Non-restraining EEG radiotelemetry is a valuable methodological approach to record in vivo long-term electroencephalograms from freely moving rodents. This detailed protocol describes stereotaxic epidural and deep intracerebral electrode placement in different brain regions in order to obtain reliable recordings of CNS rhythmicity and CNS related behavioral stages.
Implantable EEG radiotelemetry is of central relevance in the neurological characterization of transgenic mouse models of neuropsychiatric and neurodegenerative diseases as well as epilepsies. This powerful technique does not only provide valuable insights into the underlying pathophysiological mechanisms, i.e., the etiopathogenesis of CNS related diseases, it also facilitates the development of new translational, i.e., therapeutic approaches. Whereas competing techniques that make use of recorder systems used in jackets or tethered systems suffer from their unphysiological restraining to semi-restraining character, radiotelemetric EEG recordings overcome these disadvantages. Technically, implantable EEG radiotelemetry allows for precise and highly sensitive measurement of epidural and deep, intracerebral EEGs under various physiological and pathophysiological conditions. First, we present a detailed protocol of a straight forward, successful, quick and efficient technique for epidural (surface) EEG recordings resulting in high-quality electrocorticograms. Second, we demonstrate how to implant deep, intracerebral EEG electrodes, e.g., in the hippocampus (electrohippocampogram). For both approaches, a computerized 3D stereotaxic electrode implantation system is used. The radiofrequency transmitter itself is implanted into a subcutaneous pouch in both mice and rats. Special attention also has to be paid to pre-, peri- and postoperative treatment of the experimental animals. Preoperative preparation of mice and rats, suitable anesthesia as well as postoperative treatment and pain management are described in detail.
Radiotelemetry is a most valuable methodological approach for measuring a variety of behavioral and physiological parameters in conscious, unrestrained animals of various sizes, particularly in the context of EEG, ECG, EMG, blood pressure, body core temperature or activity measurements 1-7. Theoretically, any species can be analyzed using implantable EEG radiotelemetry from laboratory rodents such as mice and rats to cats, dogs, pigs and primates 3,8. Even fish, reptiles and amphibians are subject to radiotelemetric investigation 9. Over the last two decades, implantable EEG radiotelemetry has proven to be valuable in the characterization of various transgenic animal models of human diseases, such as epilepsies, sleep disorders, neurodegenerative and neuropsychiatric disorders 7,10-12. In the past, numerous methodological approaches collecting physiological data including biopotentials from mice and rats have been described. Worn in jacket recorder systems, physical restraint methods, non-implanted radiotransmitters and tethered systems have received the main attention in the past 13,14. Nowadays, various systems for radiotelemetric implantation are commercially available. However, a literature screen also revealed 29 publications that describe the development of self-made radiotelemetric systems 15-40. Whereas home-made systems are likely to be less expensive and more user adapted, commercially available systems are straight forward, relatively easy to install and can be setup quickly.
Implantable EEG radiotelemetry has a number of advantages compared to competing techniques such as physical restraint methods, worn in jacket systems or tethered approaches. The latter are restraining by definition, i.e., the animal is unable to move or its normal behavior is impaired. It might even be necessary to anesthetize the animal for acquisition of reliable data. Modern tethered systems however are likely to be less restraining, but this needs to be scientifically validated. Radiotelemetry on the other hand allows animals to exhibit their full repertoire of behavior without spatiotemporal restrictions and thus, is thought to be superior to restraining approaches and be more predictive of the results that could be acquired in humans 1,3. It is known for quite a while that restraining approaches can dramatically alter fundamental physiological parameters, e.g., food intake, body core temperature, blood pressure and heart rate and physical activity for example 3. Tethered systems represent one still widely used classical restraining approach 13,14. The electrodes which are either epidural or deep electrodes are generally connected to a miniature socket which is anchored to the skull. The socket itself is exposed for attachment of a cable that allows relatively free movement of the animal. Although nowadays tethered systems have become extremely filigree and highly flexible, one of its major disadvantages is, that it is still semi-restraining. Besides, there might be a risk of infection at the electrode implantation site as the animals tend to manipulate any external devices originating from their body (head). Although wireless radiotelemetry technology in various species has already been described