# Patent

## Title
Devices and methods for controlling patient temperature

## Abstract

Relatively non-invasive devices and methods for heating or cooling a patient's body are disclosed. Devices and methods for treating ischemic conditions by inducing therapeutic hypothermia are disclosed. Devices and methods for inducing therapeutic hypothermia through esophageal cooling are disclosed. Devices and methods for operative temperature management are disclosed.

## Background
RELATED APPLICATIONS
This application is a continuation-in-part of co-pending U.S. application Ser. No. 13/609,624, which was filed on Sep. 11, 2012 as a continuation-in-part of U.S. application Ser. No. 13/482,581, which was filed on May 29, 2012 as a continuation-in-part of U.S. application Ser. No. 13/021,805 (now U.S. Pat. No. 8,444,684), Ser. No. 13/021,820 (now U.S. Pat. No. 8,523,929), Ser. No. 13/021,828 (now U.S. Pat. No. 8,696,725), which were filed on Feb. 7, 2011 as continuation applications of U.S. application Ser. No. 12/713,644 (now U.S. Pat. No. 8,231,664), which was filed on Feb. 26, 2010 and claimed the priority of U.S. provisional application Ser. No. 61/155,876, which was filed on Feb. 26, 2009. The disclosures of each of the aforementioned application are hereby incorporated by reference in their entireties.


FEDERALLY SPONSORED RESEARCH OR DEVELOPMENT
This invention was made with Government support under National Science Foundation (NSF) Award Number 1142664. The Government has certain rights in this invention.


