a table;
Fig. 4 schematically illustrates a prior art tube in place; and Fig. 5 schematically illustrates a tube according to the invention in place.
Referring to Fig. 1, the intubation tube is constructed for use as a naso-gastric tube 10 for intubation within the nasal passages 11, esophagus 12 and stomach 13 of a patient. As indicated, the tube 10 follows the tortuous path defined by the nasal passages 11, esophagus 12 and stomach 13.
Referring to Fig. 2, the na60-gastric tube 10 is of multi-layer unitary construction. For example, the tube 10 has an outer layer 14 of plastic material which is characterized in being pliable and an inner concentric layer 15 of plastic material which defines a flow path or lumen for a fluid.
~he outer layer 14 i6 selected for strength, toughness, clarity, toxicity properties and the like. By way of example, the outer layer is made of a polyether, polyurethane resin such as Pellethane 2363-80AE as sold by Up~ohn.
lZ96592 The inner layer 15 is made of a hydrophilic polymer which is characterized in being stiff in a dry state and in being very soft and flexible in a wetted state. For example, the inner layer 15 is made of a polymer characterized as D-2 supplied by Tyndale Plains -Hunter, a polyurethane resin containing glycol chains to render the material hydrophilic.
The layers 14, 15 are bonded together to form an integral tube which is characterized in being sufficiently pliable and self-supporting to be inserted per se into a naso-gastric passage while being soft and flexible in a wetted state within the naso-gastric passage to avoid creating pressure points therein and without closing the lumen.
By way of example, a tube 10 was co-extruded using a Pellethane 2363-80AE and a D-2 polymer. These materials were extruded into a tube 10 having an inner diameter of 0.080 inches and an outer diameter of 0.113 inches. The inner layer 15 also had a thickness of 0.011 inches while the outer layer 14 had a thickness of 0.0055 inches. Two sections 17 of the tube were then cut and placed on the edge of a table 16, for example as indicated in Fig. 3 and compared with sections 18 of a tube of the same outside and inside diameter which were, as extruded, rigid and would bend only with difficulty.
In addition, one tube section 17 had water passed through the lumen and became flexible and would not support itself when a portion was placed beyond the edge of the table 16 as indicated. Further, the inner hydrophilic core of this tube section 17 did not buckle up and fill or otherwise obstruct the inner lumen.
By way of example, a second tube was extruded using the same materials as above. This tube also had an outside lZ96592 -diameter of 0.113 inches and an inner diameter of 0.080 inches. However, the inner layer was of a thickness of 0.006 inches while the outer layer had a thickness of 0.0105 inches. The rigid properties of thi6 tube in the dry state were also equivalent to those of the first example. Again, when the lumen was wetted out, the composite tube could not support its own weight.
Of note, the bond strength between the two plastic materials at the interface was exceptional for both of the examples.
Referring to Fig. 1, after intubation of the tube 10, the gastric fluids which may be withdrawn from the stomach 13 or a nutrient solution passed into the stomach 13 will wet the inner hydrophilic layer 15 to become very soft and non-self-supporting. However, the relatively thin outer layer 14 will retain its integrity while at the same time protecting the inner layer 15.
The tube 10 also will become non-self-supporting and soft so that no undue pressure is placed on the various internal passageways of the patient, such as the nasal, pharynx and esophagal passageways. Thus, tissue irritation, inflammation and necrosis can be substantially reduced if not eliminated.
The tube 10 initially possesses sufficient rigidity as well as pliability so as to be inserted into a patient without the need for a stylet. As a result, the complications of a stylet are removed and a nurse may effect placement without the need for an attending physician. Accordingly, there can be a cost savings for the intubation of such tubes in a patient.
Referring to Figs. 4 and 5, by way of comparison, a tube 19 of conventional structure and a composite tube 20 made in accordance with the invention are shown -` lZ96S92 intubated in a patient. In the cas~ of the tube 19 of prior art construction (Fig. 4), the tube 19 is pressed against the tissue at several points 21, 22 of the patient creating pressure points. However, in the case of the composite tube 20 (Fig. 5), this tube 20 being hydrated follows the contour of the patient's passages without creating pressure points.