in the late 60s and has thus existed for decades, it has only recently become affordable, reliable, and relatively easy-to-use 10,41,42, particularly in small laboratory rodents such as mice and rats. Small, miniature implantable EEG transmitters are now commercially available and can be implanted in mice greater than 20 g (~10 weeks). Thus, the electrophysiological characterization of transgenic mouse models in particular has become a predominant field of application of implantable EEG radiotelemetry these days. Animal size is no longer an absolute experimental restriction whereas the life-span of the transmitters' battery indeed is. Despite its limited life-time, implantable transmitter systems are capable of minimizing most disadvantages related to potential recording-associated stress by restraining systems. Rodents can present their complete armamentarium of physiological behavior including resting, locomotor activity (exploration) and sleep (REM, slow-wave sleep) 43,44. Importantly, implantable radiotelemetry can strongly reduce animal use 3. Currently, there is an intense discussion on how to limit the number of experimental animals in science and reduce their suffering. Clearly, animal experimentation and animal models of human and animal diseases are essential for our understanding of the bottom-line pathophysiology and subsequent progress in therapy. Furthermore, animal experiments are critical in drug research and development. They do substantially contribute to preclinical/toxicological studies in drug licensing thus committing to both human and animal care. It's noteworthy, that currently no alternatives are yet available to animal research to understand the complex pathophysiological mechanisms which would be otherwise impossible to be elicited. At the same time, the 3R, i.e., replacement, reduction and refinement strategy in the EU and the USA strongly encourages research into complementary and alternative methods. Radiotelemetry is an important example of a successful 3R strategy as it can reduce the number of experimental animals and their suffering compared to other techniques.
Here we provide a detailed and contiguous step-by-step approach to perform a subcutaneous pouch implantation of a radiofrequency transmitter in both mice and rats. This first sequence is followed by a description of stereotaxic epidural and deep intracerebral EEG electrode positioning. Special attention is paid to housing conditions, anesthesia, peri- and postoperative pain management and possible anti-infective treatment. The focus is on the computerized 3D stereotaxic approach to reliably target epidural and deep intracerebral structures. We also comment on frequent experimental pitfalls in EEG electrode implantation and strategies for reduction of trauma and optimization of pain management during postoperative recovery. Finally, examples of surface and deep EEG recordings are presented.
Ethics Statement: All animal experimentation was performed according to the guidelines of the local and institutional Council on Animal Care (University of Bonn, BfArM, LANUV, Germany). In addition, all animal experimentation was carried out in accordance with superior legislation, e.g., the European Communities Council Directive of 24 November 1986 (86/609/EEC) or individual regional or national legislation. Specific effort is made to minimize the number of animals used and their suffering.
1. Experimental Animals
2. EEG Radiotelemetry System
Note: The protocol described is based on a commercially available telemetry systems used for surface and deep intracerebral EEG recordings (Figure 2).
3. Anesthesia and Pain Management
4. Surgical Instrumentation — General Aspects
5. Surgery — Transmitter Placement
6. Stereotaxic Surface Electrode Implantation
7. Stereotaxic Deep Intracerebral EEG Electrode Implantation
8. Post-operative Care and Post-operative Pain Management
This section illustrates examples obtained from surface and deep, intracerebral EEG recordings. Initially it should be stated that baseline recordings under physiological conditions are mandatory prior to subsequent recordings following e.g., pharmacological treatment. Such baseline recordings may provide valuable information about functional interdependence of brain rhythmicity with different behavioral states or sleep / circadian rhythmicity. Here, we show examples of recorded seizure activity following acute administration of proconvulsive / psychoenergetic drugs. As outlined above, a common field of application in EEG radiotelemetry is epilepsy research. Epilepsy models include acute and chronic pharmacological models as well as genetic (transgenic) models of epilepsy. Here we demonstrate acute models of non-convulsive absence-like seizures induced by i.p. administration of R/S-baclofen at 20 mg/kg and bicucullinemethobromide at 10 mg/kg. Pharmacodynamically, baclofen is a GABA(B) receptor agonist that increases K+ efflux out of the cell both pre- and postsynaptically whereas bicuculline is a GABA(A) antagonist that inhibits Cl– influx into the cell. Activation of GABA(A) receptors results in the initiation and maintenance of hyperoscillation and hypersynchronization within the thalamocortical-corticothalamic