MICROFICHE/COPYRIGHT REFERENCE
[Not Applicable]
BACKGROUND OF THE INVENTION
In industrial countries, 36 to 128 per 100,000 inhabitants per year experience a sudden out-of-hospital cardiac arrest (“OHCA”) with survival remaining a rare event. Cardiovascular disease affects an estimated 80,700,000 North American adults, with approximately 2400 individuals dying from cardiovascular disease daily (an average of one death every 37 seconds). Approximately 310,000 coronary heart disease deaths due to OHCA occur annually.
According to data reported by the National Registry of Cardiopulmonary Resuscitation in 2007, over 75% of patients having cardiopulmonary arrest events did not survive the event. For those who did survive the event, an additional 35.2% died afterward.
In the 1950s, moderate hypothermia (body temperature of approximately 28° C. to approximately 32° C.) and deep hypothermia (body temperature of approximately <28° C.) were utilized for various surgical procedures as well as experimentally to reverse neurological insults associated with cardiac arrest. However, because of the numerous complications of moderate-to-deep hypothermia and the difficulty in inducing these temperature reductions, enthusiasm for the use of therapeutic hypothermia waned. Consequently, the use of hypothermia to help reverse the neurologic insult after normothermic cardiac arrest lay dormant for several decades. However, beginning in the late 1980s, positive outcomes following cardiac arrest were reported in dogs with mild hypothermia.
Contemporary use of mild therapeutic hypothermia following cardiac arrest in human patients is supported by recent randomized control trials and a meta-analysis of individual patient data. Major organizations, including the International Liaison Committee on Resuscitation (“ILCOR”) and the American Heart Association (“AHA”), recommend the induction of mild therapeutic hypothermia for comatose cardiac arrest survivors. However, the AHA therapeutic hypothermia guidelines lack a concrete description of exactly how to cool patients.
Despite widespread support for mild therapeutic hypothermia in the context of cardiac arrest, including consensus recommendations from major resuscitative organizations, the use of mild therapeutic hypothermia in clinical practice remains low. Many clinicians report that therapeutic hypothermia is too technically difficult to achieve in practice.
In addition, health care professionals occasionally need to induce hypothermia during certain surgical procedures or prevent inadvertent hypothermia and the multiple adverse effects that result from uncontrolled and unintended deviations from normal body temperature.
Control of a patient's body temperature while undergoing surgical procedures in the operating room is beneficial because, for instance, even mild inadvertent hypothermia during operative procedures increases the incidence of wound infection, prolongs hospitalization, increases the incidence of morbid cardiac events and ventricular tachycardia, and impairs coagulation.
Even mild hypothermia (<1° C.) significantly increases blood loss by approximately 16% and increases the relative risk for transfusion by approximately 22%, while maintaining perioperative normothermia reduces blood loss and transfusion requirement by clinically important amounts.
Because considerable strong evidence shows that thermal management improves outcomes in a variety of surgical patients, the current American Heart Association-American College of Cardiology 2007 Guidelines on Perioperative Cardiovascular Evaluation and Care for Noncardiac Surgery include a Level 1 recommendation for maintenance of perioperative normothermia.
Moreover, recognizing the numerous complications of perioperative hypothermia, the American Society of Anesthesiologists (ASA) has recently recommended that postoperative temperature become a basis for assessing physician compliance with current guidelines on the prevention of hypothermia.
Although inadvertent operative hypothermia is considered one of the most preventable surgical complications, existing methods to control body temperature are limited in efficacy, such that the incidence of inadvertent operative hypothermia for surgical patients can exceed 50%.
Currently available methods to control body temperature include both non-invasive and invasive techniques. For example, the most commonly used techniques developed to induce therapeutic hypothermia include surface cooling and invasive cooling.
Surface cooling is relatively simple to use, and can be accomplished by the use of external vests, cooling helmets, circulating cold-water blankets, cold forced-air blankets, or with less sophisticated methods, such as ice packs and cold-water immersion, but takes between 2 and 8 hours to reduce core body temperature. Surface cooling is limited by the rate at which cooling can occur, due to the tendency of blood flow to be shunted away from skin and towards the core. External devices, such as vests or blankets, significantly limit access to important patient areas that are often needed in critical care, such as for catheter placement, and require removal or modification to perform CPR. Surface cooling techniques such as ice packs limit the precision with which a patient's temperature can be controlled. Cooling with ice packs and conventional cooling blankets often results in unintentional overcooling.
For successful induction and maintenance of induced hypothermia and maintenance of normothermia, shivering, as well as other thermoregulatory responses, must be addressed. Benefits from cooling may be offset by negative consequences from shivering. Both pharmacological and nonpharmacological methods have been used to control shivering in therapeutic hypothermia, with meperidine offering one pharmacologic choice that may provide the greatest reduction in the shivering threshold, and other effective pharmacological agents being dexmedetomidine, midazolam, fentanyl, ondansetron, and magnesium sulfate. As a last resort, neuromuscular blocking agents are considered appropriate therapy for management of refractory shivering. Skin counterwarming techniques, such as use of an air-circulating blanket, are non-pharmacological methods for reducing shivering when used in conjunction with medication. Nevertheless, treatment for shivering while avoiding the negative consequences of many anti-shivering therapies is often difficult.
As another example, several methods are utilized to warm a patient, and include raising the operating room temperature and using external warming devices, such as forced-air warming blankets.
Several issues exist with these current methods: (1) excessively warm room temperature creates an uncomfortable environment for the surgical team, (2) forced-air warmers are bulky and may impact the surgical field; they tend to be inefficient and must be used for extended periods of time in the operating room, and (3) none of these systems adequately control or manage temperature, leading to both overheating or, more often, inadequate warming.
Rasmussen et al. (Forced-air surface warming versus oesophageal heat exchanger in the prevention of perioperative hypothermia. Acta Anaesthesiol Scand. 1998 March; 42(3):348-52) mention that forced-air warming of the upper part of the body is effective in maintaining normothermia in patients undergoing abdominal surgery of at least 2 h expected duration, while central heating with an esophageal heat exchanger does not suffice to prevent hypothermia. Bräuer et al. (Oesophageal heat exchanger in the prevention of perioperative hypothermia. Acta Anaesthesiol Scand. 1998 March; 42(10):1232-33) states that an esophageal heat exchanger can only add a small amount of heat to the overall heat balance of the body.
Invasive temperature management treatments include: the infusion of cold intravenous fluids; the infusion of warmed intravenous fluids; cold carotid infusions; single carotid artery perfusion with extracorporeal cooled blood; cardiopulmonary bypass; ice water nasal lavage; cold peritoneal lavage; nasogastric and rectal lavage; and the placement of invasive intravenous catheters connected to refrigerant or heat exchange (warming) devices. Invasive temperature management treatments often require significant personnel involvement and attention to perform successfully. Moreover, certain invasive temperature management modalities have been associated with overcooling, overheating, or, more often, inadequate warming.
The use of intravenous fluid as a temperature management modality has the undesirable effect of contributing to circulating fluid volume overload, and has been found to be insufficient for maintaining target temperature. In addition, large volumes of fluids must be infused to obtain a significant effect.
Other techniques for achieving hypothermia include blood cooling through inhaled gases and the use of balloon catheters.
However, Andrews et al. (Randomized controlled trial of effects of the airflow through the upper respiratory tract of intubated brain-injured patients on brain temperature and selective brain cooling. Br. J. Anaesthesia. 2005; 94(3):330-335) mention that a flow of humidified air at room temperature through the upper respiratory tracts of intubated brain-injured patients did not produce clinically relevant or statistically significant reductions in brain temperature.
Dohi et al. (Positive selective brain cooling method: a novel, simple, and selective nasopharyngeal brain cooling method. Acta Neurochirgurgica. 2006; 96:409-412) mention that a Foley balloon catheter inserted to direct chilled air into the nasal cavity, when used in combination with head cooling by electric fans, was found to selectively reduce brain temperature.
Holt et al. (General hypothermia with intragastric cooling. Surg. Gynecol Obstet. 1958; 107(2):251-54; General hypothermia with intragastric cooling: a further study. Surg Forum. 1958; 9:287-91) mention using an intragastric balloon in combination with thermic blankets to produce hypothermia in patients undergoing surgical procedures.
Likewise, Barnard (Hypothermia: a method of intragastric cooling. Br. J. Surg. 1956; 44(185):296-98) mentions using an intragastric balloon for inducing hypothermia by intragastric cooling.
US Patent Application Publication 2004/0199229 to Lasheras mentions heating or cooling via a balloon inserted into a patient's colon.
US Patent Application Publication 2004/0210281 to Dzeng et al. (now U.S. Pat. No. 7,758,623) mentions a transesophageal balloon catheter for specifically cooling the heart and disparages technologies that cool the entire body.
US Patent Application Publication 2007/0055328 to Mayse et al. mentions a balloon catheter for protecting the digestive tract of a person undergoing cardiac ablation to correct cardiac arrhythmia.
U.S. Pat. No. 6,607,517 to Dae et al. is generally directed to using endovascular cooling to treat congestive heart failure.
Several complications are known to result from increasing pressure within the gastrointestinal tract, as may occur with a balloon inflated within the stomach, colon, or other gastrointestinal organ. For example, stomach inflation may trigger intestinal rupture, regurgitation and aspiration that may result in pneumonia, esophageal tears, colon necrosis, and gut ischemia.
In addition, several temperature-controlling modalities, particularly those that employ inflatable balloons, limit access of the health care provider to particular anatomical structures that may be crucial for patient care, such as the stomach. These modalities may require removal or modification to achieve proper treatment.
To date, no available modality for controlling patient temperature has been found that sufficiently overcomes the technical, logistical, and financial barriers that exist. The ideal patient temperature control device has yet to be developed.
In summary, the state of the art related to the control of patient temperature comprises at least one significant long felt need: methods and devices for efficient, safe, and rapid control of patient temperature while maintaining access to anatomical areas necessary for additional treatment. The present technology identifies several indications, diseases, disorders, and conditions that can be treated or prevented by controlling patient temperature and, further, provides relatively non-invasive methods and devices for rapidly and efficiently controlling patient temperature while reducing the risks posed by prior devices and methods. Moreover, certain embodiments of the present technology provide relatively non-invasive methods and devices for rapidly and efficiently controlling patient temperature, while at the same time maintaining access to important anatomical structures. Certain embodiments of the present technology also provide methods and devices for inducing and maintaining mild hypothermia or maintaining normothermia in a subject without producing thermoregulatory shivering. Certain embodiments of the present technology also provide methods and devices for maintaining a subject's core body temperature within a narrow range with little variation around the goal temperature throughout the steady-state of the treatment protocol. Certain embodiments of the present technology also provide methods and devices for efficiently re-warming a subject following induced hypothermia.
BRIEF SUMMARY OF THE INVENTION
At least one aspect of the present technology provides one or more methods for inducing systemic hypothermia. The methods comprise inserting a heat transfer device, including a fluid path defined by an inflow lumen and an outflow lumen, into a patient's esophagus; initiating flow of a cooling medium along the fluid path; and circulating the medium along the fluid path for a time sufficient to induce systemic hypothermia in the patient. The heat transfer device may comprise a heat transfer region having a splined inner surface surrounding the cooling medium flow path. The heat transfer device may include a discrete heat transfer region that is confined to the patient's esophagus. The patient may be maintained in a state of hypothermia for at least about two hours, for example. The methods may further comprise monitoring at least one physiological parameter of the patient, such as body temperature, pressure, oxygen saturation, pH, heart rate, Doppler signals, electromagnetic fluctuations, or chemical composition. For example, the methods may comprise monitoring intra-abdominal compartment pressure or monitoring esophageal pressure through a pressure transducer incorporated with the device. The methods may further comprise using a lab-on-chip to perform biochemical assays, dielectrophoresis, real-time PCR, and immunoassays for the detection of bacteria, viruses, and cancers. The methods may further comprise maintaining the patient's body temperature below about 34° C.
At least one aspect of the present technology provides one or more methods for controlling core body temperature in a subject. The methods comprise inserting a heat transfer device, including a fluid path defined by an inflow lumen and an outflow lumen, into a subject's esophagus; initiating flow of a heat transfer medium along the fluid path; and circulating the medium along the fluid path for a time sufficient to control core body temperature in a subject. The heat transfer device may comprise a heat transfer region having a splined inner surface surrounding the heat transfer medium flow path. The heat transfer device may include a discrete heat transfer region that is confined to the patient's esophagus. The core body temperature of the subject may be controlled for at least about two hours, for example. The methods may further comprise monitoring at least one physiological parameter of the subject, such as body temperature, pressure, oxygen saturation, pH, heart rate, Doppler signals, electromagnetic fluctuations, or chemical composition. For example, the methods may comprise monitoring intra-abdominal compartment pressure or monitoring esophageal pressure through a pressure transducer incorporated with the device. The methods may further comprise using a lab-on-chip to perform biochemical assays, dielectrophoresis, real-time PCR, and immunoassays for the detection of bacteria, viruses, and cancers. The methods may further comprise maintaining the patient's body temperature, for example, below about 34° C., between about 34° C. and about 37° C., or at about 37° C.
At least one aspect of the present technology provides one or more esophageal heat transfer devices. The devices comprise: a plurality of lumens configured to provide a fluid path for flow of a heat transfer medium; a proximal end including an input port and an output port; a distal end configured for insertion into a patient's esophagus. The devices may further comprise a hollow tube having a distal end configured to extend into the patient's stomach or a more distal component of the gastrointestinal tract, such as the jejunum. The hollow tube can be used to administer medications or alimentation to the gastrointestinal tract. The devices may further comprise an anti-bacterial coating.
At least one aspect of the present technology provides one or more methods for treating or preventing ischemia-reperfusion injury or injury caused by an ischemic condition. The methods comprise inserting a heat transfer device, including a fluid path defined by an inflow lumen and an outflow lumen, into a patient's esophagus; initiating flow of a cooling medium along the fluid path; and circulating the cooling medium along the fluid path for a time sufficient to induce systemic hypothermia in the patient. The heat transfer device may comprise a splined inner surface surrounding the cooling medium flow path.
At least one aspect of the present technology provides one or more methods for treating or preventing neurological or cardiac injury. The methods comprise inserting a heat transfer device, including a fluid path defined by an inflow lumen and an outflow lumen, into a patient's esophagus; initiating flow of a cooling medium along the fluid path; and circulating the cooling medium along the fluid path for a time sufficient to induce systemic hypothermia in the patient. The neurological injury may be associated with, for example, stroke (including ischemic stroke), traumatic brain injury, spinal cord injury, subarachnoid hemorrhage, out-of-hospital cardiopulmonary arrest, hepatic encephalopathy, perinatal asphyxia, hypoxic-anoxic encephalopathy, infantile viral encephalopathy, near-drowning, anoxic brain injury, traumatic head injury, traumatic cardiac arrest, newborn hypoxic-ischemic encephalopathy, hepatic encephalopathy, bacterial meningitis, cardiac failure, post-operative tachycardia, or acute respiratory distress syndrome (“ARDS”). The heat transfer device may comprise a splined inner surface surrounding the cooling medium flow path.
At least one aspect of the present technology provides one or more methods for treating myocardial infarction, stroke, traumatic brain injury, or ARDS. The methods comprise inducing mild therapeutic hypothermia in a patient. Mild therapeutic hypothermia may be induced via esophageal cooling. The patient may be maintained in a state of hypothermia for at least about two hours, for example. The methods may further comprise monitoring at least one physiological parameter of the patient, such as body temperature, pressure, oxygen saturation, pH, heart rate, Doppler signals, electromagnetic fluctuations, or chemical composition. For example, the methods may comprise monitoring intra-abdominal compartment pressure or monitoring esophageal pressure through a pressure transducer incorporated with the device. The methods may further comprise using a lab-on-chip to perform biochemical assays, dielectrophoresis, real-time PCR, and immunoassays for the detection of bacteria, viruses, and cancers. The methods may further comprise maintaining the patient's body temperature below about 34° C.
At least one aspect of the present technology provides one or more methods for treating myocardial infarction, stroke, traumatic brain injury, or ARDS. The methods comprise inserting a heat transfer device, including a fluid path defined by an inflow lumen and an outflow lumen, into a patient's esophagus; initiating flow of a cooling medium along the fluid path; and circulating the cooling medium along the fluid path for a time sufficient to induce systemic hypothermia in the patient. The heat transfer device may comprise a splined inner surface surrounding the cooling medium flow path.
At least one aspect of the present technology provides one or more methods for treating cardiac arrest. The methods comprise inducing systemic hypothermia via esophageal cooling. The methods may further comprise inserting a heat transfer device, including a fluid path defined by an inflow lumen and an outflow lumen, into a patient's esophagus; initiating flow of a cooling medium along the fluid path; and circulating the cooling medium along the fluid path for a time sufficient to induce systemic hypothermia in the patient. The heat transfer device may comprise a splined inner surface surrounding the cooling medium flow path.
At least one aspect of the present technology provides one or more methods for operative temperature management. The methods comprise controlling a patient's core body temperature via esophageal cooling. The methods may further comprise inserting a heat transfer device, including a fluid path defined by an inflow lumen and an outflow lumen, into a patient's esophagus; initiating flow of a heat transfer medium along the fluid path; and circulating the heat transfer medium along the fluid path for a time sufficient to control the patient's core body temperature. The methods may further comprise administering medications or alimentation to the gastrointestinal tract while simultaneously controlling a patient's core body temperature via esophageal cooling.
At least one aspect of the present technology provides one or more devices for cooling or warming multiple portions of a patient's body simultaneously. The devices comprise a heat transfer device including a proximal end, a distal end, at least one flexible tube extending the proximal and distal end, and additional flexible tubes extending from the proximal end. The proximal end includes a heat transfer medium input port, a heat transfer medium output port, and from about 2 to about 4 ancillary tubes extending off the proximal end providing for multiple heat transfer medium flow pathways. The distal end of the device is configured for insertion into a larger orifice of a patient, while the distal ends of the ancillary tubes are configured for insertion into additional smaller orifices or configured external as an external component for surface contact. For example, the ancillary tubes can be configured as a head and/or neck wrap to provide surface cooling.
At least one aspect of the present technology provides a heat transfer device, which may comprise (a) a plurality of lumens configured to provide a fluid path for flow of a heat transfer medium; (b) a heat transfer region configured for contacting esophageal epithelium, nasopharyngeal epithelium, auricular canal epithelium, and or the tympanic membranes of a patient; (c) a proximal end including an input port, an output port, and ancillary tubing containing heat transfer medium flow channels; and (d) a distal end configured for insertion into an esophagus of a patient. The heat transfer device can also comprise a hollow tube having a distal end configured to extend into the patient's stomach or a more distal component of the gastrointestinal tract, such as the jejunum. The hollow tube can be used to administer medications or alimentation to the gastrointestinal tract. The heat transfer device can be capable of contacting substantially all of the patient's esophageal epithelium, nasopharyngeal epithelium, auricular canal epithelium, or the tympanic membranes.
At least one aspect of the present technology provides one or more devices for cooling or warming at least one portion of a patient's body. The devices comprise a heat transfer device including a proximal end, a distal end, and at least one flexible tube extending between the proximal and distal end. The proximal end includes a heat transfer medium input port and a heat transfer medium output port. The distal end is configured for insertion into an orifice of a patient. The flexible tube defines an inflow lumen and an outflow lumen and the lumens may be configured to provide a fluid path for flow of a heat transfer medium. The heat transfer medium is delivered to a heat transfer region of the heat transfer device via the inflow lumen and removed from the heat transfer region via the outflow lumen. The inflow and outflow lumens may comprise a part or all of the heat transfer region. A single flexible tube may define both the inflow lumen and the outflow lumen. For example, the flexible tube may take on a U-shaped configuration or a substantially helical configuration such that one portion of the tube defines the inflow lumen and another portion of the flexible tube defines the outflow lumen. Alternatively, the same portion of the flexible tube may define the inflow and outflow lumens. For example, heat transfer medium may be delivered to the heat transfer region and extracted from the heat transfer region via the same portion of the flexible tube. In one embodiment, an external pump may alternatively deliver and withdraw heat transfer medium via a single flexible tube. In yet another embodiment of the present technology, more than one flexible tube may define the inflow and outflow lumens. For example, two or more tubes may be arranged concentrically such that the lumen of the outer tube serves as the inflow lumen and the lumen of the inner tube serves as the outflow lumen. Alternatively, two or more tubes may be arranged in parallel, with at least one tube defining an inflow lumen and at least one tube defining an outflow lumen. The lumens of the parallel tubes may be connected such that the heat transfer medium can pass from the inflow lumen to the outflow lumen. The flexible tube may comprise a splined inner surface surrounding the heat transfer medium flow path. The devices further comprise a supply line connected to the input port and a return line connected to the output port.
The device may be used to treat or prevent, for example, injury caused by an ischemic condition; ischemia-reperfusion injury; neurological injury; cardiac injury. The device may be used to treat patients who have experienced or are experiencing myocardial infarction; stroke; traumatic brain injury; or ARDS. The methods of treating or preventing such conditions or diseases comprise inserting the distal end of the heat transfer device nasally or orally; advancing the distal end into the patient's esophagus; initiating flow of a cooling medium along the fluid path; and circulating the cooling medium along the fluid path for a time sufficient to induce systemic hypothermia in the patient. The patient may be maintained in a state of hypothermia for at least two hours. The methods may further comprise monitoring at least one physiological parameter of the patient, such as body temperature, pressure, oxygen saturation, pH, heart rate, Doppler signals, electromagnetic fluctuations, or chemical composition. For example, the methods may comprise monitoring intra-abdominal compartment pressure or monitoring esophageal pressure through a pressure transducer incorporated with the device. The methods may further comprise using a lab-on-chip to perform biochemical assays, dielectrophoresis, real-time PCR, and immunoassays for the detection of bacteria, viruses, and cancers. The methods may further comprise maintaining the patient's body temperature below about 34° C.
The device may be used to control a patient's core body temperature during, for example, surgical procedures. The methods of controlling the patient's core body temperature comprise inserting the distal end of the heat transfer device nasally or orally; advancing the distal end into the patient's esophagus; initiating flow of a heat transfer medium along the fluid path; and circulating the heat transfer medium along the fluid path for a time sufficient to control core body temperature in the patient. The core body temperature of the subject may be controlled for at least about two hours, for example. The methods may further comprise monitoring at least one physiological parameter of the subject, such as body temperature, pressure, oxygen saturation, pH, heart rate, Doppler signals, electromagnetic fluctuations, or chemical composition. For example, the methods may comprise monitoring intra-abdominal compartment pressure or monitoring esophageal pressure through a pressure transducer incorporated with the device. The methods may further comprise using a lab-on-chip to perform biochemical assays, dielectrophoresis, real-time PCR, and immunoassays for the detection of bacteria, viruses, and cancers. The methods may further comprise maintaining the patient's body temperature, for example, below about 34° C., between about 34° C. and about 37° C., or at about 37° C.
At least one aspect of the present technology provides one or more methods for inducing systemic hypothermia while simultaneously imparting local normothermia, for example to the region of the esophagus in closest proximity to the atrium of the heart.
At least one aspect of the present technology provides an esophageal heat transfer device comprising (a) a plurality of lumens configured to provide a fluid path for flow of a heat transfer medium; (b) a heat transfer region configured for contacting esophageal epithelium of a patient; (c) a proximal end including an input port and an output port; and (d) a distal end configured for insertion into an esophagus of a patient. The heat transfer device can also comprise a hollow tube having a distal end configured to extend into the patient's stomach or a more distal component of the gastrointestinal tract, such as the jejunum. The hollow tube can be used to administer medications or alimentation to the gastrointestinal tract. The heat transfer device can be capable of contacting substantially all of the patient's esophageal epithelium. The heat transfer device can comprise a semi-rigid material. The heat transfer device can be capable of cooling at a rate of about 1.2° C./hr to about 2.4° C./hr. Alternatively, the heat transfer device can be capable of cooling at a rate of about 1.2° C./hr to about 1.8° C./hr. The heat transfer device can be capable of cooling a mass at a rate of up to about 700 kJ/hr, and, in particular, at a rate of about 410 kJ/hr. Alternatively, the heat transfer device can be capable of cooling a mass at a rate of about 350 kJ/hr to about 530 kJ/hr, and, in particular, at a rate of about 430 kJ/hr. The heat transfer device can include a heat transfer region with a surface area of at least about 100 cm2 and, in particular, a surface area of about 140 cm2.
At least one aspect of the present technology provides a system for cooling or warming at least one portion of a patient's body, comprising a heat transfer device including a proximal end, a distal end, and at least one semi-rigid tube extending between the proximal and distal ends; a supply line; and a return line. The proximal end of the heat transfer device includes a heat transfer medium input port and a heat transfer medium output port. The distal end of the heat transfer device is configured for insertion into an orifice of a patient, such as the esophageal lumen. The semi-rigid tube defines an inflow lumen and an outflow lumen and the lumens are configured to provide a fluid path for flow of a heat transfer medium. The supply line is connected to the input port and the return line is connected to the output port. The heat transfer device can also comprise a hollow tube having a distal end configured to extend into the patient's stomach or a more distal component of the gastrointestinal tract, such as the jejunum. The hollow tube can be used to administer medications or alimentation to the gastrointestinal tract. The heat transfer device can be capable of contacting substantially all of the patient's esophageal epithelium. The heat transfer device can comprise a semi-rigid material. The heat transfer device can be capable of cooling at a rate of about 1.2° C./hr to about 2.4° C./hr. Alternatively, the heat transfer device can be capable of cooling at a rate of about 1.2° C./hr to about 1.8° C./hr. The heat transfer device can be capable of cooling a mass at a rate of up to about 700 kJ/hr, and, in particular, at a rate of about 410 kJ/hr. Alternatively, the heat transfer device can be capable of cooling a mass at a rate of about 350 kJ/hr to about 530 kJ/hr, and, in particular, at a rate of about 430 kJ/hr. The heat transfer device can include a heat transfer region with a surface area of at least about 100 cm2 and, in particular, a surface area of about 140 cm2.
At least one aspect of the present technology provides a system for controlling core body temperature of a subject, comprising a heat transfer tube insertable within the esophagus of the subject; an external heat exchanger containing a heat transfer fluid; a pump for flowing the heat transfer fluid through a circuit within the heat transfer tube; a heat transfer element in contact with the external heat exchanger; a sensor for detecting a parameter and generating a signal representative of the parameter, wherein the signal is transmitted to a microprocessor to control (i) the flow of heat transfer fluid within the circuit or (ii) the temperature of the heat transfer fluid. The tube is configured to contact the epithelial lining of the subject's esophagus. The sensor can be a temperature sensor positioned distal to the heat transfer tube and configured to generate a signal representing the core body temperature of the subject. The microprocessor can receive a target temperature input and responds to the signal from the temperature sensor with a proportional integrated differential response to control the rate at which the subject approaches the target temperature. The sensor can be a bubble detector and configured to generate a signal representing the presence of air in the circuit. The heat transfer device can also comprise a hollow tube having a distal end configured to extend into the patient's stomach or a more distal component of the gastrointestinal tract, such as the jejunum. The hollow tube can be used to administer medications or alimentation to the gastrointestinal tract. The heat transfer device can be capable of contacting substantially all of the patient's esophageal epithelium. The heat transfer device can comprise a semi-rigid material. The heat transfer device can be capable of cooling at a rate of about 1.2° C./hr to about 2.4° C./hr. Alternatively, the heat transfer device can be capable of cooling at a rate of about 1.2° C./hr to about 1.8° C./hr. The heat transfer device can be capable of cooling a mass at a rate of up to about 700 kJ/hr, and, in particular, at a rate of about 410 kJ/hr. Alternatively, the heat transfer device can be capable of cooling a mass at a rate of about 350 kJ/hr to about 530 kJ/hr, and, in particular, at a rate of about 430 kJ/hr. The heat transfer device can include a heat transfer region with a surface area of at least about 100 cm2 and, in particular, a surface area of about 140 cm2.
At least one aspect of the present technology provides a system for controlling core body temperature of a subject. The system comprises a heat transfer device having an inflatable heat transfer region, which is insertable within the esophagus the subject and, upon inflation, at least partially restricts gastric ventilation. The system also comprises an external heat exchanger containing a heat transfer fluid; a pump for flowing the heat transfer fluid through a circuit within the heat transfer device; and a heat transfer element in contact with the external heat exchanger. The system also comprises a sensor for detecting a parameter and generating a signal representative of the parameter, wherein the signal is transmitted to a microprocessor to control (i) the flow of heat transfer fluid within the circuit or (ii) the inflation pressure of the inflatable heat transfer region. The inflatable heat transfer region is configured to contact the epithelial lining of the subject's esophagus upon inflation. The inflatable heat transfer region can be capable of contacting substantially all of the patient's esophageal epithelium upon inflation. The sensor can be a pressure sensor positioned, for example, distal to the inflatable heat transfer region and configured to generate a signal representing the intra-abdominal, gastric or esophageal pressure of the subject. The microprocessor can receive a maximum pressure determined by a health care professional and respond to the signal from the pressure sensor with a proportional integrated differential response to control (i) the flow of heat transfer fluid within the circuit or (ii) the inflation pressure of the inflatable heat transfer region. The response generated by the microprocessor is designed to alleviate the pressure built up in the gastrointestinal tract. For example, reducing the flow of heat transfer fluid within the circuit will cause the inflatable heat transfer region to partially or fully deflate, thereby allowing for gastric ventilation. Alternatively, the microprocessor may directly control the inflation pressure of the inflatable heat transfer region. Following gastric ventilation, the microprocessor, for example, generates and sends a signal to increase pump output or otherwise re-inflate the inflatable heat transfer region, thereby at least partially restricting gastric ventilation.
At least one aspect of the present technology provides systems and methods for preventing the negative effects of elevations in gastric pressure associated with an esophageal heat transfer device having an inflatable heat transfer region that, upon inflation, at least partially restricts gastric ventilation. For example, a microprocessor may periodically deflate the inflatable heat transfer region by altering the flow of a heat transfer fluid to the inflatable heat transfer region of the device. Periodic deflation of the inflatable heat transfer region would allow for gastric ventilation. As another example, a pressure sensor for detecting intra-abdominal, gastric or esophageal pressure is incorporated with an esophageal heat transfer device having an inflatable heat transfer region that, upon inflation, at least partially restricts gastric ventilation. Information representing intra-abdominal, gastric or esophageal pressure can be communicated to a microprocessor capable of inflating or deflating the inflatable heat transfer region. The microprocessor may control inflation or deflation of the inflatable heat transfer region by, for example, altering the flow of a heat transfer fluid to the inflatable heat transfer region of the device. The pressure sensor may be located distal to the inflatable heat transfer region.
At least one aspect of the present technology provides an esophageal heat transfer device comprising: one or more lumens providing a fluid path for flow of a heat transfer medium; a distal end configured for insertion into a pharyngeal opening; a heat transfer region, wherein the heat transfer region is capable of directly contacting esophageal epithelium upon insertion into a patient; a heat transfer medium input port positioned proximal to the heat transfer region; a heat transfer medium output port positioned proximal to the heat transfer region; and a gastric tube.
In certain embodiments, the one or more lumens provide a fluid path for flow of heat transfer medium. The one or more lumens may comprise an inflow lumen and an outflow lumen. The gastric tube may be arranged in parallel to the inflow lumen or the outflow lumen. Alternatively, the gastric tube may be positioned within the inflow lumen or the outflow lumen.
In other embodiments, a single lumen provides the fluid path for flow of the heat transfer medium. The gastric tube may be arranged in parallel to the single lumen. Alternatively, the gastric tube may be positioned within the single lumen.
The heat transfer region, or a portion thereof, may be substantially helical. The substantially helical configuration creates an interior space defined by the helix, which may comprise a gastric access lumen. In certain embodiments, the gastric tube can be positioned within the gastric access lumen.
At least one aspect of the present technology provides an esophageal heat transfer device comprising: an inflow lumen connected to a heat transfer medium input port; a heat transfer region, wherein the heat transfer region is capable of directly contacting esophageal epithelium upon insertion into a patient; an outflow lumen connected to a heat transfer medium output port; a distal end configured for insertion into a nostril or mouth of a patient; and wherein the device is capable of receiving a separate gastric tube or gastric probe.
In certain embodiments, the device also comprises a gastric access tube capable of receiving the separate gastric tube or gastric probe. The gastric access tube may be arranged in parallel to the inflow lumen or the outflow lumen. Alternatively, the gastric access tube may be positioned within the inflow lumen or the outflow lumen.
In yet other embodiments, the heat transfer region, or a portion thereof, of the heat transfer device may be substantially helical. The substantially helical configuration creates an interior space defined by the helix, which may comprise a gastric access lumen. The gastric tube can be positioned within the gastric access lumen.
At least one aspect of the present technology provides an esophageal heat transfer device comprising: a distal end configured for insertion into a nostril or mouth of a patient; a heat transfer region, wherein the heat transfer region is capable of directly contacting esophageal epithelium upon insertion into the patient; and a gastric tube. The device is capable of receiving a heat transfer medium, such as a gas, liquid, solid, slurry, or gel.
The heat transfer region, or a portion thereof, may be substantially helical. The substantially helical configuration creates an interior space defined by the helix, which may comprise a gastric access lumen. In certain embodiments, the gastric tube can be positioned within the gastric access lumen.
In certain embodiments, the present technology includes a system for controlling core body temperature. The system comprises a heat transfer device having an input port capable of receiving a heat transfer medium from an external source and a lumen that is connected to the input port and provides a fluid path for flow of the heat transfer medium to an inflatable heat transfer region. Upon inflation, the inflatable heat transfer region may be capable of contacting the patient's esophageal epithelium. The system also comprises a microprocessor coupled to the external source. The microprocessor is capable of regulating the flow of the heat transfer medium to the heat transfer region. The microprocessor may also be capable of receiving a target pressure determined by a health care professional. The microprocessor may be capable of periodically increasing or decreasing the flow of the heat transfer medium to the heat transfer region. The system may also comprise a pressure sensor for detecting gastric pressure and generating a signal representative of gastric pressure. The pressure sensor may be capable of sending the signal to the microprocessor. The microprocessor may be capable of increasing or decreasing the flow of the heat transfer medium to the heat transfer region in response to the signal received from the pressure sensor. The microprocessor may be capable of responding to the signal from the pressure sensor with a proportional integrated differential response to control the flow of the heat transfer medium to the heat transfer region.
In certain embodiments, the present technology includes a method for controlling core body temperature. The method may comprise increasing, decreasing, or maintaining core body temperature. In certain embodiments the method comprises the steps of: nasally or orally inserting an esophageal heat transfer device into the patient. The heat transfer device includes an input port capable of receiving a heat transfer medium from an external source. The heat transfer device also includes an inflatable heat transfer region configured for contacting a patient's esophageal epithelium upon inflation. The heat transfer device also includes at least one lumen connected to the input port, which provides a fluid path for flow of the heat transfer medium from the input port to the inflatable heat transfer region. The method also comprises advancing the inflatable heat transfer region of the heat transfer device into the patient's esophagus. The method also comprises initiating flow of a heat transfer medium along the fluid path to inflate the inflatable heat transfer region; subsequently deflating the inflatable heat transfer region to permit gastric ventilation; and then re-inflating the inflatable heat transfer region. The method may also comprise the step of monitoring gastric pressure. Information representing gastric pressure may be communicated to a microprocessor capable of inflating or deflating the inflatable heat transfer region. The microprocessor may be capable of receiving a target pressure determined by a health care professional. The microprocessor may be capable of responding to the signal from the pressure sensor with a proportional integrated differential response to control the flow of the heat transfer medium to the heat transfer region. The method may also comprise the steps of maintaining the core body temperature of the patient at about 36° C. for at least two hours, for at least twenty four hours, or for at least seventy two hours. The method may also comprise the steps of maintaining the core body temperature of the patient below about 34° C. for at least two hours, for at least twenty four hours, or for at least seventy two hours. The method may also comprise the steps of maintaining the core body temperature of the patient at about 33° C. for at least two hours, for at least twenty four hours, or for at least seventy two hours.
In certain embodiments, the present technology includes a method for controlling core body temperature. The method may comprise increasing, decreasing, or maintaining core body temperature. In certain embodiments the method comprises the steps of: nasally or orally inserting an esophageal heat transfer device into the patient. The heat transfer device includes an inflatable heat transfer region configured for contacting a patient's esophageal epithelium upon inflation. The heat transfer device also includes at least one lumen, which provides a fluid path for flow of the heat transfer medium to the inflatable heat transfer region. The method also comprises advancing the inflatable heat transfer region of the heat transfer device into the patient's esophagus. The method also comprises initiating flow of a heat transfer medium along the fluid path to inflate the inflatable heat transfer region. Following inflation of the inflatable heat transfer region, gastric access is maintained. The method may also comprise nasally or orally inserting a gastric tube into the patient while the inflatable heat transfer region is in its inflated state. The inflatable heat transfer region may take on a substantially helical shape or a substantially hourglass shape upon inflation.