Further, since the tube does not require any stylet, the need to provide a lubricant coating on the interior of the tube to ensure removal of a stylet is eliminated.
As indicated in Fig. 1, the tube 10 has a uniform diameter from the proximal end to the distal end. Thus, the tube can be made by simple extrusion process.
Further, the tube 10 can be connected to a bolus 23, for example as described in U.S. Patent 4,705,709 via a connecting member provided with suitable openings in communication with the lumen of the tube 10 in order to permit the passage of fluids from the lumen to the exterior and vice versa.
The invention thus provides an intubation tube which can be simply manufactured and which does not require a stylet for intubation. Further, the invention provides an intubation tube which is sufficiently rigid to be intubated without the need for a stylet as well as one which becomes very soft and pliable upon being wetted after intubation so as to eliminate or substantially reduce irritation and necrosis at bends within a patient's passages.
A FLEXIBLE COMPOSITE INTUBATION TUBE
This invention relates to a flexible composite intubation tube.
Heretofore, various types of intubation tubes have been known for introducing or removing fluid materials from a medical patient. For example, in the case of a gastric feeding tube, the tube is usually inserted through the nose and esophagus into the stomach of the patient and left in place for sub6equent feeding of nutrients into the patient. Examples of such tubes are described in U.S. Patents 4,249,535; 4,410,320; 4,547,192 and 4,610,673.
Generally, the tubes must have sufficient rigidity in order to be inserted into the patient while at the same time not causing damage to the internal passages within the patient. In order to achieve these purposes, it has been known to use a stylet with a collapsible tube so that the stylet can be used to introduce the tube and thereafter removed in order to leave the tube in place.
However, in such cases, the use of a stylet has raised the risk of damaging the internal passages and/or organs, such as a lung of a patient, particularly where the internal passages have bends. Further, the use of a stylet normally requires the attendance of a physician lZ96S92 in order to ensure that the tube is properly intubated.
In other cases, it has been proposed to eliminate the need for a stylet so as to avoid the attendant risks.
For example, as suggested in U.S. Patent 4,610,673, it is proposed to provide a feeding tube which is comprised of an elongated shaft portion and an intermediate portion which extends from a distal end to the shaft as well as a weighted bolus at the distal end. The shaft is to be constructed to have sufficient flexibility to pass the nostril of a patient but with sufficient rigidity to permit intubation without the use of a stylet. The intermediate portion is to be constructed with an enlarged dimension relative to the shaft while being provided with a transverse slot to define an inner passage and a pair of side apertures for passing feeding formula to the exterior. The intermediate portion is also to be constructed to be at least as rigid as the shaft and sufficiently flexible to permit passage through a nostril of a patient during installation but nevertheless 6ufficiently rigid to permit installation without the use of a stylet.
As i8 known, the nasal passages and esophagal passages as well as the intestinal passages of a patient have numerous bends. Hence, when a feeding tube is inserted, the tube flexes around such bends and places pressure at the contact point6 with the passage walls. Over a period of time, which periods may be relatively short, the pressure points create a risk of necrosis of the pressured ti~sue. In order to avoid subsequent infection, it is necessary, from time-to-time, to remove the feeding tubes to reduce or eliminate the risk of infection.
Accordingly, it is an ob~ect of the invention to provide a feeding tube which can remain in place for relatively lZ96S92 long periods of time.
It is another object of the invention to reduce or eliminate pressure points on the passage walls of a patient by an intubated tube.
S It is another object of the invention to provide a feeding tube which can be non-rigidified after intubation.
It is another object of the invention to provide a feeding tube which is rigid when being intubated and non-rigid after being intubated.
Briefly, the invention provides a flexible composite intubation tube which is comprised of an outer layer of plastic material which is characterized in being pliable and an inner concentric layer of plastic material which defines a flow path or lumen for a fluid and which is made of a hydrophilic polymer which is characterized in being stiff in a dry state and in being very soft and flexible in a wetted state.
