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Biomedical subjects

P Zeng

Publications and source records attributed to P Zeng.

35 records · Page 2Linked to original sources
PubMed1994

[HPLC analysis of 2-(P-dimethylaminostyryl) pyridine methiodide concentration in plasma].

A reversed phase high performance liquid chromatography (RP-HPLC) method for determination of 2-(p-dimethylaminostyryl) pyridine methiodide (DSPM) concentration in rabbit plasma is reported. The stationary phase was YWG-C18H37. The mobile phase consisted of 80% CH3OH, 20% CH3COOH-CH3COONa buffer (pH 4.0, 0.20 mol/L) and (C2H5)2NH 25 mmol/L. Its flow rate was 1.0 ml/min. The column temperature and pressure was 28 degrees C and 10.13 MPa, respectively. The detect wavelength was 460 nm. The detection limit of DSPM was 2 ng or 0.08 mumol/L in plasma. The RSD (%) of within-day and between-days were less than 7%. A good linear relationship between peak area and DSPM concentration in plasma (0.68-13.65 mumol/L) was found (r = 0.9996).

Animals↗
PubMed1990

[Biphasic effects of caffeine on tension in isolated aorta of rat].

The dual effects of caffeine on the tension were observed in rat thoracic aorta. When the preparation was exposed to Tyrode's solution containing caffeine of 1, 5 and 10 mmol/L, the tension increased. In 1-2 min it slowly decreased to a level lower than the pre-caffeine tension. After norepinephrine (1 mumol/L) was added, caffeine produced a greater inhibitory effect and the contraction phase disappeared. The dual effects of caffeine were not affected by the vascular endothelium. In the Tyrode's solution containing NiCl2 2 mmol/L, the first addition of caffeine (10 mmol/L) or norepinephrine (0.1 mumol/L) caused a contraction. The one caused by norepinephrine was greater. A second addition of caffeine did not cause a contraction, but addition of norepinephrine at this time caused a small contraction. After the washout of norepinephrine which had caused a greater contraction, the addition of caffeine (10 mmol/L) did not cause a contraction. These results indicate that norepinephrine completely depletes caffeine-sensitive Ca2 stores but caffeine only partially depletes norepinephrine-sensitive Ca2+ stores.

Animals↗
PubMedDate not supplied

Measurement of rotary pump flow and pressure by computation of driving motor power and speed.

Measurement of pump flow and pressure by ventricular assist is an important process, but difficult to achieve. On one hand, the pump flow and pressure are indicators of pump performance and the physiologic status of the receptor, meanwhile providing a control basis of the blood pump itself. On the other hand, the direct measurement forces the receptor to connect with a flow meter and a manometer, and the sensors of these meters may cause haematological problems and increase the danger of infection. A novel method for measuring flow rate and pressure of rotary pump has been developed recently. First the pump performs at several rotating speeds, and at each speed the flow rate, pump head and the motor power (voltage x current) are recorded and shown in diagrams, thus obtaining P (motor power)-Q (pump volume) curves as well as P-H (pump head) curves. Secondly, the P, n (rotating speed) values are loaded into the input layer of a 3-layer BP (back propagation) neural network and the Q and H values into the output layer, to convert P-Q and P-H relations into Q = f (P,n) and H = g (P, n) functions. Thirdly, these functions are stored by computer to establish a database as an archive of this pump. Finally, the pump flow and pressure can be computed from motor power and speed during animal experiments or clinical trials. This new method was used in the authors' impeller pump. The results demonstrated that the error for pump head was less than 2% and that for pump flow was under 5%, so its accuracy is better than that of non-invasive measuring methods.

Animals↗
PubMedDate not supplied

Axial reciprocation of rotating impeller: a new concept of antithrombogenecity in centrifugal pump.

