出典(authority):フリー百科事典『ウィキペディア（Wikipedia）』「2015/09/18 22:34:44」(JST)
| Artificial cardiac pacemaker | |
|---|---|
| Intervention | |
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An artificial pacemaker with electrode for transvenous insertion. The body of the device is about 3–4 cm long, the electrode measures between 50 and 60 cm (20 to 24 inches).
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| ICD-9 | 37.8; 00.50, 00.53 |
| MeSH | D010138 |
| MedlinePlus | 007369 |
| eMedicine | 1971142 |
A pacemaker (or artificial pacemaker, so as not to be confused with the heart's natural pacemaker) is a medical device which uses electrical impulses, delivered by electrodes contracting the heart muscles, to regulate the beating of the heart.
The primary purpose of a pacemaker is to maintain an adequate heart rate, either because the heart's natural pacemaker is not fast enough, or because there is a block in the heart's electrical conduction system. Modern pacemakers are externally programmable and allow a cardiologist to select the optimum pacing modes for individual patients. Some combine a pacemaker and defibrillator in a single implantable device. Others have multiple electrodes stimulating differing positions within the heart to improve synchronisation of the lower chambers (ventricles) of the heart.
In 1889, John Alexander MacWilliam reported in the British Medical Journal (BMJ) of his experiments in which application of an electrical impulse to the human heart in asystole caused a ventricular contraction and that a heart rhythm of 60–70 beats per minute could be evoked by impulses applied at spacings equal to 60–70/minute.[1]
In 1926, Dr Mark C Lidwill of the Royal Prince Alfred Hospital of Sydney, supported by physicist Edgar H. Booth of the University of Sydney, devised a portable apparatus which "plugged into a lighting point" and in which "One pole was applied to a skin pad soaked in strong salt solution" while the other pole "consisted of a needle insulated except at its point, and was plunged into the appropriate cardiac chamber". "The pacemaker rate was variable from about 80 to 120 pulses per minute, and likewise the voltage variable from 1.5 to 120 volts". In 1928, the apparatus was used to revive a stillborn infant at Crown Street Women's Hospital, Sydney whose heart continued "to beat on its own accord", "at the end of 10 minutes" of stimulation.[2][3]
In 1932, American physiologist Albert Hyman, working independently, described an electro-mechanical instrument of his own, powered by a spring-wound hand-cranked motor. Hyman himself referred to his invention as an "artificial pacemaker", the term continuing in use to this day.[4][5]
An apparent hiatus in publication of research conducted between the early 1930s and World War II may be attributed to the public perception of interfering with nature by "reviving the dead". For example, "Hyman did not publish data on the use of his pacemaker in humans because of adverse publicity, both among his fellow physicians, and due to newspaper reporting at the time. Lidwell may have been aware of this and did not proceed with his experiments in humans".[3]
An external pacemaker was designed and built by the Canadian electrical engineer John Hopps in 1950 based upon observations by cardio-thoracic surgeon Wilfred Gordon Bigelow at Toronto General Hospital. A substantial external device using vacuum tube technology to provide transcutaneous pacing, it was somewhat crude and painful to the patient in use and, being powered from an AC wall socket, carried a potential hazard of electrocution of the patient by inducing ventricular fibrillation.
A number of innovators, including Paul Zoll, made smaller but still bulky transcutaneous pacing devices in the following years using a large rechargeable battery as the power supply.[6]
In 1957, William L. Weirich published the results of research performed at the University of Minnesota. These studies demonstrated the restoration of heart rate, cardiac output and mean aortic pressures in animal subjects with complete heart block through the use of a myocardial electrode.[7]
In 1958 Colombian doctor Alberto Vejarano Laverde and Colombian electrical engineer Jorge Reynolds Pombo constructed an external pacemaker, similar to those of Hopps and Zoll, weighing 45 kg and powered by a 12 volt car lead acid battery, but connected to electrodes attached to the heart. This apparatus was successfully used to sustain a 70-year-old priest, Gerardo Florez.