The tube is of a unitary construction in that the concentric layers are co-extruded. Further, the tube is of a uniform outside diameter from the proximal end to the distal end. The lumen provided by the inner layer is of standard size. For example, the inner layer may have an inner diameter of 0.08 inches in order to provide a lumen for use of the tube as a naso-gastric feeding tube.
In one embodiment, the inner layer has an inner diameter of 0.080 inches while the outer layer has an outer diameter of 0.113 inches. In addition, the inner layer is made of a thickness of 0.011 inches. In another embodiment, the inner layer may have an inner diameter of 0.080 inches and a thickness of 0.0006 inches so that the outer diameter is 0.092 inches.
The outer layer of the tube may be made of any suitable pliable plastic material to cooperate with the inner layer in order to contain the inner layer, be pliable and flexible and have sufficient body to prevent tube bursting during the normal syringe fluid injection. For example, the outer layer may be made of a polyether polyurethane resin while the inner layer is made of a polyurethane resin containing glycol chains.
The outer layer is selected to be compatible with body tissue and have softness and flexibility properties. The outer layer must not burst under normal syringe fluid injection conditions and have ~ood tensile strength. Materials which satisfy these requirements include polyurethanes and, in particular, a thermoplastic elastomer supplied by the Upjohn Co. of Kalamazoo, Michigan under the name Pellethane (Trade Mark).
The combination of a soft outer polyurethane layer or jacket made from a soft material with a Durometer of from 60A to 80A (Shore A scale) and a thickness one third (1/3) to two thirds ~2/3) that of a conventional tube coupled with a hydrophilic polyurethane inner core having extremely low stiffness when hydrated produces a composite tube which can not support itself thus virtually eliminating pressure points between the tube and the human body when in use.
The pressure of the hydrated hydrophilic polyurethane inner core causes the composite tube to behave very much like a substantially lower Durometer tube than a tube made of a Durometer of the outer layer. For the examples given, the composite hydrated ~ tube could not support its own weight and behaved very much like a "wet ~Z96S92 noodle". A more extended polyurethane material having a Durometer of 50 A exhibits apparent greater stiffness properties on a comparison basis.
When in use, the tube may be inserted through the nasal passage of a patient without a stylet and subsequently passed through the esophagal passages and intestinal passages as required for placement, for example in the stomach or in the small intestine as required. Once the tube has been put in place, any gastric fluids which move through the tube or any fluid nutrient solution passed through the tube for the feeding of the patient will wet the walls of the lumen of the inner hydrophilic layer. This causes the inner layer to swell while at the same time causing the inner layer to become very soft and flexible. However, it has been found that the swelling of the inner layer does not close the lumen so that fluid may still flow through the tube in either direction, as required. At same time, the overall tube becomes very soft and pliable so that the resistance to bending is substantially eliminated. In a sense, the "memory" of the plastic material is erased. As a result, the tube conforms to the bends and shape of the passages in which the tube is inserted so as to avoid pressing on the walls of the passages.
Because of the softened nature of the tube after intubation, the tube may be left in place for relatively long periods of time. More importantly, tube pressure against tissue is substantially eliminated thus increasing patient comfort and product acceptance.
These and other objects and advantages of the invention will become more apparent from the following detailed description taken in conjunction with the accompanying drawings wherein.
~Z96S92 Fig. 1 schematically illustrates a naso-gastric tube constructed in accordance with the invention and placed in a patient:
Fig. 2 illustrates an enlarged part-cross sectional view of a section of the tube of Fig. l;
Fig. 3 illustrates a part perspective view of several sections of a tube constructed in accordance with the invention on the edge of a table;
Fig. 4 schematically illustrates a prior art tube in place; and Fig. 5 schematically illustrates a tube according to the invention in place.
Referring to Fig. 1, the intubation tube is constructed for use as a naso-gastric tube 10 for intubation within the nasal passages 11, esophagus 12 and stomach 13 of a patient. As indicated, the tube 10 follows the tortuous path defined by the nasal passages 11, esophagus 12 and stomach 13.
Referring to Fig. 2, the na60-gastric tube 10 is of multi-layer unitary construction. For example, the tube 10 has an outer layer 14 of plastic material which is characterized in being pliable and an inner concentric layer 15 of plastic material which defines a flow path or lumen for a fluid.