For long-term application, rotary pumps have to solve the problems of bearing wear and thrombosis along the bearing. Most investigators choose the magnetic bearing to realize zero-friction and no contact between the rotor and stator; the former avoids the mechanical wear and the latter eliminates the possibility of thrombus formation. The authors have tried and found, however, that it is difficult to apply a magnetic bearing to the rotary pump without disturbing its simplicity, reliability and implantability, and have therefor developed a much simpler and much more creative approach to achieve the same results. Instead of using a sliding bearing, a rolling bearing has been devised for the pump, and its friction is about 1/15 of the sliding bearing. Furthermore, a wear-proof material of ultra-high-molecular weight polythene has been adopted to make the rollers, and its anti-wear property is 8 times better than metal. Thereby, the service life of the bearing has been prolonged to ten years according to the documents provided by the producer. In order to prevent the thrombus formation along the bearing, the impeller reciprocates axiallly as the impeller changes its rotating speed periodically to produce a pulsatile flow. The reciprocation is the result of the effects of a magnetic force between the motor rotor and stator, and a hydraulic force between the blood flow and the impeller. Similar to a piston pump, the oscillating impeller can make the blood flow in and out of the bearing, resulting in wash-out once a circle. This obviously helps to prevent thombosis along the bearing and in the pump. The endurance tests with saline of this novel pump demonstrated the durabililty of the device. It promises to be able to assist the circulation of patients permanently, and to be able to replace heart transplantation in the future.

Equipment Design↗
PubMedDate not supplied

How to produce a pulsatile flow with low haemolysis?

It is evident that a pulsatile flow is important for blood circulation because the flow pulsatility can reduce the resistance of peripheral vessels. It is difficult, however, to produce a pulsatile flow with an impeller pump, since blood damage will occur when a pulsatile flow is produced. Further investigation has revealed that the main factor for blood damage is turbulence shear, which tears the membranes of red blood cells, resulting in free release of haemoglobin into the plasma, and consequently leads to haemolysis. Therefore, the question for developing a pulsatile impeller blood pump is: how to produce a pulsatile flow with low haemolysis? The authors have successively developed a pulsatile axial pump and a pulsatile centrifugal pump. In the pulsatile axial pump, the impeller reciprocates axially and rotates simultaneously. The reciprocation is driven by a pneumatic device and the rotation by a dc motor. For a pressure of 40 mm Hg pulsatility, about 50 mm axial reciprocating amplitude of the impeller is desirable. In order to reduce the axial amplitude, the pump inlet and the impeller both have cone-shaped heads, and the gap between the impeller and the inlet pipe changes by only 2 mm, that is the impeller reciprocates up to 2 mm and a pressure pulsatility of 40 mm Hg can be produced. As the impeller rotates with a constant speed, low turbulence in the pump may be expected. In the centrifugal pulsatile pump, the impeller changes its rotating speed periodically; the turbulence is reduced by designing an impeller with twisted vanes which enable the blood flow to change its direction rather than its magnitude during the periodic change of the rotating speed. In this way, a pulsatile flow is produced and the turbulence is minimized. Compared to the axial pulsatile pump, the centrifugal pulsatile pump needs only one driver and thus has more application possibilities. The centrifugal pulsatile pump has been used in animal experiments. The pump assisted the circulation of calves for several months without harm to the blood elements and the organ functions of the experimental animal. The experiments demonstrated that the pulsatile impeller pump is the most efficient pump for assisting heart recovery, because it can produce a pulsatile flow like a diaphragm pump and has no back flow as occurs in a non-pulsatile rotary pump; the former reduces the circulatory resistance and the latter increases the diastole pressure in aorta and thus increases the perfusion of coronary arteries of the natural heart.

Animals↗
PubMedDate not supplied

Permanent magnetic-levitation of rotating impeller: a decisive breakthrough in the centrifugal pump.