circuitry. Figure 5B, C displays epidural EEG recordings following the i.p. administration of R/S-baclofen (20 mg/kg) and bicucullinemethobromide (10 mg/kg). Systemic administration of 4-aminopyridine (4-AP) at a dosage of 10 mg/kg i.p. or pentylenetetrazole (PTZ) can provoke generalized tonic-clonic seizures in mice and rats. Following 4-AP or PTZ injection, animals show a typical temporal sequence of motoric actions that dose-dependent in severity, i.e., intensity and duration. Seizures normally start from a hypoactive state, followed by a mild, partial myoclonus that mainly affects the face with vibrissal twitching, the head and/or the forelimbs. This partial seizure state can than generalize into a myoclonus characterized by loss of upright posture or a whole body clonus involving all four limbs. The latter is characterized by jumping, wild running and finally, a tonic extension of the hindlimbs. A typical epidural EEG recording following 4-AP administration (10 mg/kg) is depicted in Figure 5A. This epidural type of recording is capable of eliciting the early stages of seizure development, i.e., myoclonic head movement, jerks of face and forelimbs) with high precision. Although there is a high degree of motoric seizure activity associated with high EMG, i.e., muscle activity, only minimal EMG contamination of EEG recordings is observed. As becomes obvious in Figure 5A, the sporadic spike activity (*) is followed by a generalized clonus with a typical spike/polyspike/spike-wave pattern (1) followed by a subsequent episode of continuous spike activity. Note that EMG contamination is hardly detectable. Although the recording segment is characterized by enhanced muscle activity due to the whole body clonus, the spike activity originating from the brain is prominent and EMG contamination is extremely low. This example proves that the proposed experimental approach is capable of recording EEG signals selectively even under generalized seizure conditions, when EEG signals might expected to be masked by EMG artifacts. Note that drug injection regimes as described here always require recordings prior to injection, under injection and following pharmacological administration. Controls should include sham-injected / vehicle injected animals.
A typical intracerebral brain target is the hippocampus, e.g., the CA1 region. Hippocampal seizure activity can be induced by kainic acid (KA) or N-methyl-D-aspartate (NMDA). The non-NMDA receptor agonist KA is generally administered intraperitoneally at a dose of 10-30 mg/kg. Hippocampal seizures represent an important seizure subgroup that can be acutely induced by various glutamate receptor agonists. Using the deep electrode implantation procedure described above, KA induced hippocampal seizures can be recorded with high precision (Figure 5D). Besides KA, hippocampal seizures can also be induced by i.p. administration of NMDA at a dose of 150 mg/kg. As in KA treated animals, NMDA treated mice, develop seizures through a sequence of paroxysmal scratching, hypermotility and circling, tonic-clonic convulsions, and, occasionally, death.
Figure 6 illustrates examples of simultaneous cortical (epidural) and hippocampal (deep) EEGs in a most popular chronic hippocampal seizure model, i.e., the pilocarpine model of mesial temporal lobe epilepsy (mTLE) in rats. It should be noted that EEG artifacts can sometimes mimic ictiform discharges (Figure 7). Thus special attention has to be paid to reduce ECG, EMG and externally induced EEG signal disturbance. It should be noted that the implantation procedure described here allows for maximum reduction in EEG signal contamination. Artifacts either result from external electrical devices which can be shielded by, for example, a Faraday cage or by ossification processes around the drilled holes that tend to lift the electrodes out of the brain. The latter is a time-dependent process that marks an experimental limitation of the technique. It should be noted that seizure recording and analysis is not the only field of application of the techniques described here. Surface and deep intracerebral EEG recordings can be used for complex time-frequency analysis, e.g., in animal models of neuropsychiatric diseases and for sleep studies for example.
Figure 1: Housing Conditions in Radiotelemetry. In vivo studies in different mouse or rat lines or pharmacological or transgenic lines of human diseases require high standardization to minimize intra-individual variability and potential bias arising from confounding factors. Proper housing conditions are a prerequisite for high-quality recordings and valid telemetric results. Open housing conditions on lab shelves are not suitable for recording. Instead recording should be performed inside an animal facility, or in ventilated cabinets (A). Ideally, ventilated cabinets are not only used for pre-surgical and postsurgical housing and recovery, but also for EEG recording (B) as this guarantees stability of environmental conditions and lack of disturbance. If recording cannot be performed in a ventilated cabinet, they should be done in a Faraday cage inside an environmentally controlled animal room (C). Please click here to view a larger version of this figure.