The development of the silicon transistor and its first commercial availability in 1956 was the pivotal event which led to rapid development of practical cardiac pacemaking.
In 1958, engineer Earl Bakken of Minneapolis, Minnesota, produced the first wearable external pacemaker for a patient of C. Walton Lillehei. This transistorized pacemaker, housed in a small plastic box, had controls to permit adjustment of pacing heart rate and output voltage and was connected to electrode leads which passed through the skin of the patient to terminate in electrodes attached to the surface of the myocardium of the heart.
One of the earliest patients to receive this Lucas pacemaker device was a woman in her early 30s in an operation carried out in 1964 at the Radcliffe Infirmary in Oxford by cardiac surgeon Dr Alf Gunning from South Africa and later Professor Gunning[8][9] who was a student of Dr Christiaan Barnard. This pioneering operation was carried out under the guidance of cardiac consultant Dr Peter Sleight at the Radcliffe Infirmary in Oxford and his cardiac research team at St George's Hospital in London. Dr Sleight later became Professor of Cardiovascular Medicine at Oxford University.[10][11]
The first clinical implantation into a human of a fully implantable pacemaker was in 1958 at the Karolinska Institute in Solna, Sweden, using a pacemaker designed by Rune Elmqvist and surgeon Åke Senning, connected to electrodes attached to the myocardium of the heart by thoracotomy. The device failed after three hours. A second device was then implanted which lasted for two days. The world's first implantable pacemaker patient, Arne Larsson, went on to receive 26 different pacemakers during his lifetime. He died in 2001, at the age of 86, outliving the inventor as well as the surgeon.[12]
In 1959, temporary transvenous pacing was first demonstrated by Seymore Furman and John Schwedel, whereby the catheter electrode was inserted via the patient's basilic vein.[13]
In February 1960, an improved version of the Swedish Elmqvist design was implanted in Montevideo, Uruguay in the Casmu 1 Hospital by Doctors Orestes Fiandra and Roberto Rubio. That device lasted until the patient died of other ailments, nine months later. The early Swedish-designed devices used rechargeable batteries, which were charged by an induction coil from the outside.It was the first pacemaker implanted in America.
Implantable pacemakers constructed by engineer Wilson Greatbatch entered use in humans from April 1960 following extensive animal testing. The Greatbatch innovation varied from the earlier Swedish devices in using primary cells (mercury battery) as the energy source. The first patient lived for a further 18 months.
The first use of transvenous pacing in conjunction with an implanted pacemaker was by Parsonnet in the USA,[14][15][16] Lagergren in Sweden[17][18] and Jean-Jaques Welti in France[19] in 1962–63. The transvenous, or pervenous, procedure involved incision of a vein into which was inserted the catheter electrode lead under fluoroscopic guidance, until it was lodged within the trabeculae of the right ventricle. This method was to become the method of choice by the mid-1960s.
Cardiothoracic Surgeon Leon Abrams, and Medical Engineer Ray Lightwood, developed and implanted the first patient controlled variable rate heart pacemaker in 1960 at Birmingham University. The first implant took place in March 1960, with two further implants the following month. These three patients made good recoveries and returned to a high quality of life. By 1966, 56 patients had undergone implantation with one surviving for over 5½ years.[20][21]
The preceding implantable devices all suffered from the unreliability and short lifetime of the available primary cell technology which was mainly that of the mercury battery. In the late 1960s, several companies, including ARCO in the USA, developed isotope-powered pacemakers, but this development was overtaken by the development in 1971 of the lithium-iodide cell by Wilson Greatbatch. Lithium-iodide or lithium anode cells became the standard for future pacemaker designs.
A further impediment to reliability of the early devices was the diffusion of water vapour from the body fluids through the epoxy resin encapsulation affecting the electronic circuitry. This phenomenon was overcome by encasing the pacemaker generator in a hermetically sealed metal case, initially by Telectronics of Australia in 1969 followed by Cardiac Pacemakers Inc of Minneapolis in 1972. This technology, using titanium as the encasing metal, became the standard by the mid-1970s.