Magnetic bearings have no mechanical contact between the rotor and stator, and a rotary pump with magnetic bearings therefore has no mechanical wear and thrombosis. The magnetic bearings available, however, contain electromagnets, are complicated to control and have high energy consumption. Therefore, it is difficult to apply an electromagnetic bearing to a rotary pump without disturbing its simplicity, reliability and ability to be implanted. The authors have developed a levitated impeller pump using only permanent magnets. The rotor is supported by permanent radial magnetic forces. The impeller is fixed on one side of the rotor; on the other side the rotor magnets are mounted. Opposite these rotor magents, a driving magnet is fastened to the motor axis. Thereafter, the motor drives the rotor via magnetic coupling. In laboratory tests with saline, where the rotor is still or rotates at under 4,000 rpm, the rotor magnets have one point in contact axially with a spacer between the rotor magnets and the driving magnets. The contacting point is located in the center of the rotor. As the rotating speed increases gradually to more than 4000 rpm, the rotor will disaffiliate from the stator axially, and become fully levitated. Since the axial levitation is produced by hydraulic force and the rotor magnets have a giro-effect, the rotor rotates very stably during levitation. As a left ventricular assist device, the pump works in a rotating speed range of 5,000-8,000 rpm, and the levitation of the impeller is assured by use of the pump. The permanent maglev impeller pump retains the advantages of the rotary pump but overcomes the disadvantages of the leviated pump with electromagnetic-bearing, and has met with most requirements of artificial heart blood pumps, thus promising to have more applications than previously.

Equipment Design↗
PubMedDate not supplied

Technical note: a durable impeller pump with rolling bearing and purge system.

Our former works demonstrated that the authors' impeller pump could support the circulation of experimental animals for several months without harm to blood elements and organ function of the animals. The termination of the experiments was mostly related to wear of the mechanical bearing and the thrombosis along the bearing. To solve the bearing problem, a magnetic bearing was investigated in our laboratory, resulting in some new problems, such as complicated design and control, considerable energy consumption and lower reliability. Progress in developing an impeller pump for long-term application has been achieved recently. Instead of using a slide bearing, a rolling bearing system has been devised. Its service life is more than ten years due to a wear-proof roller made of ultra-high molecular weight poythene. In order to avoid thrombus formation, a special purge system was introduced to the bearing, thus saline with heparin can be infused through the bearing into the pump. Therefore, the bearing keeps working in the saline, and no thrombus will be formed along the beating. The animal experiments demonstrated that 30 cc fluid infusion per hour continuously or interruptedly is enough to prevent the thrombus formation. With these improvements, the impeller pump was continuously run for one year and no bearing wear was measured in the endurance test. The device weighing 150g is fully implantable, consumes around 9.6 W electric energy by delivering 9 l min(-1) blood flow against 120 mmHg mean pressure and reaches a highest total efficiency, 24.7%, of motor (including controller) and pump at this point, which can produce both pulsatile and non-pulsatile flow according to the requirements.

Animals↗
PubMedDate not supplied

Streamlined design of impeller and its effect on pump haemolysis.

To investigate the effect of impeller design on pump haemolysis, five impellers with different numbers of vanes or different vane angles were manufactured and tested in one pump for haemolysis comparison. The impellers had the same dimension and logarithmic spiral vane form that coincided with the stream surfaces in the pump, according to an analytical and three-dimensional design method developed by the authors. Consequently, an impeller with six vanes and a 30 degrees vane angle had the lowest haemolysis index. The result agrees with the theoretical analyses of other investigators searching for the optimal vane number and vane angle to achieve the highest efficiency of the pump.

Biomedical Engineering↗
PubMedDate not supplied

Experimental method to reveal the effect of rotor magnet size and air gap on artificial heart driving motor torque and efficiency.

To investigate experimentally the effect of rotor magnet design on artificial heart driving motor performance, seven rotors with different magnet lengths or thicknesses, as well as different peripheral angles, were manufactured and tested in the same motor stator with different rotating speeds. The input power (voltage and current) and output torque were measured and the motor efficiency was computed. The results demonstrated that the reduction of rotor magnet size and the enlargement of the air gap between the rotor magnets and the stator coil core have no significant effect on motor efficiency, but will reduce the torque value on which the motor achieves the highest efficiency; it could be remedied however by increasing the rotating speed, because the torque at the high efficiency point will increase along with the rotating speed. These results may provide a basis for developing small rotor magnets, large air gap and high efficiency motors for driving an artificial heart pump.

Air↗
PubMedDate not supplied

A novel impeller TAH using magnetic bearings for load reduction.