~he outer layer 14 i6 selected for strength, toughness, clarity, toxicity properties and the like. By way of example, the outer layer is made of a polyether, polyurethane resin such as Pellethane 2363-80AE as sold by Up~ohn.
lZ96592 The inner layer 15 is made of a hydrophilic polymer which is characterized in being stiff in a dry state and in being very soft and flexible in a wetted state. For example, the inner layer 15 is made of a polymer characterized as D-2 supplied by Tyndale Plains -Hunter, a polyurethane resin containing glycol chains to render the material hydrophilic.
The layers 14, 15 are bonded together to form an integral tube which is characterized in being sufficiently pliable and self-supporting to be inserted per se into a naso-gastric passage while being soft and flexible in a wetted state within the naso-gastric passage to avoid creating pressure points therein and without closing the lumen.
By way of example, a tube 10 was co-extruded using a Pellethane 2363-80AE and a D-2 polymer. These materials were extruded into a tube 10 having an inner diameter of 0.080 inches and an outer diameter of 0.113 inches. The inner layer 15 also had a thickness of 0.011 inches while the outer layer 14 had a thickness of 0.0055 inches. Two sections 17 of the tube were then cut and placed on the edge of a table 16, for example as indicated in Fig. 3 and compared with sections 18 of a tube of the same outside and inside diameter which were, as extruded, rigid and would bend only with difficulty.
In addition, one tube section 17 had water passed through the lumen and became flexible and would not support itself when a portion was placed beyond the edge of the table 16 as indicated. Further, the inner hydrophilic core of this tube section 17 did not buckle up and fill or otherwise obstruct the inner lumen.
By way of example, a second tube was extruded using the same materials as above. This tube also had an outside lZ96592 -diameter of 0.113 inches and an inner diameter of 0.080 inches. However, the inner layer was of a thickness of 0.006 inches while the outer layer had a thickness of 0.0105 inches. The rigid properties of thi6 tube in the dry state were also equivalent to those of the first example. Again, when the lumen was wetted out, the composite tube could not support its own weight.
Of note, the bond strength between the two plastic materials at the interface was exceptional for both of the examples.
Referring to Fig. 1, after intubation of the tube 10, the gastric fluids which may be withdrawn from the stomach 13 or a nutrient solution passed into the stomach 13 will wet the inner hydrophilic layer 15 to become very soft and non-self-supporting. However, the relatively thin outer layer 14 will retain its integrity while at the same time protecting the inner layer 15.
The tube 10 also will become non-self-supporting and soft so that no undue pressure is placed on the various internal passageways of the patient, such as the nasal, pharynx and esophagal passageways. Thus, tissue irritation, inflammation and necrosis can be substantially reduced if not eliminated.
The tube 10 initially possesses sufficient rigidity as well as pliability so as to be inserted into a patient without the need for a stylet. As a result, the complications of a stylet are removed and a nurse may effect placement without the need for an attending physician. Accordingly, there can be a cost savings for the intubation of such tubes in a patient.
Referring to Figs. 4 and 5, by way of comparison, a tube 19 of conventional structure and a composite tube 20 made in accordance with the invention are shown -` lZ96S92 intubated in a patient. In the cas~ of the tube 19 of prior art construction (Fig. 4), the tube 19 is pressed against the tissue at several points 21, 22 of the patient creating pressure points. However, in the case of the composite tube 20 (Fig. 5), this tube 20 being hydrated follows the contour of the patient's passages without creating pressure points.
Further, since the tube does not require any stylet, the need to provide a lubricant coating on the interior of the tube to ensure removal of a stylet is eliminated.
As indicated in Fig. 1, the tube 10 has a uniform diameter from the proximal end to the distal end. Thus, the tube can be made by simple extrusion process.
Further, the tube 10 can be connected to a bolus 23, for example as described in U.S. Patent 4,705,709 via a connecting member provided with suitable openings in communication with the lumen of the tube 10 in order to permit the passage of fluids from the lumen to the exterior and vice versa.