Figure 2: Standard EEG Radiotelemetry System and Radiofrequency Transmitters. Besides self-made systems, a number of commercially available systems are on the market. The basic setup of such system is depicted in (A). The system consists of a radiofrequency transmitter, the receiver plate, a data exchange matrix serving as a multiplexer, and the data acquisition, processing and analyzing core unit. For frequency analysis, seizure detection and sleep analysis specific software modules are offered. Multiple types of transmitters are available depending on which species is supposed to be investigated and depended on the scientific question. B) Implanted mice, receiver plates and a multiplexer placed inside a ventilated cabinet for standardized recording conditions. C) An adult C57Bl/6J mouse and a 2-channel radiofrequency transmitter. D) Dorsal view of the skull 4 weeks after electrode implantation and fixation using glass ionomer cement (reprinted from 61 and 62 with permission). Please click here to view a larger version of this figure.
Figure 3: Anesthesia and Stereotaxic Setup for Mice and Rats. A) Gas anesthesia system using isoflurane. A precision high-speed dental drill is mounted on a 3D stereotaxic device for mice and rats respectively. Supplemental warmth is given using a heating pad. B) Close-up of drill, stereotaxic ear bars and nose clamp (reprinted from 62 with permission). Please click here to view a larger version of this figure.
Figure 4: Stereotaxic Surface and Deep Electrode Implantation. A) Scheme of an epidural electrode placement in mice and rats. B) Anatomic structures and landmarks of the murine skull. Apical view of a C57Bl/6J mouse skull which has been prepared in 0.3% H2O2. Note cranial bones (os frontale (of), os parietale (op), os occipitale (oo)) and sutures (sutura frontalis (sf), sutura sagittalis (ss), sutura coronaria (sc), and sutura lambdoidea (sl)) which determine the major anatomic landmarks bregma (B) and lambda (L). C) Lateral view of a C57Bl/6J mouse skull. D) One epidural, differential electrode is placed on the motor cortex (M1), an additional intrahippocampal differential electrode is placed in the CA1 region of the hippocampus. Both pseudo-reference electrodes are localized on the cerebellum. E) Coronal section (scheme) illustrating the localization of the deep, intracranial electrode for recording the electrohippocampogram. F) Close-up of the deep EEG electrode, the sensing lead of the radiofrequency transmitter and their arrangement on top of the murine skull (reprinted from 61 and 62 with permission). Please click here to view a larger version of this figure.
Figure 5: Pharmacological Induction of Epileptic Discharges. A) Surface EEG recording displaying ictal discharges after i.p. administration of 4-aminopyridine (4 AP, 10 mg/kg). Sporadic spikes (*) evolve into a transitory episode of continuous spiking (1), resulting in an EEG depression (decreased amplitude, 2-3). Shortly after this period a second spike-train concomitant to the development of a generalized tonic-clonic seizure with wild running and jumping becomes apparent which finally results in a tonic extension of the hindlimbs (4) and death. The remaining tiny signal following brain death represents an ECG (R-spike) contamination. B) After i.p. administration of bicucullinemethobromide (BMB, 10 mg/kg) mice show trains of characteristic spikes and spike waves. C) Administration of baclofen (20 mg/kg) resulting in sporadic occurrence of spiking activity. D) Intrahippocampal electroencephalographic (EEG) recordings following i.p. administration of KA (30 mg/kg). I: deep CA1 recording from a C57Bl/6J mouse for 2 hr immediately after KA administration. At 30 mg/kg KA contiguous hippocampal seizure activity is observed occasionally interrupted by postictal depression (arrows). Ictal discharges are characterized by spike and/or spike-wave activity (see insets) in the delta- and theta-wave range (4-8 Hz). II-IV: At days 1, 3, and 5 post-injection 1h CA1 EEG recordings illustrate declining but still continuous ictal discharges related to neuronal excitotoxic degeneration (reprinted from 61 and 62 with permission). Please click here to view a larger version of this figure.
Figure 6: Radiotelemetric EEG Recording in a Rat Model of Mesial Temporal Lobe Epilepsy. Limbic seizures are pharmacologically induced via a pilocarpine injection regime. This figure illustrates synchronous recording from the primary motor cortex (M1) as well as the hippocampal CA1 region from a rat at the age of 3 months. Ascending and descending spike / poly-spike trains are present in both deflections (reprinted from62 with permission). Please click here to view a larger version of this figure.