In July 9 of 1974, Manuel A. Villafaña and Anthony Adducci founders of Cardiac Pacemakers, Inc. (Guidant) in St. Paul Minneosta, manufactured the world's first pacemaker with a lithium anode and a lithium-iodide electrolyte solid-state battery.[23][24]
Others who contributed significantly to the technological development of the pacemaker in the pioneering years were Bob Anderson of Medtronic Minneapolis, J.G (Geoffrey) Davies of St George's Hospital London, Barouh Berkovits and Sheldon Thaler of American Optical, Geoffrey Wickham of Telectronics Australia, Walter Keller of Cordis Corp. of Miami, Hans Thornander who joined previously mentioned Rune Elmquist of Elema-Schonander in Sweden, Janwillem van den Berg of Holland and Anthony Adducci of Cardiac Pacemakers Inc.[22]
In 2013, multiple firms announced devices that could be inserted via a leg catheter rather than invasive surgery. The devices are roughly the size and shape of a multivitamin, much smaller than the size of a traditional pacemaker. Once implanted, the device’s prongs contact the muscle and stabilize heartbeats. Engineers and scientists are currently working on this type of device.[25] In November 2014 a patient, Bill Pike of Fairbanks, Alaska, received a Medtronic Micra pacemaker in Providence St Vincent Hospital in Portland Oregon. Doctor D. Randolph Jones, MD was the EP doctor. In 2014 also St. Jude Medical Inc. announced the first enrollments in the company’s leadless Pacemaker Observational Study evaluating the Nanostim leadless pacing technology. The Nanostim pacemaker received CE marking in 2013. The post-approval implants have occurred in Europe.[26] The European study was recently stopped, after there were reports of six perforations that led to two patient deaths. After investigators St Jude Medical has since restarted the study.[27] But in the United States this therapy is still not approved by the FDA.[28] While the St Jude Nanostim and the Medtronic Micra are just single-chamber pacemakers it is anticipated that leadless dual-chamber pacing for patients with atrioventricular block will become possible with further development.[29]
Percussive pacing, also known as transthoracic mechanical pacing, is the use of the closed fist, usually on the left lower edge of the sternum over the right ventricle in the vena cava, striking from a distance of 20 – 30 cm to induce a ventricular beat (the British Journal of Anaesthesia suggests this must be done to raise the ventricular pressure to 10–15 mmHg to induce electrical activity). This is an old procedure used only as a life saving means until an electrical pacemaker is brought to the patient.[30]
Transcutaneous pacing (TCP), also called external pacing, is recommended for the initial stabilization of hemodynamically significant bradycardias of all types. The procedure is performed by placing two pacing pads on the patient's chest, either in the anterior/lateral position or the anterior/posterior position. The rescuer selects the pacing rate, and gradually increases the pacing current (measured in mA) until electrical capture (characterized by a wide QRS complex with a tall, broad T wave on the ECG) is achieved, with a corresponding pulse. Pacing artifact on the ECG and severe muscle twitching may make this determination difficult. External pacing should not be relied upon for an extended period of time. It is an emergency procedure that acts as a bridge until transvenous pacing or other therapies can be applied.
Temporary epicardial pacing is used during open heart surgery should the surgical procedure create atrio-ventricular block. The electrodes are placed in contact with the outer wall of the ventricle (epicardium) to maintain satisfactory cardiac output until a temporary transvenous electrode has been inserted.
Transvenous pacing, when used for temporary pacing, is an alternative to transcutaneous pacing. A pacemaker wire is placed into a vein, under sterile conditions, and then passed into either the right atrium or right ventricle. The pacing wire is then connected to an external pacemaker outside the body. Transvenous pacing is often used as a bridge to permanent pacemaker placement. It can be kept in place until a permanent pacemaker is implanted or until there is no longer a need for a pacemaker and then it is removed.