A novel impeller TAH (total artificial heart), i.e. bi-ventricular assist impeller pumps, has been developed. The device consists of a rotor with motor magnets and two impellers, a stator with motor coil and iron core, and two pump housings. In both sides of the rotor magnets, as well as the stator coil core, a pair of magnetic bearings was devised to partly counteract the attractive forces between the rotor magnets and the stator coil core. This means the magnetic bearings are used for load reduction. On hydrodynamic testing, the two pumps both produced a flow rate as high as 6 l min(-1) and the left pump had a pressure head of 150 mm Hg, and that of the right pump was 50 mm Hg. The highest efficiency of the device, including the motor, the two pumps and the controller, reached 14.7%. The device, weighing 250 g, had a length of 80 mm and a diameter of 40 mm at its largest point. Currently in the world, this is a unique TAH, which is electrically powered and driven by a single motor and has only one moving part, can produce either pulsatile or non-pulsatile flow, both pumps eject flow synchronistically by pulsatile mode, and the volume equilibrium of the two pumps can be achieved automatically without the need for control.

Equipment Design↗
PubMedDate not supplied

Study on stable equilibrium of levitated impeller in rotary pump with passive magnetic bearings.

It is widely acknowledged that the permanent maglev cannot achieve stable equilibrium; the authors have developed, however, a stable permanent maglev centrifugal blood pump. Permanent maglev needs no position detection and feedback control of the rotor, nevertheless the eccentric distance (ED) and vibration amplitude (VA) of the levitator have been measured to demonstrate the levitation and to investigate the factors affecting levitation. Permanent maglev centrifugal impeller pump has a rotor and a stator. The rotor is driven by stator coil and levitated by two passive magnetic bearings. The rotor position is measured by four Hall sensors, which are distributed evenly and peripherally on the end of the stator against the magnetic ring of the bearing on the rotor. The voltage differences of the sensors due to different distances between the sensors and the magnetic ring are converted into ED. The results verify that the rotor can be disaffiliated from the stator if the rotating speed and the flow rate of the pump are large enough, that is, the maximal ED will reduce to about half of the gap between the rotor and the stator. In addition, the gap between rotor and stator and the viscosity of the fluid to be pumped also affect levitation. The former has an optimal value of approximately 2% of the radius of the rotor. For the latter, levitation stability is better with higher viscosity, meaning smaller ED and VA. The pressure to be pumped has no effect on levitation.

Equipment Design↗
PubMedDate not supplied

Computational fluid dynamics verified the advantages of streamlined impeller design in improving flow patterns and anti-haemolysis properties of centrifugal pump.

Computational fluid dynamics (CFD) technology was applied to predict the flow patterns in the authors' streamlined blood pump and an American bio-pump with straight vanes and shroud, respectively. Meanwhile, haemolysis comparative tests of the two pumps were performed to verify the theoretical analysis. The results revealed that the flow patterns in the streamlined impeller are coincident with its logarithmic vanes and parabolic shroud, and there is neither separate flow nor impact in the authors' pump. In the bio-pump, the main flow has the form of logarithmic spiral in vertical section and parabola in cross section, thus there are both stagnation and swirl between the main flow and the straight vanes and shroud. Haemolysis comparative tests demonstrated that the authors' pump has an index of haemolysis of 0.030, less than that of the bio-pump (0.065).

Animals↗
PubMedDate not supplied

World-first implantable aortic valvo-pump (IAVP) with sufficient haemodynamic capacity.