Figure 7: Electrocardiographic/Electromyographic and System Artifacts Contaminating the EEG (deep electrodes (A-C), surface electrodes (D), vertical bar: 50 μV in A-C, 1 mV in D). A) Intrahippocampal EEG recording from a control mouse. B) Damaged silicone insulation of the sensing leads as well as ossification processes originating from the edge of drilled holes can result in dramatic contamination of electroencephalographic recordings. Note the regular pattern of interfering ECG signal, i.e., R-spikes (arrows). Importantly, ECG contamination cannot be completely avoided but the implantation procedure presented here will reduce it to a minimum. C) Electromyographic contamination of the EEG characterized by high frequency activity. D) Artifacts can also originate from cross-talk between receiver plates or from electrical noise evolving from room lights or various other electrical devices that are close to the receiver plates. An effective way of preventing the system picking up noise is to shield receiver plate and home cage using a ventilated cabinet or a Faraday cage (reprinted from 61and 62 with permission). Please click here to view a larger version of this figure.
Implantable EEG radiotelemetry is of central relevance as it is a non-restraining technique allowing experimental animals to perform their full repertoire of behavior1,3. This is of major interest as the telemetric approach enables not only spontaneous EEG recordings but also recordings under cognitive tasks and circadian analytical setups, such as T-maze, radial maze, water maze, sleep deprivation tasks or whenever an EEG recording is necessary or helpful during complex cognitive or motor activity.
This protocol describes epidural surface and deep intracerebral EEG electrode implantation in mice and rats and connection to an implantable EEG radiofrequency transmitter. Critical steps within the procedure comprise pre-surgical issues, i.e., selection of species and strain, housing conditions, anesthesia and pain management. A critical literature screen reveals that the latter can serve as confounding factors that contribute to divergent results in various research approaches. For example, the choice of experimental species, e.g., mice versus rats and even strains can totally alter experimental results. The same holds true for gender. In general, a gender specific grouping and analysis is highly recommended. If this is not possible, genders should be balanced at least. If experimental conditions are not strictly harmonized or controlled, acquired data are either not comparable or simply invalid.
The stereotaxic implantation procedure described here provides a reliable tool to record high-quality EEGs from both the surface and deep intracerebral structures. Critical steps of the implantation procedure include the drilling process. It should be performed at maximum speed (RPM) with minimum pressure. Though high drilling speed generates heat, minimum pressure guarantees that subcortical structures are not thermally damaged. Minimum pressure is essential to avoid a sudden breakthrough of the skull and subsequent damage of the underlying cortex. In addition, special care has to be taken not to damage a meningeal artery or a dural sinus. In mice, the skull is rather transparent due to its small thickness. Therefore, meningeal arteries and sinuses can be identified to avoid damage. In case of bleeding the early and late prognosis is bad in general and it is questionable whether such an animal meets the inclusion criteria for a reliable study. We recommend sacrificing such animals.
In our experience, high-quality EEG recordings using the described approach can be performed up to 4 weeks. Due to ossification processes originating from the drilled holes within the calvaria, electrodes tend to be lifted up resulting in ECG and EMG contamination. It should further be considered that targeting a specific surface or deep, intracerebral structure relies on stereotaxic coordinates from brain atlases. These stereotaxic brain maps are normally related to a specific mouse or rat strain of a specific age. It has to be noted critically that different mouse and rat strains can exhibit differences in age specific size of the body and the skull. Thus, there are inter-strain and intra-strain differences as regards the basic craniometrics landmarks bregma and lambda. This issue poses a specific challenge if one wants to perform surface and deep electrode recordings from young mice and rats that are still developing, i.e., display skull and brain growth. In this case, a reliable long-term recording from the position of choice is hardly possible.
In order to make the craniometric landmarks visible a bleaching procedure is recommended. Care must be taken to limit the incubation time of H2O2 as it can otherwise penetrate the skull and do oxidative damage to the cortex.
Finally, it's important to note that commercial EEG radiotelemetry systems can be combined with other electrophysiological setups as well. We recently established the combination of radiotelemetric EEG recording with an auditory evoked potential setup in mice. This sophisticated approach allows, for example, to perform endophenotyping and to identify and characterize transgenic mouse models of schizophrenia, e.g., by application of the double-click paradigm and analysis of P50/N100 potentials. In general, the technical link between EEG radiotelemetry and evoked-potentials is likely to be a promising approach in the future.
The authors have nothing to disclose.
The authors would like to thank Dr. Christina Ginkel (German Center for Neurodegenerative Diseases, DZNE), Dr. Michaela Möhring (DZNE) and Dr. Robert Stark (DZNE) for assistance in animal breeding and animal health care. This work was financially supported by the Federal Institute for Drugs and Medical Devices (Bundesinstitut für Arzneimittel und Medizinprodukte, BfArM) Bonn, Germany.