Permanent pacing with an implantable pacemaker involves transvenous placement of one or more pacing electrodes within a chamber, or chambers, of the heart, while the pacemaker is implanted inside the skin under the clavicle. The procedure is performed by incision of a suitable vein into which the electrode lead is inserted and passed along the vein, through the valve of the heart, until positioned in the chamber. The procedure is facilitated by fluoroscopy which enables the physician to view the passage of the electrode lead. After satisfactory lodgement of the electrode is confirmed, the opposite end of the electrode lead is connected to the pacemaker generator.
There are three basic types of permanent pacemakers, classified according to the number of chambers involved and their basic operating mechanism:[31]
Modern pacemakers usually have multiple functions. The most basic form monitors the heart's native electrical rhythm. When the pacemaker does not detect a heartbeat within a normal beat-to-beat time period, it will stimulate the ventricle of the heart with a short low voltage pulse. This sensing and stimulating activity continues on a beat by beat basis.
The more complex forms include the ability to sense and/or stimulate both the atrial and ventricular chambers.
| I | II | III | IV | V |
|---|---|---|---|---|
| Chamber(s) paced | Chamber(s) sensed | Response to sensing | Rate modulation | Multisite pacing |
| O = None | O = None | O = None | O = None | O = None |
| A = Atrium | A = Atrium | T = Triggered | R = Rate modulation | A = Atrium |
| V = Ventricle | V = Ventricle | I = Inhibited | V = Ventricle | |
| D = Dual (A+V) | D = Dual (A+V) | D = Dual (T+I) | D = Dual (A+V) |
From this the basic ventricular "on demand" pacing mode is VVI or with automatic rate adjustment for exercise VVIR – this mode is suitable when no synchronization with the atrial beat is required, as in atrial fibrillation. The equivalent atrial pacing mode is AAI or AAIR which is the mode of choice when atrioventricular conduction is intact but the natural pacemaker the sinoatrial node is unreliable – sinus node disease (SND) or sick sinus syndrome. Where the problem is atrioventricular block (AVB) the pacemaker is required to detect (sense) the atrial beat and after a normal delay (0.1–0.2 seconds) trigger a ventricular beat, unless it has already happened – this is VDD mode and can be achieved with a single pacing lead with electrodes in the right atrium (to sense) and ventricle (to sense and pace). These modes AAIR and VDD are unusual in the US but widely used in Latin America and Europe.[35][36] The DDDR mode is most commonly used as it covers all the options though the pacemakers require separate atrial and ventricular leads and are more complex, requiring careful programming of their functions for optimal results.
Cardiac resynchronization therapy (CRT) is used for people with heart failure in whom the left and right ventricles do not contract simultaneously (ventricular dyssynchrony), which occurs in approximately 25–50% of heart failure patients. To achieve CRT, a biventricular pacemaker (BVP) is used, which can pace both the septal and lateral walls of the left ventricle. By pacing both sides of the left ventricle, the pacemaker can resynchronize the ventricular contractions.
CRT devices have at least two leads, one passing through the vena cava and the right atrium into the right ventricle to stimulate the septum, and another passing through the vena cava and the right atrium and inserted through the coronary sinus to pace the epicardial wall of the left ventricle. Often, for patients in normal sinus rhythm, there is also a lead in the right atrium to facilitate synchrony with the atrial contraction. Thus, timing between the atrial and ventricular contractions, as well as between the septal and lateral walls of the left ventricle can be adjusted to achieve optimal cardiac function.