For better anatomic and physiologic fitting, a novel implantable aortic valvo-pump (IAVP) has been developed. A valvo-pump is a micro axial flow impeller pump, which has the same dimensions and function, as well as the same location, of a valve. Therefore, IAVP needs no inlet and outlet tubes, no additional anatomic occupation, and has less physiologic disturbance to natural circulation compared with the traditional bypass left ventricular assist device (LVAD). The device has a stator and a rotor. The stator consists of a motor coil with an iron core and an outflow guide vane; the rotor includes driven magnets and impeller. There is neither bearing nor strut in both the pump and the motor. In order to reduce the attractive force between the rotor and the stator, so as to enhance the durability of the performance, the rotor magnets were minimized without reducing the driving torque and efficiency of the motor. The impeller vane was designed according to a three-dimensional and analytical method, for preventing stasis and turbulence. The largest outer diameter is 24.7 mm and the length at this point is 12.4 mm. The total weight is 40 g (including the rotor of 11 g). The consumed power is 7 W (14 V x 0.5 A) at 15 000 rpm. This rotating speed stays unchanged during haemodynamic testing together with a pulsatile centrifugal pump, which imitates a failing ventricle. The maximal flow cross IAVP reaches over 10 l min(-1) and the pressure head at 0 l min(-1) can be as large as 80 mmHg. At flow rate of 4 - 8 l min(-1), IAVP enlarges the flow c. 1 l min(-1) and meanwhile increases the pressure about 10 mmHg. The pressure pulsatility generated by the pulsatile centrifugal pump remains 40 mmHg after passing IAVP. By first animal experimental trial the device was sewed in aortic position of an 80 kg pig without harm to adjacent tissue and organs. IAVP promises to be a viable alternative to natural donor heart for heart transplantation in the future.

Aorta↗
PubMedDate not supplied

A novel permanent maglev rotary LVAD with passive magnetic bearings.

It has been widely acknowledged that permanent maglev cannot achieve stability; however, the authors have discovered that stable permanent maglev is possible under the effect of a combination of passive magnetic and nonmagnetic forces. In addition, a rotary left ventricular assist device (LVAD) with passive magnetic bearings has been developed. It is a radially driven impeller pump, having a rotor and a stator. The rotor consists of driven magnets and impeller; the motor coil and pump housing form the stator. Two passive magnetic bearings counteract the attractive force between motor coil iron core and rotor magnets; the rotor thereafter can be disaffiliated from the stator and become levitated under the action of passive magnetic and haemodynamic forces. Because of the pressure difference between the outlet and the inlet of the pump, there is a small flow passing through the gap of rotor and stator, and then entering the lower pressure area along the central hole of the rotor. This small flow comes to a full washout of all blood contacting surfaces in the motor. Moreover, a decreased Bernoulli force in the larger gap with faster flow produces a centring force that leads to stable levitation of the rotor. Resultantly, neither mechanical wear nor thrombosis will occur in the pump. The rotor position detection reveals that the precondition of levitation is a high rotating speed (over 3250 rpm) and a high flow rate (over 1 l min(-1)). Haemodynamic tests with porcine blood indicate that the device as a LVAD requires a rotating speed between 3500 and 4000 rpm for producing a blood flow of 4 - 6 l min(-1) against 100 mmHg mean pressure head. The egg-sized device has a weight of 200 g and an O.D. of 40 mm at its largest point.

Animals↗
PubMedDate not supplied

Axial reciprocation of rotating impeller: a novel approach to preventing thrombosis in centrifugal pump.

For long-term application, rotary pumps have to solve the problems of bearing wear and thrombosis along the bearing. Some investigators choose the magnetic bearing for zero friction and to provide no contact between the rotor and stator; the former avoids the mechanical wear and the latter eliminates the possibility of thrombus formation. The authors have tried and have found, however, that it is difficult to apply a magnetic bearing to the rotary pump without disturbing its simplicity, reliability, and implantability, and have therefore developed a much simpler approach to achieve the same results. Instead of using a sliding bearing, a rolling bearing has been devised, and its friction is about 1/15 that of the sliding bearing. Furthermore, a wearproof material of ultra high molecular weight polythene has been adopted to make the rollers, and its antiwear property is eight times better than metal. The service life of the bearing has thus been prolonged. To prevent thrombus formation along the bearing, the impeller reciprocates axially as the impeller changes its rotating speed periodically to produce a pulsatile flow. The reciprocation is the result of the effects of a magnetic force between the motor rotor and stator and a hydraulic force between the blood flow and the impeller. Similar to a piston pump, the oscillating impeller can make the blood flow in and out of the bearing, resulting in washout with fresh blood once a cycle. This obviously helps to prevent thrombosis along the bearing and in the pump. Endurance tests with saline of this novel pump demonstrated device durability, promising long-term assisted circulation.

Centrifugation↗