BRIEF DESCRIPTION OF SEVERAL VIEWS OF THE DRAWINGS
FIG. 1 is a schematic view of a heat transfer system according to an exemplary embodiment of the present technology.
FIG. 2 depicts a heat transfer device according to an exemplary embodiment of the present technology.
FIG. 3 shows a schematic (FIG. 3A), top down (FIG. 3B), and cross-sectional (FIG. 3C) view of a heat transfer device according to an exemplary embodiment of the present technology.
FIG. 4 shows a schematic view of a proximal end of a heat transfer device according to an exemplary embodiment of the present technology.
FIG. 5 shows a schematic view (FIG. 5A) and several cross-sectional views, and corresponding schematic views, (FIGS. 5B-5Q) of a distal end of a heat transfer device according to an exemplary embodiment of the present technology.
FIG. 6 shows a longitudinal view (FIG. 6A) and a cross-sectional view (FIG. 6B) of a heat transfer device according to an exemplary embodiment of the present technology.
FIG. 7 is a schematic diagram of a distal end of a heat transfer device according to an exemplary embodiment of the present technology.
FIG. 8 shows schematic views (FIGS. 8A and 8B) and cross-sectional views (FIGS. 8C and 8D) of a heat transfer device according to an exemplary embodiment of the present technology.
FIG. 9A is a perspective view of a portion of an exemplary heat transfer device. FIG. 9B is a longitudinal front side view of a portion of an exemplary heat transfer device. FIG. 9C is a bottom side view of a portion of an exemplary heat transfer device. FIG. 9D is a horizontal front side view of a portion of an exemplary heat transfer device.
FIG. 10 is a graph depicting the cooling achieved with an exemplary cooling device according to an embodiment of the present technology.
FIG. 11 is a graphed comparison of the rate of cooling achieved by a heat transfer device of the present technology as compared to the rate of cooling demonstrated in US Patent Application Publication 2004/0210281 to Dzeng et al.
FIG. 12 is a graph showing the total amount of heat transferred during the warming and maintenance phase of the experiment.
FIG. 13 is a temperature plot depicting temperature modulation achieved with an exemplary cooling device according to an embodiment of the present technology.