CRT devices have been shown to reduce mortality and improve quality of life in patients with heart failure symptoms; a LV ejection fraction less than or equal to 35% and QRS duration on EKG of 120 ms or greater.[37][38]
Biventricular pacing alone is referred to as CRT-P (for pacing). For selected patients at risk of arrhythmias, CRT can be combined with an implantable cardioverter-defibrillator (ICD): such devices, known as CRT-D (for defibrillation), also provide effective protection against life-threatening arrhythmias.[39]
A major step forward in pacemaker function has been to attempt to mimic nature by utilizing various inputs to produce a rate-responsive pacemaker using parameters such as the QT interval, pO2 – pCO2 (dissolved oxygen or carbon dioxide levels) in the arterial-venous system, physical activity as determined by an accelerometer, body temperature, ATP levels, adrenaline, etc. Instead of producing a static, predetermined heart rate, or intermittent control, such a pacemaker, a 'Dynamic Pacemaker', could compensate for both actual respiratory loading and potentially anticipated respiratory loading. The first dynamic pacemaker was invented by Anthony Rickards of the National Heart Hospital, London, UK, in 1982.[40]
Dynamic pacemaking technology could also be applied to future artificial hearts. Advances in transitional tissue welding would support this and other artificial organ/joint/tissue replacement efforts. Stem cells may or may not be of interest to transitional tissue welding.[citation needed]
Many advancements have been made to improve the control of the pacemaker once implanted. Many of these have been made possible by the transition to microprocessor controlled pacemakers. Pacemakers that control not only the ventricles but the atria as well have become common. Pacemakers that control both the atria and ventricles are called dual-chamber pacemakers. Although these dual-chamber models are usually more expensive, timing the contractions of the atria to precede that of the ventricles improves the pumping efficiency of the heart and can be useful in congestive heart failure.
Rate responsive pacing allows the device to sense the physical activity of the patient and respond appropriately by increasing or decreasing the base pacing rate via rate response algorithms.
The DAVID trials[41] have shown that unnecessary pacing of the right ventricle can exacerbate heart failure and increases the incidence of atrial fibrillation. The newer dual chamber devices can keep the amount of right ventricle pacing to a minimum and thus prevent worsening of the heart disease.
A pacemaker is typically inserted into the patient through a simple surgery using either local anesthetic or a general anesthetic. The patient may be given a drug for relaxation before the surgery as well. An antibiotic is typically administered to prevent infection.[42] In most cases the pacemaker is inserted in the left shoulder area where an incision is made below the collar bone creating a small pocket where the pacemaker is actually housed in the patient's body. The lead or leads (the number of leads varies depending on the type of pacemaker) are fed into the heart through a large vein using a fluoroscope to monitor the progress of lead insertion. The Right Ventricular lead would be positioned away from the apex (tip) of the right ventricle and up on the interventricular septum, below the outflow tract, to prevent deterioration of the strength of the heart. The actual surgery may take about 30 to 90 minutes.
Following surgery the patient should exercise reasonable care about the wound as it heals. There is a follow-up session during which the pacemaker is checked using a "programmer" that can communicate with the device and allows a health care professional to evaluate the system's integrity and determine the settings such as pacing voltage output. The patient should have the strength of his or her heart analyzed frequently with echocardiography, every 1 or 2 years, to make sure the that placement of the right ventricular lead has not led to weakening of the left ventricle.
The patient may want to consider some basic preparation before the surgery. The most basic preparation is that people who have body hair on the chest may want to remove the hair by clipping just prior to surgery or using a depilatory agent (preoperative shaving has been on the decline as it can cause skin breakage and increase infection risk of any surgical procedure) as the surgery will involve bandages and monitoring equipment to be affixed to the body.
Since a pacemaker uses batteries, the device itself will need replacement as the batteries lose power. Device replacement is usually a simpler procedure than the original insertion as it does not normally require leads to be implanted. The typical replacement requires a surgery in which an incision is made to remove the existing device, the leads are removed from the existing device, the leads are attached to the new device, and the new device is inserted into the patient's body replacing the previous device.
International pacemaker patient identification cards carry information such as patient data (among others, symptom primary, ECG, aetiology), pacemaker center (doctor, hospital), IPG (rate, mode, date of implantation, manufacturer, type) and lead type.[43][44]
Once the pacemaker is implanted, it is periodically checked to ensure the device is operational and performing appropriately. Depending on the frequency set by the following physician, the device can be checked as often as is necessary. Routine pacemaker checks are typically done in-office every six (6) months, though will vary depending upon patient/device status and remote monitoring availability.