The invention thus provides an intubation tube which can be simply manufactured and which does not require a stylet for intubation. Further, the invention provides an intubation tube which is sufficiently rigid to be intubated without the need for a stylet as well as one which becomes very soft and pliable upon being wetted after intubation so as to eliminate or substantially reduce irritation and necrosis at bends within a patient's passages.
Claims (26)
1. A flexible composite intubation tube for connection to a bolus comprising:
a relatively thin outer layer (14) of plastic material having a pliable and flexible nature; and an inner concentric layer (15) within said outer layer (14) defining a lumen for fluid passage and being made of a plastic hydrophilic material, said inner layer (14) being characterized in being stiff in a dry state to permit insertion of the tube into a naso-gastric passage and in being very soft and flexible in a wetted state within the naso-gastric passage without closing said lumen.
a relatively thin outer layer (14) of plastic material having a pliable and flexible nature; and an inner concentric layer (15) within said outer layer (14) defining a lumen for fluid passage and being made of a plastic hydrophilic material, said inner layer (14) being characterized in being stiff in a dry state to permit insertion of the tube into a naso-gastric passage and in being very soft and flexible in a wetted state within the naso-gastric passage without closing said lumen.
2. A tube as set forth in claim 1 characterized in that said outer layer (14) is made of a polyether polyurethane resin and said inner layer (15) is made of a polyurethane resin containing glycol chains.
3. A tube as set forth in claim 1 characterized in that said inner layer (15) has an inner diameter of 0.080 inches and said outer layer (14) has an outer diameter of 0.113 inches.
4. A tube as set forth in claim 2 characterized in that said inner layer (15) has an inner diameter of 0.080 inches and said outer layer (14) has an outer diameter of 0.113 inches.
5. A tube as set forth in claim 3 characterized in that said inner layer (15) is of a greater thickness than said outer layer (14).
6. A tube as set forth in claim 4 characterized in that said inner layer (15) is of a greater thickness than said outer layer (14).
7. A tube as set forth in claim 3 wherein said inner layer (15) is characterized in having a thickness of 0.011 inches.
8. A tube as set forth in claim 4 wherein said inner layer (15) is characterized in having a thickness of 0.011 inches.
9. A tube as set forth in any one of claims 1 to 8 characterized in that said layers (14, 15) are bonded together to form an integral tube.
10. A tube as set forth in any one of claims 1 to 6 characterized in that said layers (14, 15) are co-extruded to form a unitary construction.
11. A tube as set forth in any one of claims 1 to 8 characterized in that said outer layer (14) has a Durometer of from 60A to 80A (Shore A scale).
12. A tube as set forth in any one of claims 1 to 8 characterized in that said layers (14, 15) are bonded together to form an integral tube and in that said outer layer (14) has a Durometer of from 60A to 80A (Shore A scale).
13. A tube as set forth in any one of claims 1 to 8 characterized in that said layers (14, 15) are co-extruded to form a unitary construction and in that said outer layer (14) has a Durometer of from 60A to 80A (Shore A scale).
14. A tube as set forth in any one of claims 1 to 8 characterized in being a naso-gastric tube having a lumen of 0.080 inches.
15. A tube as set forth in any one of claims 1 to 8 characterized in that said layers (14, 15) are bonded together to form an integral tube or co-extruded to form a unitary construction and in that said tube is a naso-gastric tube having a lumen of 0.080 inches.
16. A tube as set forth in any one of claims 1 to 8 characterized in that said layers (14, 15) are bonded together to form an integral tube or co-extruded to form a unitary construction, in that said outer layer (14) has a Durometer of from 60A to 80A (Shore A scale), and in that said tube is a naso-gastric tube having a lumen of 0.080 inches.
17. The tube as set forth in claim 1 wherein said outer layer is soft and has sufficient body to prevent tube bursting during syringe fluid injection.