DETAILED DESCRIPTION OF THE INVENTION
The present technology provides relatively non-invasive devices and methods for heating or cooling a patient's entire body. The present technology also provides devices and methods for treating ischemic conditions by inducing therapeutic hypothermia. Another aspect of the present technology provides devices and methods for inducing therapeutic hypothermia through esophageal cooling. The present application demonstrates that heat transfer devices and methods of the present technology achieve unexpectedly-greater rates of temperature change as compared to other devices and methods and, in particular, those mentioned in US Patent Application Publication 2004/0210281 to Dzeng et al. (now U.S. Pat. No. 7,758,623).
The present technology provides devices and methods for treating patients suffering from various diseases and disorders by inducing mild therapeutic hypothermia (target temperature: about 32° C. to about 34° C.) and maintaining normothermia (target temperature: about 37° C.). In particular, mild therapeutic hypothermia may be induced to treat patients suffering from ischemia or conditions related to ischemia. Without being bound by any particular theory, it is believed that several molecular and physiological responses associated with the ischemia-reperfusion cascade, including, for example, glutamate release, stabilization of the blood-brain barrier, oxygen radical production, intracellular signal conduction, protein synthesis, ischemic depolarization, reduced cerebral metabolism, membrane stabilization, inflammation, activation of protein kinases, cytoskeletal breakdown, and early gene expression, are sensitive to intra- and post-ischemic temperature reductions. In particular, mild therapeutic hypothermia may minimize the formation of several metabolic mediators such as free radicals and suppress the inflammatory response associated with ischemia-reperfusion. Moreover, with respect to neurological outcomes, mild therapeutic hypothermia may blunt the cerebral pro-inflammatory response, decrease the production of excitatory mediators of brain injury, such as excitatory amino acids and monoamines, decrease the cerebral metabolic rate, and decrease intracranial pressure. On the other hand, inadvertent hypothermia during operative procedures can reduce platelet function, impair enzymes of the coagulation cascade, enhance anesthetic drug effects, contribute to coagulopathy, increase cardiac demand, and increase the incidence of surgical wound infections.
Certain embodiments of the present technology provide devices and methods for inducing mild therapeutic hypothermia to treat individuals who have experienced myocardial infarction, stroke, traumatic brain injury, ARDS, hemorrhagic shock, subarachnoid hemorrhage (“SAH”), including non-traumatic aneurysmal SAH, neonatal encephalopathy, perinatal asphyxia (hypoxic ischemic encephalopathy), spinal cord injury, meningitis, near hanging and near drowning. Without being bound by any particular theory, it is believed that mild therapeutic hypothermia may prevent, reduce, or ameliorate neurological, or other, damage associated with the above-mentioned conditions. Additional embodiments of the present technology provide devices and methods for inducing mild therapeutic hypothermia to treat individuals who have experienced metabolic acidosis, pancreatitis, malignant hyperthermia, liver failure and hepatic encephalopathy. Additional embodiments of the present technology provide devices and methods for controlling patient temperature during any general surgical procedure. As used herein, the term “controlling patient temperature” refers to a patient's core body temperature and includes lowering core body temperature, maintaining core body temperature, raising core body temperature, inducing hypothermia, maintaining normothermia, and inducing hyperthermia.
Certain embodiments of the present technology provide devices and methods for improving cardiac output, particularly during cardiopulmonary resuscitation (CPR). Without wishing to be bound by any particular theory, it is believed that certain esophageal heat transfer devices of the present technology add support to the medial aspect of the heart, which helps reinforce the compression of the heart during the down stroke of CPR. Placement of such a device during CPR increases cardiac output and blood flow to the brain during a crucial time, which would likely confer a survival benefit.
Certain embodiments of the present technology provide for controlling patient temperature through esophageal warming or cooling. As an example, a heat transfer agent may be circulated through a heat transfer device positioned in the patient's esophagus. In certain embodiments, the heat transfer portion of the device is confined to the patient's esophagus. In certain embodiments, the heat transfer device is in contact with substantially all of the epithelial surface of the patient's esophagus. The heat transfer device may include a balloon or partially inflatable lumen. For example, the heat transfer region of the heat transfer device may include an inflatable or partially inflatable lumen. Prior to insertion of the device into a patient, the inflatable or partially inflatable lumen may be in the deflated state. Upon insertion of the device into a patient, the inflatable or partially inflatable lumen may be inflated. As described herein, the inflatable or partially inflatable lumen may comprise an inflow and an outflow lumen, thereby providing a fluid path for the flow of a heat transfer medium.
In certain embodiments, the heat transfer device may include a balloon or partially inflatable lumen and permit gastric access. In certain embodiments, the heat transfer device further comprises a tube allowing for gastric access and, for example, gastric suctioning. In one embodiment, the inflatable or partially inflatable lumen, which comprises the heat transfer region, is arranged concentrically with the gastric access tube. For example, the inflatable or partially inflatable lumen may partially or fully surround the gastric access tube. In another embodiment, the inflatable or partially inflatable lumen, which comprises the heat transfer region, is arranged in parallel with the gastric access tube. For example, the inflatable or partially inflatable lumen may run alongside the gastric access tube. In yet another embodiment, the inflatable or partially inflatable lumen, which comprises the heat transfer region, is helically wrapped around the gastric access tube. Thus, the heat transfer region, or a portion thereof, may be substantially helical. The substantially helical configuration creates an interior space defined by the helix, within which the gastric access tube may be located. In certain other embodiments, the heat transfer device comprises a balloon or partially inflatable lumen that is capable of inflating so as to permit gastric access even when in the inflated state. For example, an inflatable or partially inflatable lumen may be manufactured such that, upon inflation, the esophagus is not completely occluded. The inflatable or partially inflatable lumen may take on an hourglass or barbell shape upon inflation. Alternatively, the inflatable or partially inflatable lumen may take on a helical shape upon inflation, such that gastric access is permitted along the axis of the helix.
As another example, inflation of the inflatable or partially inflatable lumen may be guided by a strut, boss, ring, or net to restrict the orientation of the lumen upon inflation, thereby permitting gastric access even when the lumen is in the inflated state. The strut, boss, ring, net, or other structure for restricting the orientation of the lumen upon inflation may be affixed to, for example, the outer surface of a tube defining an inflow lumen. In operation, a heat transfer medium would flow through the inflow lumen into the inflatable or partially inflatable lumen, thereby causing the inflatable or partially inflatable lumen to inflate. The structure for restricting the orientation of the lumen upon inflation prevents the inflatable or partially inflatable lumen from completely occluding the esophagus. In certain embodiments, the inflow lumen and the inflatable or partially inflatable lumen are coextensive.
Alternatively, in certain embodiments of the present invention, the heat transfer portion of the heat transfer device does not include a balloon or partially inflatable lumen.
In operation, heat can be transferred to the esophagus from the heat transfer agent, resulting in an increase in the temperature of the esophagus, as well as adjacent organs or structures, including the aorta, right atrium, vena cavae, and azygos veins, and ultimately, systemic normothermia, or heat can be transferred from the esophagus to the heat transfer agent, resulting in a decrease in the temperature of the esophagus, as well as adjacent organs or structures, including the aorta, right atrium, vena cavae, and azygos veins, and ultimately, systemic hypothermia.
Certain other embodiments of the present technology provide for controlling patient temperature through esophago-gastric heat transfer. As an example, a heat exchange medium may be circulated through a heat transfer device of sufficient length such the heat transfer portion of the device extends from the patient's esophagus to the patient's stomach. In certain embodiments, the heat transfer device is in contact with substantially all of the epithelial surface of the patient's esophagus. The heat transfer device may include a balloon or partially inflatable lumen. Alternatively, in certain embodiments of the present invention, the heat transfer portion of the device does not include a balloon or partially inflatable lumen. Employing such an esophago-gastric temperature control device to modulate patient temperature provides increased surface area for heat transfer and thereby results in more efficient and more rapid temperature management.
At least one aspect of the present technology provides one or more methods for therapeutic temperature modulation in a subject. Therapeutic temperature modulation encompasses, for example, both mild hypothermia and the maintenance of normothermia. In certain embodiments, the methods for therapeutic temperature modulation comprise controlling core body temperature in a subject. The methods comprise inserting a heat transfer device, which includes a heat transfer region comprising a fluid path defined by an inflow lumen and an outflow lumen, into a subject; initiating flow of a heat transfer medium along the fluid path; and circulating the medium along the fluid path for a time sufficient to control core body temperature in a subject. In certain embodiments, the heat transfer region of the heat transfer device can be inserted into a subject's esophagus. In certain embodiments, the present application provides methods for therapeutic temperature modulation that do not require concomitant administration of muscular paralysis medications or other medications commonly utilized to treat shivering (such as meperidine, dexmedetomidine, midazolam, fentanyl, ondansetron, or magnesium sulfate).
At least one aspect of the present technology provides one or more esophageal heat transfer devices. The devices comprise: a heat transfer region configured for placement in a subject's esophagus. The heat transfer region comprises a plurality of lumens configured to provide a fluid path for flow of a heat transfer medium. In certain embodiments, the heat transfer region of the heat transfer devices can be capable of contacting substantially all of the patient's esophageal epithelium. The devices may further comprise a gastrointestinal access tube providing access to a more distal component of the gastrointestinal tract, such as the stomach or jejunum. The gastrointestinal access tube can be used to, for example, remove the contents of the subject's stomach. In certain embodiments, esophageal heat transfer devices of the present technology are capable of being used to provide therapeutic temperature modulation in a subject without producing thermoregulatory shivering. Without wishing to be bound by any particular theory, the benefits of such devices may be related to the ability to focus heat transfer at the core of a patient away from more sensitive skin receptors thought to be active in generation of the shivering reflex; the increased contact surface between the heat transfer region of the heat transfer device and the patient's anatomy; the superior heat transfer characteristics of the materials used to construct the heat transfer devices of the present technology; and/or the reduction of gastric pressure through gastric ventilation.
In certain embodiments, esophageal heat transfer devices of the present technology are capable of maintaining a subject's core body temperature within a narrow range with little variation around the goal temperature throughout the steady-state of the treatment protocol. In some embodiments, the range is about ±1° C. of goal temperature. In other embodiments, the range is about ±0.5° C. of goal temperature. In still other embodiments, the range is about ±0.1° C. of goal temperature. Without wishing to be bound by any particular theory, such tight control of a subject's core body temperature during the steady-state of the treatment protocol may be related to a focus of heat transfer at the core of a patient where a rich and abundant vascular flow provides an optimal environment to control a patient's temperature rapidly and efficiently; the increased contact surface between the heat transfer region of the heat transfer device and the patient's anatomy; the superior heat transfer characteristics of the materials used to construct the heat transfer devices of the present technology; and/or the reduction of gastric pressure through gastric ventilation.
Certain embodiments of the present technology provide for inducing mild therapeutic hypothermia by, for example, esophageal cooling, to treat individuals who have experienced cardiac arrest, including cocaine-induced cardiac arrest, traumatic cardiac arrest, and cardiac arrest due to non-coronary causes.
Still other embodiments of the present technology provide for controlling patient temperature through cooling or warming of a patient's nasopharynx, tympanic membrane, auricular canal, bladder, colon, rectum, or other anatomical structure. As an example, a heat exchange medium may be circulated through a heat transfer device positioned in the patient's bladder, colon, rectum, or other anatomical structure.
Certain embodiments of the present technology provides for a heat transfer system for heating or cooling a patient. The heat transfer system may include a heat transfer device, a heat exchanger, a heat transfer medium, and a network of tubular structures for circulating the heat transfer medium between the heat transfer device and the heat exchanger. In other embodiments, the heat transfer system includes a heat transfer device, a chiller, a coolant and a network of tubular structures for circulating the coolant between the heat transfer device and the chiller. In still other embodiments, the heat transfer system can be used to cool and subsequently re-warm the patient, as well as maintain the patient at a predetermined maintenance temperature.
In certain embodiments of the present technology, the heat transfer device comprises a distal end, a proximal end, and one or more lengths of tubing extending therebetween. The proximal end of the heat transfer device includes an input port for receiving a heat transfer medium from the heat exchanger and an output port allowing the heat transfer medium to return to the heat exchanger. The tubing extending from approximately the proximal end of the heat transfer device to approximately the distal end of the heat transfer device may include a heat transfer medium supply tube and a heat transfer medium return tube. The heat transfer medium supply tube and heat transfer medium return tube may be arranged, for example, in parallel or concentrically. In one non-limiting example, the heat transfer medium return tube is positioned within a lumen defined by the heat transfer medium supply tube. In another non-limiting example, the heat transfer medium supply tube is positioned within a lumen defined by the heat transfer medium return tube. The lumens of the heat transfer medium supply tube and heat transfer medium return tube may be in fluid communication such that the heat transfer medium may flow along a fluid path defined by the lumens of the heat transfer medium supply tube and heat transfer medium return tube. In certain embodiments, the flow rate of the heat transfer medium along the fluid path can be sufficient to prevent significant fluctuations in the temperature of the heat transfer medium as it flows along the fluid path. For example, the flow rate of the heat transfer medium can be from about 50 mL/min to about 1000 mL/min, preferably about 750 mL/min. As another example, the flow rate of the heat transfer medium can be sufficient to maintain the temperature of the heat transfer medium within about ±3° C., within about ±2° C., within about ±1° C., or within about ±0.5° C. between inlet and outlet temperature. In some embodiments, the flow rate of the heat transfer medium can be sufficient to maintain the temperature of the heat transfer medium within about ±0.1° C. between inlet and outlet temperature.
The thickness of the walls of the heat transfer medium supply tube and/or heat transfer medium return tube contributes to the heat transfer resistance of the device. Thus, in certain embodiments, it is preferable for the heat transfer medium supply tube and/or heat transfer medium return tube to have thin walls. For example, the wall of the heat transfer medium supply tube and/or heat transfer medium return tube may be less than about 1 millimeter. Alternatively, the wall of the heat transfer medium supply tube and/or heat transfer medium return tube may be less than about 0.01 millimeter. In some embodiments, the wall of the heat transfer medium supply tube and/or heat transfer medium return tube may be less than about 0.008 millimeters. As will be appreciated by one of skill in the art, the thickness of the walls of the heat transfer medium supply tube and/or heat transfer medium return tube may be modified in increments of about 0.001 millimeters, about 0.01 millimeters, or about 0.1 millimeters, for example.
In certain embodiments, heat transfer devices of the present technology include heat transfer regions that, for example, employ splined inner surfaces surrounding the heat exchange medium flow paths. The splined inner surfaces help to enhance the likelihood of maintenance of laminar flow, and reduce the likelihood of flow obstruction at the point of curvature of the oropharynx. Heat transfer devices comprising splined inner surfaces surrounding the heat exchange medium flow paths provide an unexpectedly superior rate of temperature change relative to other devices and methods. While not wishing to be bound by any particular theory, it is thought that heat transfer devices comprising splined inner surfaces surrounding the heat exchange medium flow paths transfer more heat per unit time than other devices.
In certain embodiments, heat transfer devices of the present technology include a heat transfer region having a substantially helical configuration. For example, the heat transfer region may comprise a helical tube. The tube may comprise any material described herein, including, for example, a semi-rigid plastic, such as ethylene tetrafluoroethylene (ETFE), polytetrafluoroethylene (PTFE), perfluoroalkoxy (PFA), and fluorinated ethylene propylene (FEP), a semi-rigid elastomer, such as silicone, or an inflatable or partially inflatable material, such as a balloon. The tube defines a lumen, which, in some embodiments, provides a fluid path for the flow of a liquid or gaseous heat transfer medium. For example, the tube and corresponding lumen may serve as the evaporative component of a freon/gas circuit and be connected with an external condenser. In an alternative embodiment, the tube defines a lumen, which is capable of receiving a solid or semi-solid heat transfer medium.
A helical arrangement of the heat transfer region, or a portion thereof, allows for access to anatomical sites beyond the placement of the heat transfer device. The substantially helical configuration of the tube creates an interior space defined by the helix, which may comprise, for example, an access lumen. In some embodiments, the helical heat transfer region, or portion thereof, defines an access lumen. For example, where the heat transfer device is for placement within the esophagus, the helical heat transfer region, or portion thereof, allows for gastric access via a gastric access lumen. A separate probe, such as a temperature probe, or separate tube, such as a nasogastric tube or an orogastric tube, can be inserted into the patient via the gastric access lumen. The nasogastric tube, orogastric tube, or probe may be provided with the heat transfer device or provided as an after-market component.
The manufacture of heat transfer devices of the present technology is relatively inexpensive. For example, an esophageal heat transfer device can be constructed using an elastomer such as biomedical grade extruded silicone rubber, and an adhesive. Commercially available elastomers and adhesives include, for example, Dow Corning Q7 4765 silicone and Nusil Med2-4213. The low cost and ease of use of such materials is expected to lead to widespread adoption of the esophageal heat transfer devices of the present technology.
In certain embodiments, the heat transfer device, including, for example, the supply tube, may comprise a semi-rigid material, such as a semi-rigid plastic, including ethylene tetrafluoroethylene (ETFE), polytetrafluoroethylene (PTFE), perfluoroalkoxy (PFA), and fluorinated ethylene propylene (FEP), or a semi-rigid elastomer, such as silicone. A heat transfer device comprising a supply tube constructed of a semi-rigid material is easier to place into a patient's esophagus than, for example, a flexible, balloon-type device. In particular, a heat transfer device comprising a flexible material, such as a balloon, requires a delivery device, such as a catheter, guide wire, or sleeve, to direct the heat transfer device into the patient's esophagus. Moreover, flexible, expandable material like a balloon is susceptible to failures, such as bursting, splitting, or puncturing. Use of a semi-rigid material in the construction of a heat transfer device, reduces the points of failure associated with balloon-type device.
In certain embodiments a rigid sleeve may be employed to guide the heat transfer device during placement into a patient. The rigid sleeve may have a section cut-out such that the sleeve comprises approximately a semi-circle in cross section. The sleeve may be removed by sliding it proximally off the heat transfer device. Such a sleeve has certain benefits over a centrally placed guide wire, including a reduced rate of complications from using a guide wire, such as loss of the guide wire into the body cavity and damage caused by the guide wire itself.
In other embodiments, an esophageal heat transfer device of the present technology possesses advantages over other temperature management modalities in that no additional devices, such as stylets, or complicated techniques, such as freezing of the tube, are required for obtaining successful placement in the patient. For example, placement of traditional gastric tubes in an anesthetized, paralyzed, and intubated patient can sometimes be difficult, and many methods have been proposed to aid in the procedure when difficulties occur, including freezing of the tubes, using malleable metal stylets, and the use of slipknots on intubating stylets. Such methods are cumbersome and complicated because additional devices and/or steps are required. In some cases, gastric tubes made of nonreinforced polymer plastic materials can be prone to kinking and coiling during insertion. The ability to place a gastric tube in a relatively simple manner without requiring additional devices or complicated techniques represents a problem that is not solved by methods such as tube freezing and/or the use of malleable metal stylets or slipknots on intubating stylets. Certain embodiments of the present technology provide methods and devices for placement of a gastric tube without requiring additional devices or complicated techniques.
A heat transfer device of the present technology may be placed easily in the patient without additional devices or complicated techniques, by simply connecting the device to the external heat exchanger, turning on the external heat exchanger, and allowing the natural flow of heat exchange medium to provide sufficient firmness to the heat transfer device to allow simple placement.
An esophageal heat transfer device of the present technology is portable, relatively easy to use, and can be inserted into a patient's esophagus by a single health care provider, including a nurse, certified first responder, paramedic, emergency medical technician, or other pre-hospital or in-hospital care provider. An esophageal heat transfer device of the present technology possesses advantages over devices that require multiple people and/or a person trained in advanced medical care. In addition, in a surgical setting, for example, an esophageal heat transfer device of the present technology possesses advantages over other temperature management modalities in that less personnel and attention is required to insert, employ, and/or monitor an esophageal heat transfer device.
For example, users of a balloon-type device must guard against over- or under-inflation of the balloon. Over-inflation can lead to undesired outcomes, including pressure necrosis. Under-inflation can reduce the ability of the device to transfer heat to/from the patient. The use of a balloon-type heat transfer devices also may require the use of a pressure monitor to monitor the inflation pressure. Even when used in conjunction with a pressure monitor, it may not be able to achieve the proper inflation of the balloon.
The heat transfer device may be, for example, a pharyngeo-esophageal heat transfer device, an esophageal heat transfer device, an esophago-gastric heat transfer device, or a pharyngeo-esophago-gastric heat transfer device. For example, an esophageal heat transfer device may include a heat transfer region of about twenty (20) centimeters. Alternatively, an esophago-gastric heat transfer device may include a heat transfer region of about forty (40) centimeters. As yet another alternative, a pharyngeo-esophago-gastric heat transfer device may include a heat transfer region of about forty-five (45) to about fifty (50) centimeters. Heat transfer devices of the present technology can include heat transfer regions of about 22, about 24, about 26, about 28, about 30, about 32, about 34, about 36, about 38, about 40, about 42, about 44, about 46, about 48, about 50, about 52, about 54, about 56, about 58, about 60, about 62, about 64 about 66, about 68 or about 70 centimeters.
Heat transfer devices of the present technology can have a heat transfer region having a diameter of, for example, about 1.0 to about 2.0 centimeters. The diameter of the heat transfer region can be about 1.1, about 1.2, about 1.3, about 1.4, about 1.5, about 1.6, about 1.7, about 1.8, or about 1.9 centimeters. In certain embodiments, a heat transfer region of a heat transfer device of the present technology has a length of about 32 centimeters and a diameter of about 1.4 centimeters, giving a surface area of about 140 cm2.
Increasing the length and/or circumference of the heat transfer region of the device, and therefore the surface area of the heat transfer region, improves the speed and efficiency at which the patient is cooled or heated (or re-warmed). In certain embodiments the heat transfer region can be about 15 in2, about 20 in2, about 25 in2, 30 in2, about 35 in2, about 40 in2, about 45 in2, about 50 cm2, about 60 cm2, about 70 cm2, about 80 cm2, about 90 cm2, about 100 cm2, about 110 cm2, about 120 cm2, about 130 cm2, about 140 cm2, about 150 cm2, about 160 cm2, about 170 cm2, about 180 cm2, about 190 cm2, about 200 cm2, about 210 cm2, about 220 cm2, about 230 cm2, about 240 cm2, about 250 cm2, about 260 cm2, about 270 cm2, about 280 cm2, about 290 cm2, about 300 cm2, about 310 cm2, about 320 cm2, about 330 cm2, about 340 cm2, or about 350 cm2. In certain embodiments, a heat transfer region can contact substantially all of the epithelial surface of a subject's esophagus.
The heat transfer device may be adapted to permit gastric access to the patient's health care provider. The heat transfer device may incorporate, for example, a gastric tube or gastric probe. The gastric tube or gastric probe may run parallel to the heat transfer medium supply tube and the heat transfer medium return tube. Alternatively, the gastric tube, the gastric probe, or both may be in a concentric arrangement with at least one of the heat transfer medium supply tube or the heat transfer medium return tube. The gastric probe may be, for example, a temperature probe.
The heat transfer device may incorporate, for example, multiple tubes and/or probes that, for example, permit access to the patient's gastrointestinal system. The gastric tubes may be adapted to, for example, deliver alimentation directly to a patient's stomach or to a more distal component of the gastrointestinal tract, such as the jejunum. The gastric tubes may also be adapted to, for example, administer medications to various components of the gastrointestinal tract, including esophageal mucosa, stomach, duodenum, and jejunum. Such devices allow for a relatively non-invasive method for controlling a patient's temperature while simultaneously administering alimentation and/or medication. Such methods and devices are superior to contemporary methods to affect temperature control and modification, which do not readily permit simultaneous medication and/or alimentation administration and gastric decompression, despite the fact that medication administration through the gastrointestinal tract is in some cases of superior efficacy to intravenous administration. Thus, the methods and devices of the present technology allow for the provision of alimentation and medication through the gastrointestinal tract, while simultaneously, allowing for temperature control and modification. Such an approach is an improvement over intravenous administration of nutrients and medications, adding substantially to the risk of complications and the expense of treatment.
In certain embodiments, the heat transfer device may incorporate a device that measures a physiological parameter such as temperature, pressure, oxygen saturation, pH, heart rate, Doppler signals, electromagnetic fluctuations, or chemical composition. For example, the heat transfer device may include or incorporate one or more thermometers, each with one or more temperature probes, for measuring the ambient temperature, patient temperature, or heat transfer medium temperature. The thermometers may be separate devices or integrated with the heat transfer system. Likewise, the heat transfer device may include or incorporate electrochemical biosensors, or biological micro-electromechanical systems (Bio-MEMS), allowing lab-on-chip (LOC) and incorporation of Micro Total Analysis Systems (μTAS) analysis of biochemical composition of the gastroesophageal environment. In addition, at least one aspect of the present technology provides one or more methods for use of a lab-on-chip to perform biochemical assays, dielectrophoresis, real-time PCR, and immunoassays for the detection of bacteria, viruses, and cancers.
In certain embodiments of the present technology, the heat transfer system may further incorporate or include a device that measures a physiological parameter such as pressure. For example, the heat transfer system may include one or more sensors of esophageal pressure, transpulmonary pressure, and/or intra-abdominal pressure.
In certain embodiments of the present technology, the heat transfer device comprises a pressure transducer located proximately, at any point along and throughout the midpoint, or distally, to allow measurement of esophageal pressure and/or transpulmonary pressure. Direct measurement of esophageal pressure allows for a subsequent estimate of transpulmonary pressure to provide, for example, guidance in supporting a patient with mechanical ventilation.
In patients with high pleural pressure on conventional ventilator settings, under-inflation may lead to atelectasis, hypoxemia, and exacerbation of lung injury. In patients with low pleural pressure, maintaining a low positive end-expiratory pressure (PEEP) keeps trans-pulmonary pressure low, avoiding over-distention and subsequent lung injury. Esophageal manometry has been used to identify the optimal ventilator settings in order to avoid both under-inflation and over-inflation of the pulmonary system; however, the optimal level of PEEP has been difficult to determine. Therefore, at least one aspect of the present technology provides one or more methods for measuring esophageal pressure as a means to estimate the transpulmonary pressure and subsequently determine optimal PEEP values that can maintain oxygenation of patients undergoing mechanical ventilation while preventing lung injury due to alveolar collapse or over-distention.
In certain embodiments of the present technology, the heat transfer device comprises a pressure transducer located distally to allow direct measurement of intra-abdominal pressure. The pressure transducer can be used to, for example, diagnose abdominal compartment syndrome. Abdominal compartment syndrome is a complication of a wide variety of illnesses, including many of which are known or suspected to benefit from control of a patient's temperature. For example, abdominal compartment syndrome can be a primary event developing from such conditions as pancreatitis, intraperitoneal hemorrhage from blunt trauma, penetrating trauma, perforation of an ulcer, or rupture of an aortic aneurysm. Abdominal compartment syndrome can also develop as a secondary event after large burns, sepsis, large volume resuscitation, penetrating or blunt trauma, or postoperatively.
At least one aspect of the present technology provides one or more methods for measuring intra-abdominal compartment pressure and diagnosing intra-abdominal compartment syndrome through the incorporation of a pressure transducer at the distal end of the device, which allows direct measurement of intra-abdominal pressure. The devices and methods of the present technology provide for superior measurement of intra-abdominal pressure as compared to contemporary methods, such as those mentioned in US Patent Application Publication 2009/0221933 to Nagao et al., which are indirect, technically challenging, invasive, and time-consuming.
Manufacture of heat transfer devices of the present technology can be accomplished via stereolithography. Stereolithography is a manufacturing process in which parts are built one layer at a time using an ultraviolet curable photopolymer resin, in a method referred to as an additive manufacturing process.
Another embodiment of the present technology provides for a multi-lumen heat transfer device for inducing mild therapeutic hypothermia. The heat transfer device may include one or more lumens that provide a fluid path for circulation of a coolant. For example, the heat transfer device may include a coolant supply tube and a coolant return tube. The lumens of the coolant supply tube and coolant return tube may be in fluid communication with each other thereby defining a fluid path for coolant flow. The coolant supply tube and coolant return tube may be arranged, for example, in parallel or concentrically.
Another embodiment of the present technology provides for a multi-lumen heat transfer device for controlling patient temperature. The heat transfer device may include one or more lumens that provide a fluid path for circulation of a heat transfer medium. For example, the heat transfer device may include a medium supply tube and a medium return tube. The lumens of the medium supply tube and medium return tube may be in fluid communication with each other thereby defining a fluid path for medium flow. The medium supply tube and medium return tube may be arranged, for example, in parallel or concentrically.
At least one aspect of the present technology provides a heat transfer device comprising one or more lumens. For example, the device may comprise a single lumen for delivery of a heat transfer medium to a heat transfer region of the device. As described herein, the heat transfer medium may be a gas (e.g., nitrous oxide, Freon, carbon dioxide, or nitrogen), liquid (e.g., water, saline, propylene glycol, ethylene glycol, or mixtures thereof), solid (e.g., ice, metal, metal alloy, or carbon fiber), slurry, and/or gel. In certain embodiments, the single lumen may function as both the inflow lumen and the outflow lumen. For example, heat transfer medium may be delivered to the heat transfer region and extracted from the heat transfer region via the single lumen by, for example, an external pump that alternatively pumps and withdraws heat transfer medium via the single lumen. In certain other embodiments, a solid heat transfer medium, which may comprise a heating element such as a wire or coil; a thermoelectric module such as a Peltier module; or a carbon fiber such as a graphitic carbon fiber, may be inserted into the single lumen.
In certain embodiments, the one or more lumens may be defined by a tube having a substantially helical configuration. The substantially helical configuration of the tube creates an interior space defined by the helix, which may comprise, for example, an access lumen. The substantially helical tube can helically wrap around a separate probe or tube, such as a commercially available nasogastric or orogastric tube. In certain embodiments, such as esophageal heat transfer devices, the substantially helical configuration allows for gastric access. For example, the external walls of the tube having a substantially helical configuration may define an access lumen. Where the heat transfer device is for placement within the esophagus, the tube having a substantially helical configuration allows for gastric access via a gastric access lumen. A separate probe, such as a temperature probe, or separate tube, such as a nasogastric tube or an orogastric tube, can be inserted into the patient via the gastric access lumen. The separate probe or tube may be inserted within the gastric access lumen before or after inserting the device into the patient. Alternatively, the nasogastric or orogastric tube may be affixed (e.g., glued) to the substantially helical tube. The nasogastric tube, orogastric tube, or probe may be provided with the heat transfer device or provided as an after-market component.
In certain embodiments, the one or more lumens may be defined by a tube having a C-shaped cross section. In certain embodiments, such as esophageal heat transfer devices, the C-shaped design allows for gastric access. For example, the C-shaped design allows for the use of a commercially available probe, such as a temperature probe, or tube, such as a nasogastric tube or an orogastric tube, with the heat transfer device of the present technology. For example, the C-shaped tube can wrap around a commercially available nasogastric or orogastric tube. The nasogastric or orogastric tube may be inserted within the interior space defined by the C-shaped tube before or after inserting the device into the patient. Alternatively, the nasogastric or orogastric tube may be affixed (e.g., glued) to the C-shaped tube.
Thus, in some embodiments, the present technology comprises an esophageal heat transfer system comprising an esophageal heat transfer device and a nasogastric tube. In other embodiments, the present technology comprises an esophageal heat transfer system comprising an esophageal heat transfer device and an orogastric tube. In still other embodiments, the present technology comprises an esophageal heat transfer system comprising an esophageal heat transfer device and a temperature probe. In yet other embodiments, the present technology comprises an esophageal heat transfer system comprising an esophageal heat transfer device and an orogastric tube, nasogastric tube, and/or temperature probe.
Yet another embodiment of the present technology provides one or more devices for cooling or warming multiple portions of a patient's body simultaneously. The devices comprise a heat transfer device including a proximal end, a distal end, at least one flexible tube extending between the proximal and distal end, and additional flexible tubes extending from the proximal end. The proximal end includes a heat transfer medium input port, a heat transfer medium output port, and about 2 to about 4 ancillary tubes extending off the proximal end providing for additional heat transfer medium flow pathways. The distal end of the device is configured for insertion into a larger orifice of a patient, while the distal ends of the ancillary tubes are configured for insertion into additional smaller orifices or configured external as an external component for surface contact. For example, the ancillary tubes can be configured as a head and/or neck wrap to provide surface cooling.
At least one aspect of the present technology provides a heat transfer device comprising (a) a plurality of lumens configured to provide a fluid path for flow of a heat transfer medium; (b) a heat transfer region configured for contacting esophageal epithelium, nasopharyngeal epithelium, auricular canal epithelium, and/or the tympanic membranes of a patient; (c) a proximal end including an input port, an output port, and ancillary tubing containing heat transfer medium flow channels; and (d) a distal end configured for insertion into an esophagus of a patient. The heat transfer device can also comprise a hollow tube having a distal end configured to extend into the patient's stomach. The heat transfer device can be capable of contacting substantially all of the patient's esophageal epithelium, nasopharyngeal epithelium, auricular canal epithelium, or the tympanic membranes.
Without wishing to be bound by theory, it is believed that affecting temperature change through the nasopharynx and/or auricular canals has the benefit of affecting temperature change at a location in direct proximity to the brain. The methods and devices of the present technology overcome the logistical and technical challenges of affecting temperature change through the nasopharynx and/or auricular canals.
A device for cooling or warming multiple portions of a patient's body simultaneously may be used to treat or prevent, for example, injury caused by an ischemic condition; ischemia-reperfusion injury; neurological injury; or cardiac injury. The device may be used to treat patients who have experienced or are experiencing myocardial infarction; stroke; traumatic brain injury; or ARDS. The methods of treating or preventing such conditions or diseases comprise, for example, inserting the distal end of the heat transfer device orally; advancing the distal end into the patient's esophagus; advancing the ancillary tubing into the patient's nasopharynx and/or into the patient's auricular canals; initiating flow of a cooling medium along the fluid path; and circulating the cooling medium along the fluid path for a time sufficient to induce systemic hypothermia in the patient. The patient may be maintained in a state of hypothermia for at least two hours. The methods may further comprise monitoring at least one physiological parameter of the patient, such as body temperature. The methods may further comprise maintaining the patient's body temperature below about 34° C.
The device may be used to control a patient's core body temperature during, for example, surgical procedures. The methods of controlling the patient's core body temperature comprise, for example, inserting the distal end of the heat transfer device nasally or orally; advancing the distal end into the patient's esophagus; advancing the ancillary tubing into the patient's nasopharynx and/or into the patient's auricular canals; initiating flow of a cooling medium along the fluid path; and circulating the heat transfer medium along the fluid path for a time sufficient to control core body temperature in the patient. The core body temperature of the subject may be controlled for at least about two hours, for example. The methods may further comprise monitoring at least one physiological parameter of the subject, such as body temperature. The methods may further comprise maintaining the patient's body temperature, for example, below about 34° C., between about 34° C. and about 37° C., or at about 37° C.
Yet another embodiment of the present technology provides relatively non-invasive devices and methods for heating or cooling a patient's entire body while simultaneously maintaining a less drastic, or opposite direction, local temperature change. Thus, at least one aspect of the present technology provides one or more methods for inducing systemic hypothermia while simultaneously imparting local normothermia, for example to the region of the esophagus in closest proximity to the atrium of the heart. Such methods and devices are superior to contemporary methods to affect temperature control and modification, which can either warm or cool independently, but are unable to cool some sections of the body while simultaneously warming others, or vice versa. Because of differential effects of temperature change on organs and regions of the human body, the ability to impart varying degrees of temperature differential, in similar or opposite directions simultaneously at different parts of the body, is beneficial.
Certain embodiments of the present technology may utilize a controller such as that described in US20070203552 (Machold). For example, a controller may employ a Peltier module to heat or cool a heat exchange region of the device, which would allow the device to alternate between heating and cooling modalities merely by changing the polarity of the current flowing through the module. In addition, the amount of heat or cold generated can be adjusted by controlling the amount of current flowing through the module. In particular, a controller may employ a cascading proportional integrated differential (PID) control scheme. In such a scheme, a control system is provided that may be divided into two sections: (a) a Bulk PID control section which takes input from the health care provider or other user, such as target temperature, and input from the sensors on the patient representing patient temperature, and calculates an intermediate set point temperature (SP1) and an output signal to the Heat Transfer Fluid PID control; and (b) the Heat Transfer Fluid PID control, that receives input from the Bulk PID control section and from a sensor representing the temperature of a heat transfer fluid, and generates a signal that controls the temperature of the heat exchanger by, for example, varying the power input to the heat exchanger.
The heat transfer fluid circulates in heat exchanger, so the Heat Transfer Fluid PID essentially controls the temperature of the heat transfer fluid. In this way, the control scheme is able to automatically achieve a specified target based on input from sensors placed on the patient and the logic built into the controller. Additionally, this scheme allows the unit to automatically alter the patient temperature very gradually the last few tenths of a degree to achieve the target temperature very gently and avoid overshoot or dramatic, and potentially damaging, swings in the electronic power to the heat exchanger. Once the target temperature is achieved, the system continues to operate automatically to add or remove heat at precisely the rate necessary to maintain the patient at the target temperature.
In general, the controller can include a controlled variable, such as pump output, inflation/deflation pressure, or power input to the heat exchanger. A detecting unit or sensor can act as a feedback device for detecting a parameter, such as patient temperature, intra-abdominal pressure, or the presence of air in a line, and outputting a feedback signal relative to the control variable. The control unit performs a PID operation, in which the controlled variable is adjusted according to the comparison between the feedback signal and a predetermined target value.
As an example, the feed back signal T can represent patient temperature and the predetermined target value TTarg can represent a target temperature set by a health care professional. When the feedback signal T is larger than the target value TTarg, it means that the patient's temperature is too high. Accordingly, the controller, for example, increases or decreases pump output or power input to the heat exchanger in order to change the temperature and/or flow rate of the heat exchange medium. When the feedback signal T is smaller than the target value TTarg, it means that the patient's temperature is too low. Accordingly, the controller, for example, increases or decreases pump output or power input to the heat exchanger in order to change the temperature and/or flow rate of the heat exchange medium.