At the time of in-office follow-up, the device will be interrogated to perform diagnostic testing. These tests include:
As modern pacemakers are "on-demand", meaning that they only pace when necessary, device longevity is affected by how much it is utilized. Other factors affecting device longevity include programmed output and algorithms (features) causing a higher level of current drain from the battery.
An additional aspect of the in-office check is to examine any events that were stored since the last follow-up. These are typically stored based on specific criteria set by the physician and specific to the patient. Some devices have the availability to display intracardiac electrograms of the onset of the event as well as the event itself. This is especially helpful in diagnosing the cause or origin of the event and making any necessary programming changes.
A patient's lifestyle is usually not modified to any great degree after insertion of a pacemaker. There are a few activities that are unwise such as full contact sports and activities that involve intense magnetic fields.
The pacemaker patient may find that some types of everyday actions need to be modified. For instance, the shoulder harness of a vehicle seatbelt may be uncomfortable if the harness should fall across the pacemaker insertion site.
Any kind of an activity that involves intense magnetic fields should be avoided. This includes activities such as arc welding possibly, with certain types of equipment,[45] or maintaining heavy equipment that may generate intense magnetic fields (such as a magnetic resonance imaging (MRI) machine).
However, in February 2011 the FDA approved a new pacemaker device called the Revo MRI SureScan[46] which is the first to be labeled conditional[47] for MRI use.[48] There are several limitations to its use including certain patients' qualifications, body parts, and scan settings.
A 2008 U.S. study has found[49] that the magnets in some headphones included with portable music players, when placed within an inch of pacemakers, may cause interference.
Some medical procedures may require the use of antibiotics to be administered before the procedure. The patient should inform all medical personnel that he or she has a pacemaker. Some standard medical procedures such as the use of MRI may be ruled out by the patient having a pacemaker.
In addition, according to the American Heart Association, some home devices have a remote potential to cause interference by occasionally inhibiting a single beat. Cellphones available in the United States (less than 3 watts) do not seem to damage pulse generators or affect how the pacemaker works.[50]
A panel of The Heart Rhythm Society, a specialist organization based in Washington, DC found that it was legal and ethical to honor requests by patients, or by those with legal authority to make decisions for patients, to deactivate implanted cardiac devices. Lawyers say that the legal situation is similar to removing a feeding tube, though there is currently no legal precedent involving pace makers in the United States of America. A patient in the United States is thought to have a right to refuse or discontinue treatment, including a pacemaker that keeps him or her alive. Physicians have a right to refuse to turn it off, but are advised by the HRS panel that they should refer the patient to a physician who will.[51] Some patients believe that hopeless, debilitating conditions, like those brought on by severe strokes or late-stage dementia, can cause so much suffering that they would prefer not to prolong their lives with supportive measures, such as cardiac devices.[52]
Security and privacy concerns have been raised with pacemakers that allow wireless communication. Unauthorized third parties may be able to read patient records contained in the pacemaker, or reprogram the devices, as has been demonstrated by a team of researchers.[53] The demonstration worked at short range; they did not attempt to develop a long range antenna. The proof of concept exploit helps demonstrate the need for better security and patient alerting measures in remotely accessible medical implants.[53] In response to this threat, Purdue University and Princeton University researchers have developed a prototype firewall device, called MedMon, which is designed to protect wireless medical devices such as pacemakers and insulin pumps from attackers.[54]
A possible complication of dual-chamber artificial pacemakers is 'pacemaker-mediated tachycardia' (PMT), a form of reentrant tachycardia. In PMT, the artificial pacemaker forms the anterograde (atrium to ventricle) limb of the circuit and the atrioventricular (AV) node forms the retrograde limb (ventricle to atrium) of the circuit.[55] Treatment of PMT typically involves reprogramming the pacemaker.[55]
Another possible complication is "pacemaker-tracked tachycardia," where a supraventricular tachycardia is tracked by the pacemaker and produces beats from a ventricular lead. This is becoming exceedingly rare as newer devices are often programmed to recognize supraventricular tachycardias and switch to non-tracking modes.