18. A flexible composite intubation tube for connection to a bolus comprising:
a relatively thin outer layer of plastic material characterized in being pliable and flexible; and an inner concentric layer of plastic material defining a flow path for a fluid, said inner layer having an inner diameter of 0.080 inches and being made of a hydrophilic polymer characterized in being stiff in a dry state and in being very soft and flexible in a wetted state; said layers forming a tube characterized in being sufficiently pliable and self-supporting to be inserted per se into a naso-gastric passage and in being soft and flexible in a wetted state within the naso-gastric passage to avoid creating pressure points therein and without closing said lumen.
a relatively thin outer layer of plastic material characterized in being pliable and flexible; and an inner concentric layer of plastic material defining a flow path for a fluid, said inner layer having an inner diameter of 0.080 inches and being made of a hydrophilic polymer characterized in being stiff in a dry state and in being very soft and flexible in a wetted state; said layers forming a tube characterized in being sufficiently pliable and self-supporting to be inserted per se into a naso-gastric passage and in being soft and flexible in a wetted state within the naso-gastric passage to avoid creating pressure points therein and without closing said lumen.
19. A composite intubation tube as set forth in claim 18 wherein said layer are co-extruded to form a unitary construction.
20. A composite intubation tube as set forth in claim 18 wherein said outer layer has an outer diameter of 0.113 inches.
21. A composite intubation tube as set forth in claim 20 wherein said inner layer has a thickness of 0.011 inches.
22. A composite intubation tube as set forth in claim 20 wherein said outer layer is made of a polyether polyurethane resin and said inner layer is made of a polyurethane resin containing glycol chains.
23. A composite intubation tube as set forth in claim 20 wherein said inner layer has a thickness of 0.006 inches.
24. A composite intubation tube as set forth in claim 18 wherein said outer layer is made of a polyether polyurethane resin and said inner layer is made of a polyurethane resin containing glycol chains.
25. A naso-gastric tube for connection to a bolus comprising:
a soft outer layer of plastic material of pliable and flexible nature having sufficient body to prevent tube bursting during syringe fluid injection; and an inner concentric layer within said outer layer, said inner layer defining a lumen for fluid passage and being made of a plastic hydrophilic material characterized in being stiff in a dry state to permit insertion of the tube into a naso-gastric passage and in being very soft and flexible in a wetted state within the naso-gastric passage to render the tube non-self- supporting without closing said lumen to eliminate pressure points in the passage.
a soft outer layer of plastic material of pliable and flexible nature having sufficient body to prevent tube bursting during syringe fluid injection; and an inner concentric layer within said outer layer, said inner layer defining a lumen for fluid passage and being made of a plastic hydrophilic material characterized in being stiff in a dry state to permit insertion of the tube into a naso-gastric passage and in being very soft and flexible in a wetted state within the naso-gastric passage to render the tube non-self- supporting without closing said lumen to eliminate pressure points in the passage.
26. A naso-gastric tube as set forth in claim 25 wherein said outer layer is made of a polyether polyurethane resin and said inner layer is made of a polyurethane resin containing glycol chains.