Carprofen (Rimadyl VET – InjektionA2:D43slösung) | Pfizer | PZN 0110208 | 20 ml |
binocular surgical magnification microscope | Zeiss Stemi 2000 | 0000001003877, 4355400000000, 0000001063306, 4170530000000, 4170959255000, 4551820000000, 4170959040000, 4170959050000 | |
bulldog serrefine | F.S.T. | 18051-28 | 28mm |
cages (Macrolon) | Techniplast | 1264C, 1290D | |
cold light source | Schott KL2500 LCD | 9.705 202 | ordered at Th.Geyer |
cotton tip applicators (sterile) | Carl Roth | EH12.1 | |
Dexpanthenole (Bepanthen Wund- und Heilsalbe) | Bayer | PZN: 1578818 | |
drapes (sterile) | Hartmann | PZN 0366787 | |
70% ethanol | Carl Roth | 9065.5 | |
0.3% / 3% hydrogene peroxide solution | Sigma | 95321 | 30% stock solution |
gloves (sterile) | Unigloves | 1570 | |
dental glas ionomer cement | KentDental /NORDENTA | 957 321 | |
2% glutaraldehyde solution | Sigma | G6257 | |
Graefe Forceps-curved, serrated | F.S.T. | 11052-10 | |
Halsey Micro Needle Holder-Tungsten Carbide | F.S.T. | 12500-12 | 12.5 cm |
heat-based surgical instrument sterilizer | F.S.T. | 18000-50 | |
heating pad | AEG HK5510 | 520010 | ordered at myToolStore |
high-speed dental drill | Adeor | SI-1708 | |
Iris scissors extra thin | F.S.T. | 14058-09 | 9 cm |
Inhalation narcotic system (isoflurane) | Harvard Apparatus GmbH | 34-1352, 10-1340, 34-0422, 34-1041, 34-0401, 34-1067, 72-3044, 34-0426, 34-0387, 34-0415, 69-0230 | |
Isoflurane | Baxter 250 ml | PZN 6497131 | |
Ketamine | Pfizer | PZN 07506004 | |
lactated Ringer’s solution (sterile) | Braun | L7502 | |
Lexar-Baby Scissors-straight, 10 cm | F.S.T. | 14078-10 | 10 cm |
Nissl staining solution | Armin Baack | BAA31712159 | |
non-absorbable suture material 5-0/6-0 (sterile) | SABANA (Sabafil) | N-63123-45 | |
Covidien (Sofsilk) | S1172, S1173 | ||
Halsey Needle Holder | F.S.T. | 12001-13 | 13 cm |
pads (sterile) | ReWa Krankenhausbedarf | 2003/01 | |
0.9% saline (NaCl, sterile) | Braun | PZN:8609255 | |
scalpel blades with handle (sterile) | propraxis | 2029/10 | |
Standard Pattern Forceps | F.S.T. | 11000-12, 11000-14 | 12 cm and 14.5 cm length |
Steel and tungsten electrodes parylene coated | FHC Inc., USA) | UEWLGESEANND | |
stereotaxic frame | Neurostar | 51730M | ordered at Stoelting |
(Stereo Drive-New Motorized Stereotaxic) | |||
tapes (sterile) | BSN medical GmbH & Co. KG | 626225 | |
TA10ETA-F20 | DSI | 270-0042-001X | Radiofrequency transmitter 3.9 g, 3.9 g, 1.9 cc, input voltage range ± 2.5 mV, channel bandwidth (B) 1-200 Hz, nominal sampling rate (f) 1000 Hz (f = 5B) temperature operating range 34-41 °C warranted battery life 4 months |
TL11M2-F20EET | DSI | 270-0124-001X | Radiofrequency transmitter 3.9 g, 1.9 cc, input voltage range ± 1.25 mV, channel bandwidth (B) 1-50 Hz, nominal sampling rate (f) 250 Hz (f = 5B) temperature operating range 34-41 °C warranted battery life 1.5 months |
Tissue Forceps- 1×2 Teeth 12 cm | F.S.T. | 11021-12 | 12 cm length |
Tungsten carbide iris scissors | F.S.T. | 14558-11 | 11.5 cm |
Vibroslicer 5000 MZ | Electron Microscopy Sciences | 5000-005 | |
Xylazine (Rompun) | Bayer | PZN: 1320422 |