Sometimes the leads, which are small diameter wires, from the pacemaker to the implantation site in the heart muscle will need to be removed. The most common reason for lead removal is infection however over time leads can degrade due to a number of reasons such as lead flexing.[56] Changes to programming of the pacemaker may overcome lead degradation to some extent. However a patient who has several pacemaker replacements over a decade or two in which the leads were reused may require a lead replacement surgery.
Lead replacement may be done in one of two ways. Insert a new set of leads without removing the current leads (not recommended as it provides additional obstruction to blood flow and heart valve function) or remove the current leads and then insert replacements. The lead removal technique will vary depending on the surgeon's estimation of the probability that simple traction will suffice to more complex procedures. Leads can normally be disconnected from the pacemaker easily which is why device replacement usually entails simple surgery to access the device and replace it by simply unhooking the leads from the device to replace and hooking the leads to the new device. The possible complications, such as perforation of the heart wall, come from removing the lead{s} from the patient's body.
The other end of a pacemaker lead is actually implanted into the heart muscle. In addition leads that have been implanted for a decade or two will usually have attachments to the patient's body at various places in the pathway from device to heart muscle since the human body tends to incorporate foreign devices into tissue. In some cases such as a device that has been inserted for a short amount of time, removal may involve simple traction to pull the lead from the body. Removal in other cases is typically done with a cutting device which threads over the lead and is moved down the lead to remove any organic attachments with tiny cutting lasers or similar device.
Pacemaker lead malposition in various locations has been described in the literature. Depending on the location of the pacer lead and symptoms treatment varies.[57]
Sometimes devices resembling pacemakers, called implantable cardioverter-defibrillators (ICDs) are implanted. These devices are often used in the treatment of patients at risk from sudden cardiac death. An ICD has the ability to treat many types of heart rhythm disturbances by means of pacing, cardioversion, or defibrillation. Some ICD devices can distinguish between ventricular fibrillation and ventricular tachycardia (VT), and may try to pace the heart faster than its intrinsic rate in the case of VT, to try to break the tachycardia before it progresses to ventricular fibrillation. This is known as fast-pacing, overdrive pacing, or anti-tachycardia pacing (ATP). ATP is only effective if the underlying rhythm is ventricular tachycardia, and is never effective if the rhythm is ventricular fibrillation.