Applications Claiming Priority (2)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| US07/043,865 US4798597A (en) | 1987-04-29 | 1987-04-29 | Flexible composite intubation tube |
| US043,865 | 1987-04-29 |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CA1296592C true CA1296592C (en) | 1992-03-03 |
Family
ID=21929279
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA000565275A Expired - Lifetime CA1296592C (en) | 1987-04-29 | 1988-04-27 | Flexible composite intubation tube |
Country Status (5)
| Country | Link |
|---|---|
| US (1) | US4798597A (en) |
| EP (1) | EP0289218A3 (en) |
| JP (1) | JPS6420855A (en) |
| AU (1) | AU610578B2 (en) |
| CA (1) | CA1296592C (en) |
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| US4994047A (en) * | 1988-05-06 | 1991-02-19 | Menlo Care, Inc. | Multi-layer cannula structure |
| US5061254A (en) * | 1989-06-21 | 1991-10-29 | Becton, Dickinson And Company | Thermoplastic elastomeric hydrophilic polyetherurethane expandable catheter |
| US4976704A (en) * | 1989-07-17 | 1990-12-11 | Mclees Donald J | Moisture disabled needle |
| IE67657B1 (en) * | 1990-03-26 | 1996-04-17 | Becton Dickinson Co | Catheter tubing of controlled in vivo softening |
| US5226899A (en) * | 1990-03-26 | 1993-07-13 | Becton, Dickinson And Company | Catheter tubing of controlled in vivo softening |
| US5102401A (en) * | 1990-08-22 | 1992-04-07 | Becton, Dickinson And Company | Expandable catheter having hydrophobic surface |
| US5112312A (en) * | 1991-03-14 | 1992-05-12 | Luther Medical Products, Inc. | Vascular/venous access device and method of utilizing and forming the same |
| US5348537A (en) * | 1992-07-15 | 1994-09-20 | Advanced Cardiovascular Systems, Inc. | Catheter with intraluminal sealing element |
| US5403283A (en) * | 1993-10-28 | 1995-04-04 | Luther Medical Products, Inc. | Percutaneous port catheter assembly and method of use |
| US5460619A (en) | 1994-04-04 | 1995-10-24 | Esrock; Bernard S. | Disposable tubular device and method |
| US5531701A (en) * | 1994-06-06 | 1996-07-02 | Luther Medical Products, Inc. | Over-the-needle catheter |
| US5522807A (en) * | 1994-09-07 | 1996-06-04 | Luther Medical Products, Inc. | Dual lumen infusion/aspiration catheter |
| US5554136A (en) * | 1994-09-07 | 1996-09-10 | Luther Medical Products, Inc. | Dual lumen infusion/aspiration catheter |
| US5738660A (en) * | 1994-10-27 | 1998-04-14 | Luther Medical Products, Inc. | Percutaneous port catheter assembly and method of use |
| US5702372A (en) | 1995-02-08 | 1997-12-30 | Medtronic, Inc. | Lined infusion catheter |
| US6045734A (en) * | 1995-05-24 | 2000-04-04 | Becton Dickinson And Company | Process of making a catheter |
| US5878745A (en) | 1996-03-01 | 1999-03-09 | Brain; Archibald I.J. | Gastro-laryngeal mask |
| US5913848A (en) | 1996-06-06 | 1999-06-22 | Luther Medical Products, Inc. | Hard tip over-the-needle catheter and method of manufacturing the same |
| US6055984A (en) | 1996-11-06 | 2000-05-02 | Brain; Archibald I. J. | Endotracheal tube construction |
| US6139525A (en) * | 1997-07-08 | 2000-10-31 | Advanced Cardiovascular Systems, Inc. | Fusion bonding of catheter components |
| US6010521A (en) * | 1997-11-25 | 2000-01-04 | Advanced Cardiovasular Systems, Inc. | Catheter member with bondable layer |
| US6631720B1 (en) * | 1999-10-07 | 2003-10-14 | Archibald I. J. Brain | Laryngeal mask with large-bore gastric drainage |
| US7264858B2 (en) * | 2002-10-29 | 2007-09-04 | Lubrizol Advanced Materials, Inc. | Multilayered articles having biocompatibility and biostability characteristics |
| US20090165784A1 (en) * | 2007-12-28 | 2009-07-02 | Tyco Healthcare Group Lp | Lubricious intubation device |