As another example, the feedback signal P can represent the patient's intra-abdominal, esophageal, and/or gastric pressure and the predetermined target value PMax can represent a maximum pressure set by a health care professional. In certain embodiments, placement of an esophageal heat transfer device having an inflatable heat transfer region may cause elevated intra-abdominal, gastric, and/or esophageal pressure by preventing adequate gastric ventilation. When the feedback signal P approaches, reaches, and/or surpasses PMax, it means that the patient's intra-abdominal, esophageal, and/or gastric pressure is in danger of or has become unacceptably high. Accordingly, the controller, for example, decreases pump output or otherwise deflates the inflatable heat transfer region in order to allow for gastric ventilation. Following gastric ventilation, the feedback signal P should approach, reach, and/or fall below PMax as the patient's intra-abdominal, esophageal, and/or gastric pressure is returning to or has returned to an acceptable level. Accordingly, the controller, for example, increases pump output or otherwise inflates the inflatable heat transfer region, thereby at least partially restricting gastric ventilation.
As yet another example, the controller may be programmed to periodically inflate and deflate the inflatable heat transfer region to prevent the build-up of intra-abdominal, esophageal, and/or gastric pressure. For example, the controller may increase pump output or otherwise inflate the inflatable heat transfer region. The inflation time period may be about 5 to about 60 minutes, including about 10, about 15, about 20, about 25, about 30, about 35, about 40, about 45, about 50, or about 55 minutes. During this period of inflation, the subject may experience elevated intra-abdominal, gastric, and/or esophageal pressure because adequate gastric ventilation is restricted by placement of the inflatable heat transfer region within the esophagus. Periodic deflation of the inflatable heat transfer region allows for adequate gastric ventilation. For example, the controller may decrease pump output or otherwise deflate the inflatable heat transfer region. The deflation time period may be about 1 to about 10 minutes, including about 2, about 3, about 4, about 5, about 6, about 7, about 7, about 8, or about 9 minutes.
Certain embodiments of the present technology provide an unexpectedly superior rate of temperature change relative to other devices and methods. The present methods and devices can provide a rate of cooling of about 0.5° C./hour to about 2.2° C./hour in a large animal model of similar size to an average adult human. Present methods and devices are capable of demonstrating a total heat extraction capability of about 250 kJ/hour to about 750 kJ/hour. For example, the present methods and devices can provide a rate of cooling of about 1.2° C./hr to about 2.4° C./hr in a large animal model of similar size to an average adult human. Alternatively, the present methods and devices can provide a rate of cooling of about 1.2° C./hour to about 1.8° C./hour in a large animal model of similar size to an average adult human, which demonstrates a total heat extraction capability of about 350 kJ/hour to about 530 kJ/hour. Methods and devices of the present technology can provide a rate of cooling of about 1.3, about 1.4, about 1.5, about 1.6, and about 1.7° C./hour. Methods and devices of the present technology are capable of demonstrating a total heat extraction capability of about 350, about 360, about 370, about 380, about 390 about 400, about 410, about 420, about 430, about 440, about 450, about 460, about 470, about 480, about 490, about 500, about 510, and about 520 kJ/hour.
While not wishing to be bound by any particular theory, it is thought that the methods and devices of the present technology transfer more heat per unit time than other devices. For example, heat transfer devices of the present technology include heat transfer regions that, for example, extend to substantially the entire length and/or circumference of the patient's esophagus, providing increased contact surface between the heat transfer region of the heat transfer device and patient anatomy including, the esophageal epithelium and the vasculature that surrounds the esophagus. Heat transfer devices of the present technology additionally enable reduction of gastric pressure through gastric ventilation, thereby reducing the possibility of ballooning and distention of the esophageal mucosa away from contact with the esophageal mucosa, and further enhancing heat transfer across the esophageal mucosa. In addition, materials for constructing the heat transfer devices of the present technology include those with superior heat transfer characteristics. Heat transfer devices of the present technology can be manufactured with thinner wall thicknesses, further reducing the heat transfer resistance across the device and increasing the effectiveness of heat extraction from, or heat addition to, the patient.
The presently described technology now will be described with respect to the appended figures; however, the scope of the present technology is not intended to be limited thereby. It is to be understood that the scope of the present technology is not to be limited to the specific embodiments described herein. The technology may be practiced other than as particularly described and still be within the scope of the claims.
FIG. 1 is a schematic view of a heat transfer system 100 according to an embodiment of the present technology. The heat transfer system 100 includes a heat transfer device 102, a heat exchanger 104, a heat transfer medium 106, and a network of tubular structures 108 for circulating the heat transfer medium 106 between the heat transfer device 102 and the heat exchanger 104.
The heat exchanger 104 is configured to heat or chill the heat transfer medium 106. The heat exchanger 104 may be any of a variety of conventionally designed heat exchanger 104s. For example the heat exchanger 104 may be a standard chiller, such as an RF-25 Recirculating Chiller manufactured by New Brunswick Scientific. The heat transfer medium 106 may be a gas, such as, for example, nitrous oxide, Freon, carbon dioxide, or nitrogen. Alternatively, the heat transfer medium 106 may be a liquid, such as, for example, water, saline, propylene glycol, ethylene glycol, or mixtures thereof. In other embodiments, the heat transfer medium 106 may be a slurry, such as, for example, a mixture of ice and salt. In still other embodiments, the heat transfer medium 106 may be a gel, such as, for example, a refrigerant gel. Alternatively, the heat transfer medium 106 may be a solid, such as, for example, ice or a heat conducting metal. For example, the heat transfer medium 106 may comprise a heating element, such as a wire or ribbon. Such a wire or ribbon may be straight or coiled and may comprise any metal or combination of metals, including those that are routinely used such as iron-chromium-aluminum wires, nichrome wires, and copper-nickel wires. Alternatively, the heat transfer medium 106 may comprise a cooling tube comprising a heat conducting metal. For example, the heat transfer medium 106 may comprise a copper tube. The copper tube may carry a refrigerant or blend comprising, for example, freon, hydrofluorocarbon, chlorofluorocarbon, or hydrochlorofluorocarbon. In yet another embodiment, a solid heat transfer medium 106 may comprise a carbon fiber, such as graphitic carbon fibers. In other embodiments, the heat transfer medium 106 may be formed, for example, by mixing a powder with a liquid. Thus, it should be understood that combinations and/or mixtures of the above-mentioned media may be employed to achieve a heat transfer medium 106 according to the present technology.
The network of tubular structures 108 for circulating the heat transfer medium 106 may include an external supply tube 110 and an external return tube 112. The external supply tube 110 defines an external supply lumen 114 providing a fluid path for flow of the heat transfer medium 106 from the heat exchanger 104 to the heat transfer device 102. The external return tube 112 defines an external return lumen 116 providing a fluid path for flow of the heat transfer medium 106 from the heat transfer device 102 to the heat exchanger 104. A pump 118 may be employed to circulate the heat transfer medium 106 through the network of tubular structures 108, and the flow rate of the medium, and, hence the heat transfer capabilities of the device, can be regulated by adjusting the pumping rate.
The heat transfer device 102 is adapted for placement within an anatomical structure of a mammalian patient. The heat transfer device 102 has a proximal and a distal end. The distal end of the heat transfer device 102 may be configured for insertion into a body orifice. For example, the distal end of the heat transfer device 102 may be configured for insertion into the nostrils, mouth, anus, or urethra of a patient. When properly inserted, the distal end of the heat transfer device 102 may be ultimately positioned in the esophagus, rectum, colon, bladder, or other anatomical structure. The proximal end of the heat transfer device 102 includes an input port 120 and an output port 122. The input port 120 and output port 122 are connected to the network of tubular structures 108 for circulating the heat transfer medium 106. For example, the input port 120 may be connected to the external supply tube 110 and the output port 122 may be connected to the external return tube 112. Thus, in certain embodiments, the heat exchanger 104 may be in fluid communication with the heat transfer device 102 via the network of tubular structures 108.
In operation, the heat transfer device 102 is positioned into an anatomical structure, such as the esophagus. The heat exchanger 104 is used to heat or chill the heat transfer medium 106 that is supplied to the heat transfer device 102 via the external supply tube 110. The heat transfer medium 106 flows through the external supply tube 110 and enters the heat transfer device 102 through the input port 120. The heat transfer medium 106 circulates through the heat transfer device 102 and exits the heat transfer device 102 through the output port 122, and returns to the heat exchanger 104 via the external return tube 112. Raising or lowering the temperature of the heat transfer medium 106 alters the body temperature of the patient.
The heat transfer system 100 may further incorporate a device that measures a physiological parameter such as temperature, pressure, or electromagnetic fluctuations. For example, the heat transfer system 100 may include one or more thermometers 124, each with one or more temperature probes 126, for measuring the ambient temperature, patient temperature, or heat transfer medium 106 temperature. The thermometers may be separate devices or integrated with the heat transfer system 100.
FIG. 2 depicts a heat transfer device 200 according to an embodiment of the present technology. For purposes of further elucidating this embodiment, the heat exchanger will be referred to as a chiller (not shown) and the heat transfer medium will be referred to as a coolant. However, it should be understood that any suitable heat exchanger and any suitable heat transfer medium may be employed with the heat transfer device depicted in FIG. 2.
The heat transfer device 200 comprises a distal end 202, a proximal end 204, and a length of flexible tubing 206 extending therebetween. The proximal end 202 includes an input port 208 for receiving coolant from the chiller and an output port 210 allowing coolant to return to the chiller.
The input port 208 comprises a standard plumbing tee fitting 212. Alternatively, any fitting with two or more open ends, such as a wye fitting may be employed. The fitting may be composed of any suitable material, including, for example metal, such as, copper or iron; metal alloy, such as steel or brass; or plastic, such as, polyvinyl chloride (“PVC”) or polyethylene (“PE”). A brass plug 214 is affixed to the proximal open end of the tee fitting 212. Alternatively, standard caps, such as metal or plastic caps, may be affixed to the proximal open end of the fitting. The plug 214 includes an opening to allow for tubing clearance. The plug 214 is affixed to the fitting with chemical sealant 216, such as, for example, Room-Temperature Vulcanization (“RTV”) Silicone Sealant. In other embodiments, the input port 208 may be manufactured in a way that eliminates the need for affixed end caps, such as, for example, by extrusion.
The output port 210 comprises a standard plumbing tee fitting 212. Alternatively, any fitting with two or more open ends, such as a wye fitting may be employed. The fitting may be composed of any suitable material, including, for example metal, such as, copper or iron; metal alloy, such as steel or brass; or plastic, such as, PVC or PE. Brass plugs 214 are affixed to the proximal open end and distal open end of the tee fitting. Alternatively, standard caps, such as metal, metal alloy, or plastic caps, may be affixed to the open ends of the fitting. Each plug 214 may include an opening to allow for tubing clearance. The plugs 214 are affixed to the fitting with chemical sealant 216, such as, for example, RTV Silicone Sealant. In other embodiments, the output port 210 may be manufactured in a way that eliminates the need for affixed end caps, such as, for example, by extrusion.
The length of tubing 206 extending between the proximal end 204 and distal end 202 of the heat transfer device 200 is a coolant supply tube 218. The coolant supply tube 218 may be composed of clear vinyl. Alternatively, the coolant supply tube 218 may be composed of other suitable materials, such as, for example, flexible medical grade transparent PVC. The dimensions of the coolant supply tube 218 may be approximately 0.625′′ outside diameter (“OD”)×0.500′′ inside diameter (“ID”). The coolant supply tube 218 is affixed to the input port 208 with chemical sealant 216, such as, for example, RTV Silicone Sealant. The coolant supply tube 218 extends from the input port 208 to the distal end 202 of the heat transfer device 200. The length of the coolant supply tube 218 may be about eighteen (18) to about fifty-two (52) centimeters. In certain embodiments, the length of the coolant supply tube 218 may be from about eighteen (18) to about twenty-two (22) centimeters. In certain embodiments, the length of the coolant supply tube 218 may be from about thirty (30) to about forty-two (42) centimeters. In other embodiments, the length of the coolant supply tube 218 may be from about forty-five (45) to about fifty-two (52) centimeters. The length of the coolant supply tube 218 can be about thirty-two (32) centimeters.
The distal end 202 of the heat transfer device 200 includes an end cap 220. The end cap 220 may be composed of any suitable material, including, for example, metal, such as, copper or iron; metal alloy, such as steel or brass; or plastic, such as, PVC or PE. The end cap 220 is affixed to the coolant supply tube with chemical sealant 216, such as, for example, RTV Silicone Sealant.
A coolant return tube 222 may be positioned within the coolant supply tube 218. The coolant return tube 222 may be composed of clear vinyl. Alternatively, the coolant return tube 222 may be composed of other suitable materials, such as, for example, flexible medical grade transparent PVC. The outside diameter of the coolant return tube 222 is smaller than the inside diameter of the coolant supply tube 218. For example, the dimensions of the coolant return tube 222 may be approximately 0.437′′ outside diameter (“OD”)×0.312′′ inside diameter (“ID”). The coolant return tube 222 may be affixed to one or both of the input port 208 or output port 210 with chemical sealant 216, such as, for example, RTV Silicone Sealant.
The coolant return tube 222 does not extend to the end cap 220 at the distal end 202 of the heat transfer device 200. Thus, the lumen of the coolant supply tube 224 and the lumen of the coolant return tube 226 may be in fluid communication with each other, thereby defining a fluid path for coolant flow.
In operation, the coolant enters the input port 208 and flows through the lumen of the coolant supply tube 224 to the distal end 202 of the heat transfer device 200, which may be positioned in, for example, the esophagus of a patient. The coolant then flows through the lumen of the coolant return tube 226 to the output port 210. In operation, heat is transferred from, for example, the esophagus to the coolant, resulting in a decrease in the temperature of the esophagus, as well as adjacent organs, and ultimately, systemic hypothermia.
In certain embodiments, additives with high heat transfer coefficient, such as copper, for example, may be added to the material used for manufacture of the coolant supply tube 218 or the coolant return tube 222. In one embodiment, lengths of wire, for example, running linearly or spiraling along the length of the tube may be included. In other embodiments, particulate matter with a high heat transfer coefficient may be mixed in to the material used for manufacture of the coolant supply tube 218 or the coolant return tube 222 (for example, vinyl or PVC) before or during extrusion.
In certain embodiments, the walls of the coolant supply tube 218 and/or coolant return tube 222 may be relatively thin. For example, the wall of the coolant supply tube 218 may be less than about 1 millimeter. Alternatively, the wall of the coolant supply tube 218 may be less than about 0.01 millimeter. In some embodiments, the wall of the coolant supply tube 218 may be less than about 0.008 millimeters. As will be appreciated by one of skill in the art, the thickness of the walls of the heat transfer medium supply tube and/or heat transfer medium return tube may be modified in increments of about 0.001 millimeters, about 0.01 millimeters, or about 0.1 millimeters, for example.
Optionally, the heat transfer device 200 may include a gastric tube 228, to allow for gastric access and, for example, gastric suctioning as well as gastric lavage for diagnosis and/or therapeutic purposes, if so desired. The gastric tube 228 may be composed of clear vinyl. Alternatively, the gastric tube 228 may be composed of other suitable materials, such as, for example, flexible medical grade transparent PVC. The outside diameter of the gastric tube 228 is smaller than the inside diameter of the coolant return tube 222. For example, the dimensions of the gastric tube 228 may be approximately 0.250′′ outside diameter (“OD”)×0.170′′ inside diameter (“ID”). The gastric tube 228 may be affixed to the most proximal port, either the input port 208 or the output port 210, with chemical sealant 216, such as, for example, RTV Silicone Sealant. The gastric tube 228 may allow the patient's health care provider to insert, for example, a nasogastric tube that allows for suctioning of the gastric contents. Alternatively, the gastric tube 228 may allow the patient's health care provider to insert, for example, a gastric temperature probe (not shown).
Optionally, an antibiotic or antibacterial coating may be applied to portions of the coolant supply tube 218, the coolant return tube 222, or the gastric tube 228. Particularly, an antibiotic or antibacterial coating may be applied to portions of the tubes that, upon insertion to a patient, may contact, for example, a mucosal lining of the patient. For example, topical antibiotics, such as tobramycin, colistin, amphotericin B, or combinations thereof, may be applied to the tubes. Incorporation of an antibiotic or antibacterial coating may allow selective decontamination of the digestive tract (“SDD”), which may further improve outcome.
As another alternative, all or part of the heat transfer device 200 can be manufactured by, for example, extrusion. Employing such a manufacturing modality would eliminate the need to seal junctions or affix end caps and reduce the points at which leaks may occur.
FIG. 3 depicts a heat transfer device 300 according to an embodiment of the present technology. The heat transfer device 300 comprises a proximal end 302, a distal end 306, and a length of flexible tubing 304 extending therebetween.
All or part of the heat transfer device 300 can be manufactured by, for example, extrusion. Employing such a manufacturing modality would eliminate the need to seal junctions or affix end caps and reduce the points at which leaks may occur. Alternatively, or additionally, a fast curing adhesive, such as RTV silicone sealant or temperature-curable sealant can be used to seal junctions and/or bond tubing together. The heat transfer device 300 can be constructed using a biocompatible elastomer and/or plastic, and, optionally, adhesive. For example, biomedical grade extruded silicone rubber such as Dow Corning Q7 4765 silicone, and an adhesive such as Nusil Med2-4213 can be used to manufacture heat transfer device 300.
FIG. 3A shows a schematic view of the exterior of heat transfer device 300. The heat transfer device 300 includes an input port 308, a heat transfer medium supply tube 310, a heat transfer medium return tube 312, and an output port 314. In one embodiment, the outer wall of the heat transfer medium supply tube 310 can be in direct contact with patient tissue upon placement of the heat transfer device 300 in a patient. For example, the outer wall of heat transfer medium supply tube 310 can be in direct contact with the patient's esophagus when the heat transfer device 300 is inserted orally or nasally. The portion of the heat transfer medium supply tube 310 that can be in direct contact with patient tissue can be part of the heat transfer region of the heat transfer device 300. Input port 308 is connected to the heat transfer medium supply tube 310 and allows for heat transfer medium to be delivered to the lumen of the heat transfer medium supply tube 310. Input port 308 may be positioned along the length of the heat transfer medium supply tube 310, preferably proximal to the region of the heat transfer medium supply tube 310 that is capable of directly contacting the patient tissue. Heat transfer medium may flow through the heat transfer medium supply tube 310 to the heat transfer medium return tube 312. Output port 314 is connected to the heat transfer medium return tube 312 and may allow for heat transfer medium to exit the device. Output port 314 may be positioned along the length of the heat transfer medium return tube 312, preferably proximal to the heat transfer region of heat transfer device 300. The heat transfer device also includes a central tube 316 that, for example, allows for gastric access. The central tube 316 is in a concentric arrangement with the heat transfer medium supply tube 310 or the heat transfer medium return tube 312 (see FIG. 3B). The central tube lumen 318 provides the health care professional with access to, for example, the patient's stomach while the heat transfer device is positioned within the patient's esophagus.
FIG. 3C is a cross-sectional view along the line 3C, which is identified in FIG. 3B.
The outermost tube is the heat transfer medium supply tube 310. The heat transfer medium supply tube 310 extends from about the input port 308 to about the distal end 306 of the heat transfer device 300. The length of the heat transfer medium supply tube 310 can be about eighteen (18) to about seventy-five (75) centimeters. In a particular embodiment, the length of the heat transfer medium supply tube 310 is about thirty-two (32) centimeters. The outside diameter of the heat transfer medium supply tube 310 can be, for example, about 1.0 to about 2.0 centimeters. In a particular embodiment, the outside diameter of the heat transfer medium supply tube 310 is about 1.4 centimeters.
Upon insertion into, for example, the esophagus of a patient, the wall of the heat transfer medium supply tube 310 can be in direct contact with the patient's esophagus. As noted above, the length and/or circumference of the heat transfer medium supply tube 310, and therefore the surface area of heat transfer medium supply tube 310, can vary. Increasing the area of contact between the heat transfer device 300 and the patient's esophagus improves the speed and efficiency at which the patient is cooled or heated (or re-warmed). In certain embodiments the surface area of the heat transfer medium supply tube 310 can be from about 50 cm2 to about 350 cm2. In a particular embodiment, the surface area of the heat transfer region of the heat transfer medium supply tube 310 can be about 140 cm2. In certain embodiments, the heat transfer medium supply tube 310 can contact substantially all of the epithelial surface of a patient's esophagus.
Positioned within the heat transfer medium supply tube 310 is the heat transfer medium return tube 312. The outside diameter of the heat transfer medium return tube 312 is smaller than the inside diameter of the heat transfer medium supply tube 310. The heat transfer medium return tube 312 does not extend to the distal end of the heat transfer medium supply tube 310. Thus, the heat transfer medium supply tube lumen 320 and the heat transfer medium return tube lumen 322 are in fluid communication with each other, thereby defining a fluid path for the flow of the heat transfer medium.
Positioned within the heat transfer medium return tube is the central tube 316. The outside diameter of the central tube 316 is smaller than the inside diameter of the heat transfer medium return tube 312. The central tube 316 can be, for example, a gastric tube, to allow for gastric access. The central tube 316 can act as a gastric tube that, for example, allows for suctioning of the gastric contents. The central tube 316 also allows a health care professional to insert, for example, a nasogastric tube that allows for suctioning of the gastric contents. Alternatively, the central tube 316 allows a health care professional to insert, for example, a gastric temperature probe.
The distal end of the heat transfer medium supply tube 310 can be sealed with an end cap 324. The end cap 324 can be constructed from, for example, silicone. The end cap 324 can include a hole or other passageway through which central tube 316 can pass. Likewise, the proximal end of the heat transfer medium return tube 312 can be sealed with an end cap 326. The end cap 326 can be constructed from, for example, silicone. The end cap 326 can include a hole or other passageway through which central tube 316 can pass. Junctions between the various components and tubes can be sealed with a sealant 328, such as Nusil Med2-4213.
FIG. 4 shows several views of a proximal end of a heat transfer device according to the present technology.
The heat transfer device comprises at least two concentrically arranged tubes, such as a heat transfer supply tube 402 and a heat transfer return tube 404, forming a multi-lumen heat transfer device having a generally coaxial lumen configuration. The proximal ends of each of the heat transfer supply tube 402 and the heat transfer return tube 404 can be sealed with end caps (not shown). The heat transfer device, optionally, includes a first central tube 410 and/or a second central tube 412. For example, the heat transfer device can comprise one or more gastric tubes.
The heat transfer supply tube lumen 406 is of sufficient diameter to allow passage of the heat transfer return tube 404. Likewise, the heat transfer return tube lumen 408 may be of sufficient diameter to allow passage of the first central tube 410 and/or the second central tube 412. The first central tube 410 and the second central tube 412 can be, for example gastric tubes that provide access to the patient's stomach and allow for suctioning of gastric contents and/or placement of a gastric temperature probe. The end cap (not shown) of the heat transfer return tube 404 can include a hole or other passageway through which central tubes 410 and 412 pass.
The heat transfer supply tube 402 may be coupled to an input port 414. Preferably, input port 414 is in a position such that upon insertion of the device, input port 414 remains external to the patient. The input port 414 may be coupled to an external supply tube (not shown) equipped with standard connectors for interface with a chiller and/or warming device. The heat transfer return tube 404 may be coupled to an output port 416. Preferably, output port 416 is in a position such that upon insertion of the device, output port 416 remains external to the patient. The output port 416 may be coupled to an external return tube (not shown) equipped with standard connectors for interface with the chiller and/or warming device.
FIG. 5 shows schematic and cross-section views of a distal end of a heat transfer device according to the present technology.
The heat transfer device as depicted in FIG. 5A comprises at least two concentrically arranged tubes, such as a heat transfer supply tube 502 and a heat transfer return tube 504, to form a multi-lumen heat transfer device having a generally coaxial lumen configuration. The distal end of the heat transfer supply tube 502 extends beyond the distal end of heat transfer return tube 504 such that the heat transfer supply tube 502 and heat transfer return tube 504 form a heat transfer flow path. The distal end of the heat transfer supply tube 502 can be rounded or otherwise formed to facilitate insertion and positioning of the heat transfer device in the patient's esophagus. The heat transfer device can also comprise a first central tube 506 and/or a second central tube 508. The first central tube 506 and the second central tube 508 can be, for example gastric tubes that provide access to the patient's stomach and allow for suctioning of gastric contents and/or placement of a gastric temperature probe.
FIG. 5B is a cross-sectional view along the line 58, which is identified in FIG. 5A. The heat transfer supply tube 502 and the heat transfer return tube 504 are arranged concentrically. The heat transfer return tube 504 is positioned within the heat transfer supply tube lumen 510. The first central tube 506 and the second central tube 508 are positioned within the heat transfer return tube lumen 512. A health care professional can, for example, insert a gastric temperature probe (not shown) through the first central tube lumen 514 and/or the second central tube lumen 516.
FIGS. 5B-5Q depict additional arrangements of the tubes and lumens that comprise exemplary heat transfer devices and systems of the present technology. FIGS. 5B-5Q show cross-sectional (FIGS. 5B-5I), and corresponding schematic (5J-5Q), views of several alternative configurations of multi-lumen and single-lumen heat transfer devices and/or systems according to embodiments of the present technology.
As shown in FIG. 5C and corresponding FIG. 5K, the heat transfer supply tube lumen 510 and the heat transfer return tube lumen 512 can be arranged in parallel to each other. As shown in FIG. 5D and corresponding FIG. 5L, the first central tube lumen 514 and the second central tube lumen 516 can also be arranged in parallel to the heat transfer supply tube lumen 510 and the heat transfer return tube lumen 512. Alternatively and as shown in FIGS. 5E and 5F, and corresponding FIGS. 5M and 5N, the first central tube lumen 514 and/or the second central tube lumen 516 can be positioned between the heat transfer supply tube lumen 510 and the heat transfer return tube lumen 512. In yet another alternative and as shown in FIG. 5G and corresponding FIG. 5O, the first central tube lumen 514 can abut and run in parallel to the heat transfer supply tube 502 and/or the heat transfer return tube 504. Optionally, a gastric tube or a gastric probe can be inserted into a patient's stomach via the first central tube lumen 514 and/or the second central tube lumen 516. In some embodiments, a commercially available tube, such as a nasogastric tube or an orogastric tube, can be inserted into the patient's stomach via the first central tube lumen 514 and/or the second central tube lumen 516. Such tubes are well known to those of skill in the art. In certain embodiments, the first central tube 506 and/or the second central tube 508 serve as a gastric tube and the need to place a separate nasogastric or orogastric tube is eliminated.
As shown in FIG. 5H and corresponding FIG. 5P, heat transfer supply tube 502 defining the heat transfer supply tube lumen 510 and the heat transfer return tube 504 defining the heat transfer return tube lumen 512 can be arranged to form a C-shape, defining a central interior 518. In embodiments such as an esophageal heat transfer device, the C-shaped design can allow for gastric access. For example, the C-shaped design allows for the use of a commercially available probe, such as a temperature probe, or tube, such as a nasogastric tube or an orogastric tube, with the heat transfer device. The nasogastric tube, orogastric tube, or probe (not shown) may be placed within the central interior 518 of the C-shape formed by the heat transfer supply tube 502 and the heat transfer return tube 504. The nasogastric tube, orogastric tube, or probe (not shown) may be provided with the heat transfer device or provided as an after-market component.
As shown in FIG. 5I and corresponding FIG. 5Q, a heat transfer device may comprise a single heat transfer lumen 520 defined by heat transfer tube 522. The single heat transfer lumen 520 may serve as the heat transfer supply tube lumen 510 and the heat transfer return tube lumen 512. For example, heat transfer medium may be delivered to a heat transfer region of the device and extracted from the heat transfer region via the single heat transfer lumen 520 by, for example, an external pump (not shown) that alternatively pumps and withdraws heat transfer medium via the single lumen. In certain other embodiments, a solid heat transfer medium, which may comprise a heating element such as a wire or coil; a thermoelectric module such as a Peltier module; or a carbon fiber such as a graphitic carbon fiber, may be inserted into the single heat transfer lumen 520. Optionally, at least one central tube 506 defining at least one central lumen 514 can abut and run in parallel to heat transfer tube 522. The central tube 506 can be, for example a gastric tube that provides access to the patient's stomach and allows for suctioning of gastric contents and/or placement of a gastric temperature probe. A gastric tube, such as a nasogastric or orogastric tube, or a gastric probe can be inserted into a patient's stomach via the central tube lumen 514. Alternatively, the central tube 506 can serve as a gastric tube and the need to place a separate nasogastric or orogastric tube is eliminated.
The esophageal heat transfer device shown in FIGS. 2-5 and further discussed herein above is merely exemplary and not meant to be limiting to the present technology. The heat transfer device of the present technology may be configured for insertion into the ears, nostrils, mouth, anus, or urethra of a patient. When properly inserted, the heat transfer portion of the device may be ultimately positioned in the auricular canal, nasopharynx, esophagus, stomach, rectum, colon, bladder, or other anatomical structure.
FIG. 6 depicts a cross-sectional and longitudinal view of heat transfer device 600 according to an embodiment of the present technology.
FIG. 6A depicts a longitudinal view of heat transfer device 600 according to an embodiment of the present technology. The heat transfer device 600 comprises a proximal end 602 and a distal end 604. The heat transfer device 600 includes an inlet port 606, a heat transfer medium supply tube 608, a heat transfer medium return tube 610, and an outlet port 612. The distal end of the heat transfer medium supply tube 608 extends beyond the distal end of heat transfer medium return tube 610 such that the heat transfer medium supply tube 608 and heat transfer medium return tube 610 form a heat transfer medium flow path. The heat transfer device also includes a central tube 614 that, for example, allows for gastric access. The central tube 614 is in a concentric arrangement with the heat transfer medium supply tube 608 or the heat transfer medium return tube 610 or both, to form a multi-lumen heat transfer device having a generally coaxial lumen configuration. The central tube 614 can be, for example, a gastric tube that provides access to the patient's stomach and allows for suctioning of gastric contents and/or placement of a gastric temperature probe. The central tube lumen 616 provides the health care professional with access to, for example, the patient's stomach while the heat transfer device is positioned within the patient's esophagus.
FIG. 6B depicts a cross-sectional view of heat transfer device 600 according to an embodiment of the present technology. The heat transfer medium supply tube 608 and the heat transfer medium return tube 610 are arranged concentrically. The heat transfer medium return tube 610 is positioned within the inflow channel 618, which is defined by heat transfer medium supply tube 608. The central tube 614 is positioned within outflow channel 620, which is defined by heat transfer medium return tube 610. A health care professional can, for example, insert a gastric temperature probe (not shown) through the central tube lumen 616. The heat transfer medium supply tube 608 and the heat transfer medium return tube 610 have inner surfaces comprised of a plurality of splines 622. The plurality of splines 622 surround the heat transfer medium flow path, thereby helping to enhance the likelihood of maintenance of laminar flow, and reduce the likelihood of flow obstruction.
FIG. 7 depicts a schematic view of a distal end of a heat transfer device according to an embodiment of the present technology.
In certain embodiments, an esophageal heat transfer device incorporates a gastric tube 702. The gastric tube 702 may be the center tube of the concentric arrangement of tubes and may comprise a generally hollow tube that provides gastric access. For example, a tube that allows for suctioning of the gastric contents may be inserted into the patient's stomach via the gastric tube 702. In certain embodiments a commercially available tube, such as a nasogastric tube or an orogastric tube, can be inserted into the patient's stomach via the gastric tube 702. Such tubes are well known to those of skill in the art. In certain embodiments, the gastric tube 702 serves as a tube for suctioning stomach contents and the need to place a separate nasogastric tube is eliminated. As another example, a gastric temperature probe may be inserted via the gastric tube 702.
The gastric tube 702 may include several ports 704 that serve as small tubular connections or passageways from the external environment (here, the patient's stomach) to gastric tube lumen 706. The ports 704 may communicate directly (and only) with the gastric tube lumen 706. The ports 704 may be positioned at the distal end of the heat transfer device to provide additional communication portals between the patient's stomach and the gastric tube 702. The ports 704 provide for additional passageways for gastric contents to flow from the patient's stomach out through the gastric tube lumen 706, thereby reducing the likelihood of blockage of the single lumen from semi-solid stomach contents.
In other embodiments, an esophago-gastric heat transfer device comprises concentric tubes such that the center-most tube serves as a gastric tube 702. In such an arrangement, the outermost tube can be, for example, a heat transfer medium supply tube 708. A heat transfer medium return tube 710 can be positioned within the heat transfer medium supply tube 708. Likewise, the gastric tube 702 can be positioned within the heat transfer medium return tube 710.
As shown in FIG. 7, the heat transfer device may be an esophageal or esophago-gastric heat transfer device and comprise three concentrically arranged tubes, including a heat transfer medium supply tube 708, a heat transfer medium return tube 710, and a gastric tube 702 to form a multi-lumen heat transfer device having a generally coaxial lumen configuration. The heat transfer portion of the heat transfer device may be confined to the patient's esophagus, while the gastric tube 702 extends into the patient's stomach. The heat transfer device may further include ports 704 along the side of the gastric tube 702. The distal end of the gastric tube 702 includes several ports along the side of the tube to provide access to the gastric tube lumen 706, thereby reducing the likelihood of blockage of the single lumen from semi-solid stomach contents. The addition of such ports 704 may improve and enhance the removal of stomach contents, which, in turn, may improve contact between gastric mucosa and the heat transfer device. Such improved contact may enhance heat transfer between the heat transfer device and the gastric mucosa.
The configuration of the ports as shown in FIG. 7 is oval. However, the ports can be, for example, circular, rectangular, or any other shape that permits flow of gastric contents from the stomach to the gastric tube lumen 706.
FIG. 8 depicts a heat transfer device 800 according to an embodiment of the present technology. The heat transfer device 800 comprises a proximal end 802, a distal end 806, and a length of flexible tubing 804 extending therebetween. The length of flexible tubing 804 may comprise a heat transfer region. The distal end 806 of the heat transfer device 800 may be configured for insertion into a body orifice. For example, the distal end 806 of the heat transfer device 800 may be configured for insertion into the nostrils or mouth of a patient. When properly inserted, the heat transfer region of the heat transfer device 800 may be ultimately positioned in the esophagus, or other anatomical structure. Upon placement in, for example, the esophagus of a patient, the heat transfer region of the heat transfer device 800 can be in direct contact with the patient's esophagus. In certain embodiments, the heat transfer region of the heat transfer device 800 can contact substantially all of the epithelial surface of a patient's esophagus. The distal end 806 of the heat transfer device 800 may be configured to extend into a stomach of a patient.
All or part of the heat transfer device 800 can be manufactured by, for example, extrusion. Employing such a manufacturing modality would eliminate the need to seal junctions or affix end caps and reduce the points at which leaks may occur. Alternatively, or additionally, a fast curing adhesive, such as RTV silicone sealant or temperature-curable sealant can be used to seal junctions and/or bond tubing together. The heat transfer device 800 can be constructed using a biocompatible elastomer and/or plastic, and, optionally, adhesive. For example, biomedical grade extruded silicone rubber such as silicone rubber available from Dow Corning (e.g., Q7-4765, C6-165, and/or C6-550), and an adhesive such as Nusil Med2-4213 can be used to manufacture heat transfer device 800.
FIG. 8A shows a schematic view of the exterior of heat transfer device 800. The heat transfer device 800 includes an input port 808 and an output port 810. The heat transfer device 800 includes a gastric tube 812 that, for example, allows for gastric access. The proximal end of the gastric tube can be adapted to accommodate attachment to, for example, a suctioning device.
FIG. 8C is a cross-sectional view of the heat transfer device 800. The heat transfer device 800 comprises an internal cavity 816 and a gastric tube 812. The gastric tube 812 defines a gastric lumen 818. As shown in FIGS. 8B and 8C, the distal end 806 of the heat transfer device 800 includes one or more ports 814 along the side of the gastric tube 812. The ports 814 may provide for communication between the space exterior to the device 800 and the gastric tube lumen 818. For example, the ports 814 may act as a portal between the patient's stomach and the gastric tube lumen 818 allowing the gastric contents to be suctioned from the patient's stomach out through the gastric tube lumen 818. The presence of multiple ports 814 provides reduced likelihood of blockage of the gastric tube lumen 818 from semi-solid stomach contents. Alternatively, multiple gastric tube lumens may be employed. The addition of ports 814 may improve and enhance the removal of stomach contents, which, in turn, may improve contact between gastric mucosa and the heat transfer device 800. Such improved contact may enhance heat transfer between the heat transfer device 800 and the gastric mucosa. The configuration of the ports 814 shown in FIG. 8 is oval. However, the ports 814 can be, for example, circular, rectangular, or any other shape that permits flow of gastric contents from the stomach to the gastric tube lumen 818.
FIG. 8D is a cross-sectional view of the heat transfer device 800 along the line D-D shown in FIG. 8A. The internal cavity 816 can be divided by wall 820 into a multi-lumen cavity comprising, for example, a heat transfer medium supply lumen 822 and a heat transfer medium return lumen 824. The heat transfer medium supply tube lumen 822 and the heat transfer medium return tube lumen 824 may be in fluid communication with each other, thereby defining a fluid path for the flow of the heat transfer medium.
The gastric lumen 818 is in a concentric arrangement with the interior cavity 816. As discussed above, the gastric tube lumen 818 provides the health care professional with access to, for example, the patient's stomach while the heat transfer device 800 is positioned within the patient's esophagus.
FIGS. 9A-9D depict schematic representations of a portion of an exemplary heat transfer device according to the present technology. The portion of the heat transfer device represents all or part of a heat transfer region 900. The heat transfer region 900 comprises a tube 902 having a substantially helical configuration. The tube 902 defines an internal lumen 904, which is capable of receiving a heat transfer medium. For example, the internal lumen 904 may provide a fluid path for the flow of a liquid or gaseous heat transfer medium. In one embodiment, the tube 902 may serve as the evaporative component of a freon/gas circuit and be connected with an external condenser (not shown). Alternatively, the internal lumen 904 may be capable of receiving a solid or semi-solid heat transfer medium.
The substantially helical configuration of the tube 902 creates an interior space 906 defined by the helix, which serves as, for example, an access lumen. The access lumen allows for access to anatomical sites beyond the placement of the heat transfer device. For example, where the heat transfer device is for placement within the esophagus, the helical arrangement allows for gastric access via the interior space 906, which serves as, for example, a gastric access lumen. The helical design allows for the use of a commercially available probe, such as a temperature probe, or tube, such as a nasogastric tube or an orogastric tube, with the heat transfer device. The nasogastric tube, orogastric tube, or probe (not shown) may be placed within the interior 906. The nasogastric tube, orogastric tube, or probe (not shown) may be provided with the heat transfer device or provided as an after-market component.
In certain embodiments, the term “patient” refers to a mammal in need of therapy for a condition, disease, or disorder or the symptoms associated therewith. The term “patient” includes dogs, cats, pigs, cows, sheep, goats, horses, rats, mice and humans. The term “patient” does not exclude an individual that is normal in all respects.
As used herein, the term “treating” refers to abrogating; preventing; substantially inhibiting, slowing or reversing the progression of; substantially ameliorating clinical and/or non-clinical symptoms of; or substantially preventing or delaying the appearance of clinical and/or non-clinical symptoms of a disease, disorder or condition.
In the preceding paragraphs, use of the singular may include the plural except where specifically indicated. As used herein, the words “a,” “an,” and “the” mean “one or more,” unless otherwise specified. In addition, where aspects of the present technology are described with reference to lists of alternatives, the technology includes any individual member or subgroup of the list of alternatives and any combinations of one or more thereof.
The disclosures of all patents and publications, including published patent applications, are hereby incorporated by reference in their entireties to the same extent as if each patent and publication were specifically and individually incorporated by reference.
It is to be understood that the scope of the present technology is not to be limited to the specific embodiments described above. The present technology may be practiced other than as particularly described and still be within the scope of the accompanying claims.
Likewise, the following examples are presented in order to more fully illustrate the present technology. They should in no way be construed, however, as limiting the broad scope of the technology disclosed herein.
EXAMPLES
Example 1
Cooling of a Model System
An experiment was conducted to quantify the approximate rate of temperature reduction achievable by use of an exemplary embodiment of the present technology. Target temperature reduction is 4° C. Data were collected and plotted on a common X-Y graph, as shown in FIG. 10.
The arrangement of equipment for this experiment is shown in FIG. 1. A brief description of each piece of equipment is as follows:

    
    
        1. The heat transfer device 102 was an exemplary embodiment of a heat transfer device according to the present technology
        2. An insulated container, 96 cm (l)×36 cm (w)×36 cm (h), containing 88 kg water at the initial temperature shown in Table 1 represented the mass to be cooled.
        3. A 110V electric pump, Little Giant Model PES-70 (4.4 L/min free-flow) was used to circulate hot water within the insulated container (2) to maintain homogeneous temperature of water within this container.
        4. The heat exchanger 104 comprised an insulated container, 51 cm (l)×28 cm (w)×34 cm (d), containing 40 kg ice water.
        5. The pump 118 comprised a 110V electric pump, Little Giant Model PES-70 (250 mL/min as installed) and was used to provide circulation of coolant from the heat exchanger 104 through the external supply tube 110, then through the heat transfer device 102, then through the external return tube 112, and back to the heat exchanger 104.
        6. The external supply tube 110 comprised a Watts clear vinyl #SVKI10, 5⁄8′′ (od)×1⁄2′′ (id)×42′′ (l), to carry coolant from the heat exchanger 104 to the heat transfer device 102.
        7. The external return tube 112 comprised a Watts clear vinyl #SVKI10, 5⁄8′′ (od)×1⁄2′′ (id)×42′′ (l), to carry coolant from heat transfer device 102 to the heat exchanger 104.
        8. A thermometer 124, such as a digital waterproof thermometer including 2 remote probes 126, Taylor Model 1441, was used to monitor:
        