| I | II | III | IV |
|---|---|---|---|
| Shock chamber | Antitachycardia pacing chamber | Tachycardia detection | Antibradycardia pacing chamber |
| O = None | O = None | E = Electrogram | O = None |
| A = Atrium | A = Atrium | H = Hemodynamic | A = Atrium |
| V = Ventricle | V = Ventricle | V = Ventricle | |
| D = Dual (A+V) | D = Dual (A+V) | D = Dual (A+V) |
| ICD-S | ICD with shock capability only |
| ICD-B | ICD with bradycardia pacing as well as shock |
| ICD-T | ICD with tachycardia (and bradycardia) pacing as well as shock |
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| リンク元 | 「人工心臓ペースメーカー」 |
| 関連記事 | 「cardiac」「artificial」「pacemaker」「cardiac pacemaker」 |
| ClassⅠ | ClassⅡa | ClassⅡb | ClassⅢ | |
| 有益であるという根拠があり，適応であることが一般に同意されている | 有益であるという意見が多いもの | 有益であるという意見が少ないもの | 有益でないまたは有害であり，適応でないことで意見が一致している | |
| 房室ブロック | １ 徐脈による明らかな臨床症状を有する第2度、高度または第3度房室ブロック ２ 高度または第3度房室ブロックで以下のいずれかを伴う場合 （1）投与不可欠な薬剤によるもの （2）改善の予測が不可能な術後房室ブロック （3）房室接合部のカテーテルアブレーション後 （4）進行性の神経筋疾患に伴う房室ブロック （5）覚醒時に著明な徐脈や長時間の心室停止を示すもの |
１ 症状のない持続性の第3度房室ブロック ２ 症状のない第2度または高度房室ブロックで、以下のいずれかを伴う場合 （1）ブロック部位がHis束内またはHis束下のもの （2）徐脈による進行性の心拡大を伴うもの （3）運動または硫酸アトロピン負荷で伝導が不変もしくは悪化するもの 3。徐脈によると思われる症状があり、他に原因のない第1度房室ブロックで、ブロック部位がHis束内またはHis束下のもの |
１ 至適房室間隔設定により血行動態の改善が期待できる心不全を伴う第1度房室ブロック | |
| 2枝ブロック 3枝ブロック |
１ 慢性の2枝または3枝ブロックがあり、第2度MobitzⅡ型、高度もしくは第3度房室ブロックの既往のある場合 ２ 慢性の2枝または3枝ブロックがあり、投与不可欠な薬剤の使用が房室ブロックを誘発する可能性の高い場合 3。慢性の2枝または3枝ブロックとWenckebach型第2度房室ブロックを認め、失神発作の原因として高度の房室ブロック発現が疑われる場合 |
１ 慢性の2枝または3枝ブロックがあり、失神発作を伴うが原因が明らかでないもの ２ 慢性の2枝または3枝ブロックがあり、器質的心疾患を有し、電気生理検査によりHis束以下での伝導遅延・途絶が証明された場合 |
１ 慢性の2枝または3枝ブロックがあり、電気生理検査でHis束以下での伝導遅延・途絶の所見を認めるが、器質的心疾患のないもの | |
| 洞機能不全症候群 | １ 失神、痙攣、眼前暗黒感、めまい、息切れ、易疲労感等の症状あるいは心不全があり、それが洞結節機能低下に基づく徐脈、洞房ブロック、洞停止あるいは運動時の心拍応答不全によることが確認 された場合。それが長期間の必要不可欠な薬剤投与による場合を含む |
１ 上記の症状があり、徐脈や心室停止を認めるが、両者の関連が明確でない場合 ２ 徐脈頻脈症候群で、頻脈に対して必要不可欠な薬剤により徐脈を来たす場合 |
１ 症状のない洞房ブロックや洞停止 | |
| 徐脈性心房細動 | １ 失神、痙攣、眼前暗黒感、めまい、息切れ、易疲労感等の症状あるいは心不全があり、それが徐脈や心室停止によるものであることが確認された場合。それが長期間の必要不可欠な薬剤投与による場合を含む | １ 上記の症状があり、徐脈や心室停止を認めるが、両者の関連が明確でない場合 | ||
| 過敏性頸動脈洞症候群 反射性失神 |
１ 過敏性頸動脈洞症候群で、心拍抑制による反復する失神発作を認める場合 ２ 反射性失神で、心電図で心拍抑制が記録され、反復する失神発作を認める場合 |
１ 反射性失神で、反復する失神発作があり、head-uptilt試験により心拍抑制反応が認められる場合 | １ head-up tilt試験により心拍抑制反応が認められない過敏性頸動脈症候群・反射性失神 | |
| 閉塞性肥大型心筋症 | １ 有意な流出路圧較差があり、圧較差に基づく症状によりQOL低下を来たす閉塞性肥大型心筋症で、他にペースメーカ植込みの適応となる理由を有する場合（薬剤による徐脈を含む）。 | １ 有意な圧較差があり、圧較差に基づく症状によりQOL低下を来たす閉塞性肥大型心筋症で、症状と圧較差が関連しており、薬物治療が無効か副作用のため使用不能か、他の方法が不適当な場合 | １ 圧較差がなく、徐脈による植込み適応もない場合。 |