| FR2863961B1 (en) * | 2003-12-22 | 2007-08-17 | Faurecia Sieges Automobile | SEAT SEAT STRUCTURE OF VEHICLE PROVIDED WITH A SEAT COMPRISING SUCH A STRUCTURE |
| GB0510951D0 (en) | 2005-05-27 | 2005-07-06 | Laryngeal Mask Company The Ltd | Laryngeal mask airway device |
| CN101959553B (en) * | 2007-10-11 | 2014-12-17 | 冯亚山 | A device for tube feeding |
| GB0903654D0 (en) | 2009-03-03 | 2009-04-15 | Laryngeal Mask Company The Ltd | Artificial airway device |
| KR20120070559A (en) | 2009-07-06 | 2012-06-29 | 우메데이스 리미티드 | Artificial airway |
| CN102498377B (en) | 2009-08-13 | 2014-05-14 | 奇姆德恩医疗有限公司 | Pressure indicator |
| JP5836931B2 (en) | 2010-03-26 | 2015-12-24 | テルモ株式会社 | Indwelling needle assembly |
| GB201016562D0 (en) | 2010-10-01 | 2010-11-17 | Laryngeal Mask Company The Ltd | Artificial airway device |
| AU2011315319B2 (en) | 2010-10-15 | 2016-06-02 | Teleflex Life Sciences Llc | Artificial airway device |
| CN109200416A (en) | 2011-02-02 | 2019-01-15 | 梅田有限公司 | improved artificial airway |
| GB201120628D0 (en) | 2011-11-30 | 2012-01-11 | Laryngeal Mask Company The Ltd | Endoscopy device |
| JP6794349B2 (en) | 2015-05-15 | 2020-12-02 | テルモ株式会社 | Catheter assembly |
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| GB1220114A (en) * | 1967-05-12 | 1971-01-20 | Ceskoslovenska Akademie Ved | Method of joining polyglycolmethacrylates together with other materials |
| US3566874A (en) * | 1968-08-13 | 1971-03-02 | Nat Patent Dev Corp | Catheter |
| US3695921A (en) * | 1970-09-09 | 1972-10-03 | Nat Patent Dev Corp | Method of coating a catheter |
| US3746683A (en) * | 1970-12-24 | 1973-07-17 | Department Of Health Education | Thromboresistant articles made from polyurethanes containing a polypropylene glycol-ethylene oxide block copolymer |
| US3861396A (en) * | 1973-08-08 | 1975-01-21 | Hydro Med Sciences Inc | Drainage tube |
| CS173836B1 (en) * | 1974-03-19 | 1977-03-31 | ||
| US4306563A (en) * | 1979-11-28 | 1981-12-22 | Firma Pfrimmer & Co. Pharmazeutische Werke Erlangen Gmbh | Catheter for introduction into body cavities |
| US4373009A (en) * | 1981-05-18 | 1983-02-08 | International Silicone Corporation | Method of forming a hydrophilic coating on a substrate |
| US4410320A (en) * | 1981-08-28 | 1983-10-18 | Ethox Corp. | Weighted enteric feeding tube |
| CA1191064A (en) * | 1981-12-31 | 1985-07-30 | Bard (C. R.), Inc. | Catheter with selectively rigidified portion |
| SE430695B (en) * | 1982-04-22 | 1983-12-05 | Astra Meditec Ab | PROCEDURE FOR THE PREPARATION OF A HYDROPHILIC COATING AND ACCORDING TO THE PROCEDURE OF MEDICAL ARTICLES |
| GB8517091D0 (en) * | 1985-07-05 | 1985-08-14 | Franklin Medical Ltd | Balloon catheters |
| SE8504501D0 (en) * | 1985-09-30 | 1985-09-30 | Astra Meditec Ab | METHOD OF FORMING AN IMPROVED HYDROPHILIC COATING ON A POLYMER SURFACE |
| US4705709A (en) * | 1985-09-25 | 1987-11-10 | Sherwood Medical Company | Lubricant composition, method of coating and a coated intubation device |
-
1987
- 1987-04-29 US US07/043,865 patent/US4798597A/en not_active Expired - Lifetime
-
1988
- 1988-04-21 EP EP88303608A patent/EP0289218A3/en not_active Withdrawn
- 1988-04-27 CA CA000565275A patent/CA1296592C/en not_active Expired - Lifetime
- 1988-04-28 AU AU15260/88A patent/AU610578B2/en not_active Ceased
- 1988-04-28 JP JP63107391A patent/JPS6420855A/en active Granted
Also Published As
| Publication number | Publication date |
|---|---|
| JPH0244548B2 (en) | 1990-10-04 |
| AU1526088A (en) | 1988-11-03 |
| EP0289218A2 (en) | 1988-11-02 |
| JPS6420855A (en) | 1989-01-24 |
| EP0289218A3 (en) | 1990-06-27 |
| US4798597A (en) | 1989-01-17 |
| AU610578B2 (en) | 1991-05-23 |
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Legal Events
| Date | Code | Title | Description |
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| MKLA | Lapsed |