            a. coolant temperature (T3 as shown in FIG. 1) near the discharge of the external return tube 112 into the heat exchanger 104;
            b. ambient temperature (T4 as shown in FIG. 1) within test cell.
        
        
        9. A thermometer 124, such as a digital waterproof thermometer including 2 remote probes 126, Taylor Model 1441, was used to monitor:
        
            a. hot water temperature (T1 as shown in FIG. 1) within insulated container (2), at the end opposite circulation pump (3).
            b. hot water temperature (T2 as shown in FIG. 1) within insulated container (2), at the end nearest circulation pump (3).
        
        
    
    


The body to be cooled in each iteration of this experiment was an 88-kg mass of water, which was held in an insulated container (2) measuring 94×36×26 cm. This mass was chosen as it is representative of the body mass of a typical adult male. Heat transfer to ambient air by free convection was through the 94×36 cm top surface of the body of water. Initial temperature of this mass of water for each iteration of the procedure is shown in Table 1.
The coolant for each iteration of this experiment was a 30-kg mass of water containing an additional 10-kg of ice, which was held in an insulated container. Ice was used to keep the temperature of the coolant nearly constant for the duration of each iteration of the experiment without the need for a powered chiller, and was replenished at the start of each iteration for which the conductive cooling mode was enabled.
There are two modes of temperature reduction to consider in this experiment. They are convective cooling to ambient air, and conductive cooling through the heat transfer device. To quantify the contribution of each mode to the total temperature reduction, a control case was run with the conductive cooling mode disabled (no coolant circulated through the heat transfer device). The procedure was then run two additional times with the conductive cooling mode enabled (the heat transfer device was submerged in the body of hot water, and coolant circulated through it). The difference between temperature reduction rates, with and without conductive cooling enabled, is the temperature reduction rate due to conductive cooling through the heat transfer device.
Summary of data for each iteration of the experiment is shown in Table 1 below:







TABLE 1







Cooling Experiment Results

















4° C. 




Tinit, avg
Tamb, avg
Tcoolant, avg
drop time


Iteration
Description
° C.
° C.
° C.
(hh:mm)





1
Control case,
38.8
19.6
N/A
02:53



convection to







ambient only






2
Conductive 
39.4
20.3
3.9
01:39



cooling enabled, 







Run #1






3
Conductive 
38.1
20.4
3.5
01:38



cooling enabled,







Run #2





In Table 1:


“Tinit, avg“ is the average initial temperature of the body to be cooled, average of two readings


“Tamb, avg“ is the average ambient temperature for the duration of the iteration


“Tcoolant, avg” is the average coolant temperature for the duration of the iteration


“4° C. drop time” is the time required to achieve a 4° C. reduction in average temperature of the body to be cooled.






Thus, conductive cooling through the exemplary heat transfer device employed in this Example significantly decreases time to achieve a 4° C. temperature reduction.
Example 2
Operative Temperature Management
A heat transfer device according to the present technology was utilized in an animal study as described below. The heat transfer region of the heat transfer device was approximately 70 centimeters in length (to accommodate the length of the snout) and had a diameter of about 1.4 centimeters, for a surface area of about 305 cm2.
A large swine with a mass of 70 kg was chosen to best represent the size and average mass of a human patient. The swine was singly housed in an Association for the Assessment and Accreditation of Laboratory Animal Care, International (AAALAC) accredited facility, with primary enclosures as specified in the USDA Animal Welfare Act (9 CFR Parts 1, 2 and 3) and as described in the Guide for the Care and Use of Laboratory Animals (National Academy Press, Washington D.C., 1996).
The swine was anesthetized with a pre-anesthetic mix of Telozole/Xylazine, then provided with anesthesia via inhalational route with isoflurane 2% after endotracheal intubation achieved with standard endotracheal intubation equipment and technique well known to those skilled in the art. Muscular paralysis was obtained with intravenous paralytic. Temperature was monitored continuously via rectal thermocouple probe placed after anesthesia and endotracheal intubation.
A commercially available thermal water bath and circulator (Gaymar Meditherm MTA-5900) was utilized to provide a controlled-temperature heat transfer medium to the heat transfer device. The specific heat transfer medium utilized was distilled water. Specifications of the commercially available thermal water bath and circulator are as follows:
Dimensions: 94 cm H×35 cm W×48 cm D
Weight: 54.9 kg empty; 64.0 kg full
Material: Aluminum Shell, 16 Gauge Steel Chassis
Flow Rate: 1 liter per minute
Power: 220V, 240V, 50 Hz, 6 A
Temperature: Manual: 4 to 42° C., Automatic: 30 to 39° C.
Electrical Cord: 4.6 m detachable power cord
The heat transfer device was connected to the thermal water bath and circulator, which was then powered on and allowed to equilibrate while preparing the swine.
After successful anesthesia, paralysis, and endotracheal intubation of the swine, a central semi-rigid stylet was placed into the heat transfer device and the heat transfer device was lubricated with a biocompatible lubricant.
The heat transfer device was then introduced into the esophagus of the swine using standard esophageal intubation technique well known to those skilled in the art. An external measurement of the distance from oropharyngeal opening to xiphoid process served as an indicator to which the depth of the heat transfer device was inserted. Confirmation of proper depth of insertion was obtained by successful aspiration of gastric contents through the gastric lumen of the heat transfer device.
In order to demonstrate the capacity of the heat transfer device to successfully warm a patient under hypothermic conditions typically found in the operating room environment, the swine was cooled by setting the supply temperature of the heat transfer medium to the low set point (4° C.) for a time sufficient to reduce the temperature of the swine to 33.6° C.
Data from the cooling portion of the experiment are shown in Table 2. As can be seen in Table 2, a 1° C. reduction in core body temperature of a 67.5 kg swine was achieved in about 40 minutes; a 2° C. reduction in core body temperature of a 67.5 kg swine was achieved in about 80 minutes; a 3° C. reduction in core body temperature of a 67.5 kg swine was achieved in about 125 minutes; and a 4° C. reduction in core body temperature of a 67.5 kg swine was achieved in about 175 minutes.







TABLE 2







Esophageal Cooling.










Time (min)
Rectal Temperature (° C.)














0
37.8



10
37.8



15
37.6



20
37.4



25
37.3



32
37.2



35
37



40
36.8



45
36.7



50
36.6



55
36.4



60
36.3



65
36.1



70
36



75
35.9



80
35.7



85
35.6



90
35.5



95
35.4



100
35.3



105
35.2



110
35.1



115
35



120
34.9



125
34.8



130
34.7



135
34.6



140
34.5



145
34.4



150
34.4



155
34.3



160
34.2



165
34.1



170
33.9



175
33.8



180 
33.7



185 
33.6










FIG. 11 shows a comparison of the rate of cooling achieved by a heat transfer device of the present technology as compared to the rate of cooling demonstrated in US Patent Application Publication 2004/0210281 to Dzeng et al. (now U.S. Pat. No. 7,758,623). In order to make an accurate comparison, and to properly account for the differences in mass between the two experiments, the total amount of heat extracted in each case is calculated in standard units of Joules. Using a standard specific heat capacity of water (cp=4.186 J/g C) to model the specific heat capacity of the experimental animal, the heat extracted at each time point is calculated as Q=m(ΔT)cp, where m is the mass of the experimental animal, and ΔT is the temperature difference obtained at each time point.
At the time point of one hour, the total heat extracted is 439 kJ in one hour (122 Watts) with a heat transfer device of the present technology, as compared to a total heat extraction of 260 kJ in one hour (72 Watts) achieved with the device mentioned by Dzeng et al. in US Patent Application Publication 2004/0210281 (now U.S. Pat. No. 7,758,623).
The results of the swine cooling experiment show that even in a relatively large animal, with correspondingly greater heat reservoir capacity, a significantly greater heat transfer rate is achievable with a heat transfer device of the present technology than with prior devices such as those mentioned by Dzeng et al. in US Patent Application Publication 2004/0210281 (now U.S. Pat. No. 7,758,623). From the data presented, the total heat extracted, and the consequent cooling achieved, can be seen to be significantly greater with a heat transfer device of the present technology as compared to the rate of heat transfer and cooling achieved with prior devices such as those mentioned by Dzeng et al. in US Patent Application Publication 2004/0210281 (now U.S. Pat. No. 7,758,623). Thus, it was unexpectedly and surprisingly observed that the cooling rate achieved with a heat transfer device of the present technology is significantly greater than that achieved with other devices and that the methods and devices of the present technology transfer more heat per unit time than other devices. Without wishing to be bound by any particular theory, it is thought that these unexpected findings can be attributed to, for example, one or more of the following features of the heat transfer device: the increased contact surface between the heat transfer region of the heat transfer device and the patient's anatomy; the reduction in heat transfer resistance across the device achieved by manufacturing heat transfer devices of the present technology with thinner wall thicknesses; the superior heat transfer characteristics of the materials used to construct the heat transfer devices of the present technology; and the reduction of gastric pressure through gastric ventilation.
Following cooling, the set point temperature of the heat transfer medium was switched to a warming mode (42° C.).
To further simulate the hypothermia inducing conditions of the operating room, the swine was left exposed to the ambient temperature of the room (22° C.), continuously anesthetized with inhalational anesthesia, paralyzed with a non-depolarizing paralytic to prevent shivering, and provided with a continuous flow of maintenance room temperature intravenous fluid hydration.
Data from the warming and maintenance phase of the experiment are shown in Table 3. The data in Table 3 demonstrate an initial maintenance of the swine body temperature at 33.6° C., followed by a successful safe, gradual increase in body temperature for the duration of the experiment. FIG. 12 shows the total amount of heat transferred, as calculated above, during the warming and maintenance phase of the experiment.







TABLE 3







Operative Temperature Management and Warming










Time (min) 
Rectal Temperature (° C.)














0
33.6



5
33.6



10
33.6



15
33.7



20
33.7



25
33.8



30
33.8



35
33.8



40
33.8



45
33.8



50
33.9



55
33.9



60
33.9



65
33.9



70
33.9



85
34



100
34.1



115 
34.2



130
34.3



145
34.3



160
34.3



175
34.4



190 
34.5



205 
34.5










Consequently, the data demonstrate that a heat transfer device of the present technology can maintain, and increase, body temperature while the patient is exposed to adverse hypothermic conditions of an operating room environment.
Example 3
Temperature Modulation
In an experimental model of therapeutic temperature modulation, a heat transfer device according to the present technology was utilized in an animal study as described below.
Five large swine with masses of between 60 kg and 70 kg were chosen to best represent the size and average mass of a human patient. The study utilized methods consistent with current veterinary and USDA standards, with a state-of-the-art, Association for Assessment and Accreditation of Laboratory Animal Care (AAALAC) International-accredited vivarium. Animal care and handling of was in accord with Office of Laboratory Animal Welfare guidance for humane care and use of animals and with regulations outlined in the USDA Animal Welfare Act (9 CFR Parts 1, 2 and 3) and the conditions specified in the Guide for the Care and Use of Laboratory Animals (National Academy Press, Washington D.C., 1996).
Swine were anesthetized with a pre-anesthetic dose of ketamine, then provided with anesthesia via inhalational route with isoflurane 2% after endotracheal intubation achieved with standard endotracheal intubation equipment and technique well known to those skilled in the art.
Temperature was monitored continuously via continuous rectal thermometer, intravascular thermometer, and both vaginal and/or bladder thermometer using temperature-sensing Foley catheters, all placed after anesthesia and endotracheal intubation.
A commercially available thermal water bath and circulator (Gaymar Meditherm III, MTA-7900) was utilized to provide a controlled-temperature heat transfer medium to the heat transfer device. The specific heat transfer medium utilized was distilled water. Specifications of the commercially available thermal water bath and circulator are as follows:
Size: 37′′h×14′′w×183⁄4′′d (94 cm×36 cm×46 cm)
Weight: Empty: 121 lbs. (54.9 kg), Full: 141 lbs. (64.0 kg)
Material: Aluminum shell, 16-gauge steel chassis
Flow Rate: 17 gph per minute
Power: 120 VAC, 60 Hz, 11.5 amps
Electrical Cord: 15 ft. (4.6 m) power cord (16/3 SO), hospital-grade plug
Temperature Settings: Manual: Water temperature selection range 4 to 42° C. (39.2 to 107.6° F.)
Automatic: Patient temp. selection range 30 to 41° C. (86 to 105.8° F.)
Code: UL416 and CSA C22.2, EMC meets EN60601-1-2
After successful anesthesia and endotracheal intubation of the swine, the heat transfer device was connected to the external thermal water bath and circulator which was then powered on to initiate the flow of heat exchange medium (distilled water). The heat transfer device was then lubricated with a biocompatible lubricant and introduced into the esophagus of the swine using standard esophageal intubation technique well known to those skilled in the art. No stylets or additional techniques to enhance rigidity of the heat transfer device were necessary to allow proper placement. An external measurement of the distance from oropharyngeal opening to xiphoid process served as an indicator to which the depth of the heat transfer device was inserted. Confirmation of proper depth of insertion was obtained by successful auscultation of stomach gurgling upon injection of 20 mL of air, aspiration of gastric contents through the gastric lumen of the heat transfer device, and x-ray fluoroscopy demonstrating presence of the radio-opaque stripe and tip in the stomach.
Starting from baseline temperature measured prior to preparation, swine temperature was reduced by 4° C. by setting the external chiller to run in an automatic mode, with set point that was 4° C. below the baseline temperature. At 24 hours after initiation of cooling, a rewarming protocol was initiated, in which the external heat exchanger was set to a warming mode, while swine temperature was gradually allowed to rewarm at a rate of approximately 0.5° C. per hour. Upon surpassing a goal temperature of 36° C., recovery from anesthesia was initiated, and each swine was then monitored post recovery for periods of between 3 and 14 days.
A representative plot of temperature versus time is shown in FIG. 13. Throughout the entire protocol, no evidence of thermoregulatory shivering was seen, and therefore no muscular paralysis medications were required, and no medications commonly utilized to treat shivering (such as meperidine, dexmedetomidine, midazolam, fentanyl, ondansetron, or magnesium sulfate) were required.
Existing methods to control and modify patient temperature typically demonstrate significant variation around goal temperature during treatment, with up to plus or minus 1.3° C. variance from goal temperature seen in some cases. Inadvertent increases above the goal temperature lessen the therapeutic benefit of hypothermia. Inadvertent overcooling can result in significant complications, including cardiac arrhythmias, coagulopathy, and an increased rate of infection. In contrast, devices of the present technology provided the surprising and unexpected benefit of reduced variation around the goal temperature throughout the steady-state of the treatment protocol. Variation around the goal temperature fell far below that which is demonstrated by other devices, and in fact remained for almost the entire protocol within plus or minus 0.1° C. of goal temperature.
During the cooling process, temperature measurements were performed every 15 minutes initially, and then every 30 minutes once steady state was reached. The rate of temperature reduction ranged from 0.8° C./hour to as fast as 2.4° C./hour, with an average of 1.4° C./hour. The rate of temperature reduction was as fast as 703 kJ/hour, with an average of 410 kJ/hour. Thus, it was unexpectedly and surprisingly observed that the cooling rate achieved with a heat transfer device of the present technology is greater than that achieved with many other devices and that the methods and devices of the present technology extract more heat per unit time than many other devices.
During the warming process, temperature measurements were performed every 15 minutes. As can be seen in the figure, at each 15 min. interval, the rate of temperature increase ranged from zero to as high as 1.2° C./hour, with an average of 0.39° C./hour. Thus, it was unexpectedly and surprisingly observed that the warming rate achieved with a heat transfer device of the present technology is greater than that achieved with many other devices and that the methods and devices of the present technology impart more heat per unit time than many other devices.
Specific Embodiments
The methods described herein can be illustrated by the following embodiments enumerated in the numbered sentences that follow:
1. A method for inducing systemic hypothermia comprising:
inserting a heat transfer device into an esophagus of a patient, wherein the heat transfer device includes a fluid path defined by an inflow lumen and an outflow lumen;
initiating flow of a cooling medium along the fluid path; and
circulating the medium along the fluid path for a time sufficient to induce systemic hypothermia in the patient.
2. The method of sentence 1, wherein the heat transfer device includes a discrete heat transfer region and the heat transfer region is confined to the esophagus.
3. The method of sentence 1, further comprising cooling the medium to a temperature below normothermia.
4. The method of sentence 1, further comprising maintaining the patient in a state of hypothermia for at least two hours.
5. The method of sentence 1, further comprising monitoring at least one physiological parameter of the patient.
6. The method of sentence 5, wherein the at least one physiological parameter is body temperature.
7. The method of sentence 6, further comprising maintaining the body temperature below about 34° C.
8. The method of sentence 7, further comprising maintaining the body temperature between about 32° C. to about 34° C.
The devices described herein can be illustrated by the following embodiments enumerated in the numbered sentences that follow:
1. An esophageal heat transfer device comprising:
(a) a plurality of lumens configured to provide a fluid path for flow of a heat transfer medium;
(b) a proximal end including an input port and an output port;
(c) a distal end configured for insertion into an esophagus of a patient.
2. The heat transfer device of sentence 1, further comprising a hollow tube having a distal end configured to extend into a stomach of the patient.
3. The heat transfer device of sentence 1, further comprising an anti-bacterial coating.
4. The heat transfer device of sentence 1, further comprising an expandable balloon.
The methods described herein can be illustrated by the following embodiments enumerated in the numbered sentences that follow:
1. A method for treating or preventing injury caused by an ischemic condition comprising:
inserting a heat transfer device into an esophagus of a patient, wherein the heat transfer device includes a fluid path defined by an inflow lumen and an outflow lumen;
initiating flow of a cooling medium along the fluid path; and
circulating the medium along the fluid path for a time sufficient to induce systemic hypothermia in the patient.
2. A method for treating or preventing ischemia-reperfusion injury comprising:
inserting a heat transfer device into an esophagus of a patient, wherein the heat transfer device includes a fluid path defined by an inflow lumen and an outflow lumen;
initiating flow of a cooling medium along the fluid path; and
circulating the medium along the fluid path for a time sufficient to induce systemic hypothermia in the patient.
3. A method for treating or preventing neurological injury comprising:
inserting a heat transfer device into an esophagus of a patient, wherein the heat transfer device includes a fluid path defined by an inflow lumen and an outflow lumen;
initiating flow of a cooling medium along the fluid path; and
circulating the medium along the fluid path for a time sufficient to induce systemic hypothermia in the patient.
4. The method of sentence 3, wherein the neurological injury is associated with stroke, traumatic brain injury, spinal cord injury, subarachnoid hemorrhage, out-of-hospital cardiopulmonary arrest, hepatic encephalopathy, perinatal asphyxia, hypoxic-anoxic encephalopathy, infantile viral encephalopathy, near-drowning, anoxic brain injury, traumatic head injury, traumatic cardiac arrest, newborn hypoxic-ischemic encephalopathy, hepatic encephalopathy, bacterial meningitis, cardiac failure, post-operative tachycardia, or acute respiratory distress syndrome.
5. The method of sentence 4, wherein the stroke is ischemic stroke.
6. A method for treating or preventing cardiac injury comprising:
inserting a heat transfer device into an esophagus of a patient, wherein the heat transfer device includes a fluid path defined by an inflow lumen and an outflow lumen;
initiating flow of a cooling medium along the fluid path; and
circulating the medium along the fluid path for a time sufficient to induce systemic hypothermia in the patient.
7. A method for treating myocardial infarction comprising:
inducing mild therapeutic hypothermia.
8. A method for treating stroke comprising:
inducing mild therapeutic hypothermia.
9. A method for treating traumatic brain injury comprising:
inducing mild therapeutic hypothermia.
10. A method for treating Acute Respiratory Distress Syndrome comprising:
inducing mild therapeutic hypothermia.
11. The method of any one of sentences 7-10, wherein the hypothermia is systemic hypothermia.
12. The method of any one of sentences 7-10, wherein the hypothermia is induced via esophageal cooling.
13. The method of any one of sentences 7-10, further comprising maintaining the patient in a state of hypothermia for at least two hours.
14. The method of sentence 13, further comprising maintaining the patient in a state of hypothermia for at least twenty-four hours.
15. The method of sentence 14, further comprising maintaining the patient in a state of hypothermia for at least seventy-two hours.
16. The method of any one of sentences 7-10, further comprising monitoring at least one physiological parameter of the patient.
17. The method of sentence 16, wherein the at least one physiological parameter is body temperature.
18. The method of sentence 17, further comprising maintaining the body temperature below about 34° C.
19. The method of sentence 18, further comprising maintaining the body temperature between about 32° C. to about 34° C.
20. The method of sentence 12, further comprising:
inserting a heat transfer device into an esophagus of a patient, wherein the heat transfer device includes a fluid path defined by an inflow lumen and an outflow lumen;
initiating flow of a cooling medium along the fluid path; and
circulating the medium along the fluid path for a time sufficient to induce systemic hypothermia in the patient.
21. A method for treating cardiac arrest comprising:
inducing systemic hypothermia via esophageal cooling.
22. The method of sentence 21, further comprising:
inserting a heat transfer device into an esophagus of a patient, wherein the heat transfer device includes a fluid path defined by an inflow lumen and an outflow lumen;
initiating flow of a cooling medium along the fluid path; and
circulating the medium along the fluid path for a time sufficient to induce systemic hypothermia in the patient.
The methods and devices described herein can be illustrated by the following embodiments enumerated in the numbered sentences that follow:
1. A device for cooling or warming at least one portion of a patient's body, comprising:
a heat transfer device including a proximal end, a distal end, and at least one flexible tube extending therebetween;
the proximal end including a heat transfer medium input port and a heat transfer medium output port;
the distal end configured for insertion into an orifice of a patient;
the at least one flexible tube defining an inflow lumen and an outflow lumen;
the lumens configured to provide a fluid path for flow of a heat transfer medium;
a supply line connected to the input port; and
a return line connected to the output port.
2. The device of sentence 1, wherein the heat transfer medium is a cooling medium.
3. A method of using the device of sentence 2 to treat or prevent injury caused by an ischemic condition comprising:
inserting the distal end of the heat transfer device nasally or orally;
advancing the distal end into an esophagus;
initiating flow of a cooling medium along the fluid path; and
circulating the medium along the fluid path for a time sufficient to induce systemic hypothermia in the patient.
4. A method of using the device of sentence 2 to treat or prevent ischemia-reperfusion injury comprising:
inserting the distal end of the heat transfer device nasally or orally;
advancing the distal end into an esophagus;
initiating flow of a cooling medium along the fluid path; and
circulating the medium along the fluid path for a time sufficient to induce systemic hypothermia in the patient.
5. A method of using the device of sentence 2 to treat or prevent neurological injury comprising:
inserting the distal end of the heat transfer device nasally or orally;
advancing the distal end into an esophagus;
initiating flow of a cooling medium along the fluid path; and
circulating the medium along the fluid path for a time sufficient to induce systemic hypothermia in the patient.
6. A method of using the device of sentence 2 to treat or prevent cardiac injury comprising:
inserting the distal end of the heat transfer device nasally or orally;
advancing the distal end into an esophagus;
initiating flow of a cooling medium along the fluid path; and
circulating the medium along the fluid path for a time sufficient to induce systemic hypothermia in the patient.
7. A method of using the device of sentence 2 to treat myocardial infarction comprising:
inserting the distal end of the heat transfer device nasally or orally;
advancing the distal end into an esophagus;
initiating flow of a cooling medium along the fluid path; and
circulating the medium along the fluid path for a time sufficient to induce systemic hypothermia in the patient.
8. A method of using the device of sentence 2 to treat stroke comprising:
inserting the distal end of the heat transfer device nasally or orally;
advancing the distal end into an esophagus;
initiating flow of a cooling medium along the fluid path; and
circulating the medium along the fluid path for a time sufficient to induce systemic hypothermia in the patient.
9. A method of using the device of sentence 2 to treat traumatic brain injury comprising:
inserting the distal end of the heat transfer device nasally or orally;
advancing the distal end into an esophagus;
initiating flow of a cooling medium along the fluid path; and
circulating the medium along the fluid path for a time sufficient to induce systemic hypothermia in the patient.
10. A method of using the device of sentence 2 to treat Acute Respiratory Distress Syndrome comprising:
inserting the distal end of the heat transfer device nasally or orally;
advancing the distal end into an esophagus;
initiating flow of a cooling medium along the fluid path; and
circulating the medium along the fluid path for a time sufficient to induce systemic hypothermia in the patient.
11. The method of any one of sentences 3-10, further comprising cooling the medium to a temperature below normothermia.
12. The method of any one of sentences 3-10, further comprising maintaining the patient in a state of hypothermia for at least two hours.
13. The method of sentence 12, further comprising maintaining the patient in a state of hypothermia for at least twenty-four hours.
14. The method of sentence 13, further comprising maintaining the patient in a state of hypothermia for at least seventy-two hours.
15. The method of any one of sentences 3-10, further comprising monitoring at least one physiological parameter of the patient.
16. The method of sentence 15, wherein the at least one physiological parameter is body temperature.
17. The method of sentence 16, further comprising maintaining the body temperature below about 34° C.
18. The method of sentence 17, further comprising maintaining the body temperature between about 32° C. to about 34° C.
The methods described herein can be illustrated by the following embodiments enumerated in the numbered sentences that follow:
1. A method for controlling core body temperature in a patient comprising:
inserting a heat transfer device into an esophagus of a patient, wherein the heat transfer device includes a fluid path defined by an inflow lumen and an outflow lumen;
initiating flow of a heat transfer medium along the fluid path; and
circulating the medium along the fluid path for a time sufficient to control core body temperature in the patient.
2. The method of sentence 1, wherein the heat transfer device includes a discrete heat transfer region and the heat transfer region is confined to the esophagus.
3. The method of sentence 1, further comprising cooling the medium to a temperature below normothermia.
4. The method of sentence 1, further comprising warming the medium to a temperature above normothermia.
5. The method of sentence 1, further comprising maintaining the patient in a state of hypothermia for at least two hours.
6. The method of sentence 1, further comprising maintaining the patient at normothermia for at least two hours.
7. The method of sentence 1, further comprising monitoring at least one physiological parameter of the patient.
8. The method of sentence 7, wherein the at least one physiological parameter is body temperature.
9. The method of sentence 1, further comprising maintaining the body temperature below about 34° C.
10. The method of sentence 1, further comprising maintaining the body temperature between about 32° C. to about 34° C.
11. The method of sentence 1, further comprising maintaining the body temperature at about 37° C.
The methods described herein can be illustrated by the following embodiments enumerated in the numbered sentences that follow:
1. A method for operative temperature management comprising:
inserting a heat transfer device into an esophagus of a patient, wherein the heat transfer device includes a fluid path defined by an inflow lumen and an outflow lumen;
initiating flow of a heat transfer medium along the fluid path; and
circulating the medium along the fluid path for a time sufficient to manage core body temperature in the patient.
2. The method of sentence 1, further comprising maintaining the patient in a state of hypothermia for at least two hours.
3. The method of sentence 1, further comprising maintaining the body temperature below about 34° C.
4. The method of sentence 1, further comprising maintaining the body temperature between about 32° C. to about 34° C.
5. The method of sentence 1, further comprising maintaining the patient in a state of normothermia for at least two hours.
6. The method of sentence 1, further comprising maintaining the body temperature at about 37° C.
7. The method of sentence 1, further comprising monitoring at least one physiological parameter of the patient.
8. The method of sentence 7, wherein the at least one physiological parameter is body temperature.
The devices described herein can be illustrated by the following embodiments enumerated in the numbered sentences that follow:
1. An esophageal heat transfer device comprising:

    
    
        (a) a plurality of lumens configured to provide a fluid path for flow of a heat transfer medium;
        (b) a heat transfer region configured for contacting esophageal epithelium of a patient;
        (c) a proximal end including an input port and an output port;
        (d) a distal end configured for insertion into an esophagus of a patient.
    
    


2. The heat transfer device of sentence 1, further comprising a hollow tube having a distal end configured to extend into a stomach of the patient.
3. The heat transfer device of sentence 1, wherein the heat transfer region is capable of contacting substantially all of the esophageal epithelium.
4. The heat transfer device of sentence 1, wherein the heat transfer region comprises a semi-rigid material.
5. The heat transfer device of sentence 1, wherein the device is capable of cooling at a rate of about 1.2° C./hr to about 1.8° C./hr.
6. The heat transfer device of sentence 1, wherein the device is capable of cooling a mass at a rate of about 350 kJ/hr to about 530 kJ/hr.
7. The heat transfer device of sentence 6, wherein the device is capable of cooling a mass at a rate of about 430 kJ/hr.
8. The heat transfer device of sentence 1, wherein the device includes a heat transfer region with a surface area of at least about 100 cm2.
9. The heat transfer device of sentence 8, wherein the heat transfer region has a surface area of about 140 cm2.
The devices and systems described herein can be illustrated by the following embodiments enumerated in the numbered sentences that follow:
1. A system for cooling or warming at least one portion of a patient's body, comprising:
a heat transfer device including a proximal end, a distal end, and at least one semi-rigid tube extending therebetween;

    
    
        the proximal end including a heat transfer medium input port and a heat transfer medium output port;
        the distal end configured for insertion into an orifice of a patient;
        the at least one semi-rigid tube defining an inflow lumen and an outflow lumen;
        the lumens configured to provide a fluid path for flow of a heat transfer medium;
    
    


a supply line connected to the input port; and
a return line connected to the output port.
2. The system of sentence 1, wherein the orifice is an esophageal lumen.
3. The system of sentence 2, wherein the heat transfer device comprises a heat transfer region capable of contacting substantially all of the esophageal epithelium.
4. The system of sentence 1, further comprising a hollow tube having a distal end configured to extend into a stomach of the patient.
5. The heat transfer device of sentence 1, wherein the device is capable of cooling at a rate of about 1.2° C./hr to about 1.8° C./hr.
6. The system of sentence 1, wherein the device is capable of cooling a mass at a rate of about 350 kJ/hr to about 530 kJ/hr.
7. The system of sentence 6, wherein the device is capable of cooling a mass at a rate of about 430 kJ/hr.
8. The system of sentence 1, wherein the device includes a heat transfer region with a surface area of at least about 100 cm2.
9. The system of sentence 8, wherein the heat transfer region has a surface area of about 140 cm2.
The devices and systems described herein can be illustrated by the following embodiments enumerated in the numbered sentences that follow:
1. A system for controlling core body temperature of a subject, comprising:
a heat transfer tube insertable within the esophagus of the subject, wherein the tube is configured to contact the epithelial lining of the esophagus;
an external heat exchanger containing a heat transfer fluid;
a pump for flowing the heat transfer fluid through a circuit within the heat transfer tube;
a heat transfer element in contact with the external heat exchanger; and
a sensor for detecting a parameter and generating a signal representative of the parameter, wherein the signal is transmitted to a microprocessor to control (i) the flow heat transfer fluid within the circuit or (ii) the temperature of the heat transfer fluid.
2. The system of sentence 1, wherein the sensor is a temperature sensor positioned distal to the heat transfer tube and configured to generate a signal representing the core body temperature of the subject.
3. The system of sentence 2, wherein the microprocessor receives a target temperature input and responds to the signal from the temperature sensor with a proportional integrated differential response to control the rate at which the subject approaches the target temperature.
4. The system of sentence 1, wherein the sensor is a bubble detector and configured to generate a signal representing the presence of air in the circuit.
5. The system of sentence 1, wherein the heat transfer tube comprises a heat transfer region capable of contacting substantially all of the esophageal epithelium.
6. The system of sentence 1, further comprising a hollow tube having a distal end configured to extend into a stomach of the patient.
7. The system of sentence 1, wherein the device is capable of cooling at a rate of about 1.2° C./hr to about 1.8° C./hr.
8. The system of sentence 1, wherein the device is capable of cooling a mass at a rate of about 350 kJ/hr to about 530 kJ/hr.
9. The system of sentence 1, wherein the device is capable of cooling a mass at a rate of about 430 kJ/hr.
10. The system of sentence 1, wherein the device includes a heat transfer region with a surface area of at least about 100 cm2.
11. The system of sentence 10, wherein the heat transfer region has a surface area of about 140 cm2.
The presently described technology is now described in such full, clear, concise and exact terms as to enable any person skilled in the art to which it pertains, to practice the same. It is to be understood that the foregoing describes preferred embodiments of the technology and that modifications may be made therein without departing from the spirit or scope of the invention as set forth in the appended sentences.

## Claims

1. A system for controlling core body temperature of a patient comprising:
a heat transfer device having
(a) an input port capable of receiving a heat transfer medium from an external source;
(b) a lumen connected to the input port; and
(c) an inflatable heat transfer region configured for contacting the patient's esophageal epithelium upon inflation, wherein the lumen provides a fluid path for flow of the heat transfer medium to the inflatable heat transfer region

a microprocessor coupled to the external source, wherein the microprocessor regulates the flow of the heat transfer medium to the heat transfer region to inflate the heat transfer region and subsequently deflate the heat transfer region to permit gastric ventilation.

2. The system of claim 1, wherein the microprocessor is capable of receiving a target pressure determined by a health care professional.

3. The system of claim 1, wherein the microprocessor is capable of decreasing the flow of the heat transfer medium to the heat transfer region.

4. The system of claim 1, wherein the microprocessor is capable of increasing the flow of the heat transfer medium to the heat transfer region.

5. The system of claim 1, wherein the microprocessor is capable of periodically increasing or decreasing the flow of the heat transfer medium to the heat transfer region.

6. The system of claim 1, further comprising a pressure sensor for detecting gastric pressure and generating a signal representative of gastric pressure.

7. The system of claim 6, wherein the pressure sensor is capable of sending the signal to the microprocessor.

8. The system of claim 6, wherein the microprocessor is capable of responding to the signal from the pressure sensor with a proportional integrated differential response to control the flow of the heat transfer medium to the heat transfer region.

9. A method for reducing core body temperature in a patient, comprising the steps of:
nasally or orally inserting an esophageal heat transfer device into the patient; wherein the heat transfer device includes:
(a) an input port capable of receiving a heat transfer medium from an external source;
(b) a lumen connected to the input port; and
(c) an inflatable heat transfer region configured for contacting a patient's esophageal epithelium upon inflation, wherein the lumen provides a fluid path for flow of the heat transfer medium to the inflatable heat transfer region

advancing the inflatable heat transfer region of the heat transfer device into the patient's esophagus;
initiating flow of a heat transfer medium along the fluid path to inflate the inflatable heat transfer region;
deflating the inflatable heat transfer region to permit gastric ventilation; and
re-inflating the inflatable heat transfer region.

10. The method of claim 9, further comprising the step of monitoring gastric pressure.

11. The method of claim 9, wherein information representing gastric pressure is communicated to a microprocessor capable of inflating or deflating the inflatable heat transfer region.

12. The method of claim 11, wherein the microprocessor is capable of receiving a target pressure determined by a health care professional.

13. The method of claim 12, wherein the microprocessor is capable of responding to the signal from the pressure sensor with a proportional integrated differential response to control the flow of the heat transfer medium to the heat transfer region.

14. The method of claim 9, further comprising the step of maintaining the core body temperature of the patient below about 34° C. for at least two hours.

15. The method of claim 9, further comprising the step of maintaining the core body temperature of the patient below about 34° C. for at least twenty four hours.

16. The method of claim 9, further comprising the step of maintaining the core body temperature of the patient below about 34° C. for at least seventy two hours.

17. A method for reducing core body temperature in a patient, comprising the steps of:
nasally or orally inserting an esophageal heat transfer device into the patient; wherein the heat transfer device includes one or more lumens configured to provide a fluid path for flow of a heat transfer medium to an inflatable heat transfer region configured for contacting a patient's esophageal epithelium upon inflation;
advancing the inflatable heat transfer region of the heat transfer device into the patient's esophagus;
initiating flow of a heat transfer medium along the fluid path to inflate the inflatable heat transfer region; wherein gastric access is maintained upon inflation of the inflatable heat transfer region; and
nasally or orally inserting a gastric tube into the patient.

18. The method of claim 17, wherein the inflatable heat transfer region takes on a substantially helical shape upon inflation.

19. The method of claim 17, wherein the inflatable heat transfer region takes on a substantially hourglass shape upon inflation.